US20050065521A1

US20050065521A1 - Method and apparatus for bone fracture fixation

Info

Publication number: US20050065521A1
Application number: US10/980,705
Authority: US
Inventors: Shon Steger; Brian Schumacher; Jeffrey Duncan
Original assignee: Individual
Current assignee: Zimmer Biomet CMF and Thoracic LLC
Priority date: 2002-02-22
Filing date: 2004-11-03
Publication date: 2005-03-24
Also published as: EP1654994B1; US20100179600A1; DE602005005918T2; ES2303173T3; JP2006130317A; EP1654994A1; US8460345B2; DE602005005918D1

Abstract

A plate for coupling severed bone regions comprising at least one bridge region, the at least one bridge region terminating in at least two bone fixation regions. The at least two bone fixation regions each contain at least one aperture for receiving a suitable fastening device for securing the plate to the bone regions to be coupled. The bridge region may be configured so as to be easily severed by a suitable severing device such as surgical scissors. The plate and fastening device may be formed from a bio-compatible or bio-resorbable material.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation-in-part of U.S. patent application Ser. No. 10/081,166, filed on Feb. 22, 2002. The disclosure of the above application is incorporated herein by reference.

FIELD

The present teachings relate to surgical applications for the repair of bone fractures and deformities. More particularly, the teachings relate to a method and apparatus for securing two severed bone portions in a relatively fixed relationship to each other.

BACKGROUND

In various orthopedic surgical procedures, it is necessary to align and secure two severed bone portions in a relatively fixed relationship to each other. For example, it is often necessary to establish such a secured relationship after a bone has been fractured as a result of either natural causes or physician intervention. To ensure that the bone can regenerate in the proper orientation and fuse the fracture, it is important that the bone portions be fixed in the desired position during bone regeneration.
It is known in the art to provide metal plates for the repair of bone fractures. The plates are generally secured to the fractured bone portions with fasteners such as screws. Among other applications, the plates and fasteners are used to provide rigid stabilization of sternum fractures. The plates conventionally employed for sternum osteosynthesis generally comprise small, generally flat, sections of metal. The sections contain round and perhaps threaded screw holes at various points along their lengths for fastening the sections to bone.
In one technique for sternum reconstruction, a plate having one or more apertures is positioned proximate to the surface of the sternum so that the plate spans the severed region of the sternum and is held in relative position thereto through a threaded plate/screw interface. The plate is then bent into shape, if necessary, and secured to the sternum using a plurality of fasteners seated within the apertures. Subsequently, the fasteners and plate may be removed to allow surgical access to the sternum (e.g., to treat vital organs within the thoracic cavity). Finally, the same plate or a new plate is again fastened to the sternum through engagement of the fasteners with the sternum.
While known systems utilizing plates and fasteners for aiding the osteosynthesis of severed bone regions have proven to be acceptable for certain applications, such systems are nevertheless susceptible to improvements that may enhance their performance. In this regard, many known systems require time consuming attachment. Additionally, known systems, which necessitate the insertion, removal, and subsequent reinsertion of fasteners into the bone, negatively affect fastener purchase. Furthermore, many known systems do not facilitate cutting of the plate to provide expedited physician access to the area or cavity requiring access through the location spanned by the plate.

SUMMARY

The present teachings relate to an apparatus and method for reapproximating and securing portions of severed bone. Reapproximation of the severed bone portions is carried out using a bone reapproximation device, which is able to laterally hook and reapproximate the separated bone regions. Once reapproximated, the bone regions are coupled using a plate including at least two bone fixation regions and a bridge region disposed between the bone fixation regions. Each bone fixation region contains at least one receptor used to receive a fastener suitable for securing the plate to the bone portions to be coupled. Both the plate and the fastening devices may be bio-resorbable and/or bio-compatible.
The fasteners may include a main body portion with an upper shaft portion and a lower shaft portion. Once secured to the bone surface due to interaction with the fasteners, the plate may be removed from engagement with the bone surface by removing the head member and subsequently removing the plate from the bone surface. The fastener configuration allows for removal of the plate without requiring removal of the main body portion of the fastener from the bone, thus allowing the main body portion and hole within the bone to be used again in the future to secure the plate to the bone surface. In addition, the plate may alternatively be secured to the bone surface by a one-piece locking, or non-locking, screw such that removal of the plate from the bone requires severing of the plate or removal of each one-piece screw. As can be appreciated, the fastener chosen (i.e., one-piece versus multiple-piece construction) for the particular plate will vary depending on the requirements of the particular application.
The plate of the present teachings is configured to permit rapid separation of the bone portions previously secured by the plate. The plate may be severed using any suitable cutting device, such as surgical scissors, surgical wire cutters, or surgical plate cutters. Severing of the plate using surgical scissors, wire cutters, or plate cutters is facilitated due to the presence of a bridge region that is specifically configured to allow for such engagement. Optimum bridge severability is accomplished mainly through manipulation of the aspect ratio and area of the cross-section of the bridge region. The aspect ratio of the cross section is generally defined as the height of the bridge region in the cutting device divided by the width of the bridge region in the cutting device. Therefore, the aspect ratio of the cross-section will change depending on the orientation of the cutting device, unless the cross-section of the bridge includes a generally square or round cross-section. Generally speaking, for a cross section of a constant area, as the width of the bridge region in the cutting device is increased, the height of the bridge region is decreased, and the force required to sever the bridge region is reduced. In addition, the bridge region may be raised or tapered so as to ease engagement of the bridge region by surgical wire cutters, surgical plate cutters, or surgical scissors. The bridge region may also be weakened or contain a notch to further aid in severing the bridge region.
The plate of the present teachings may also have numerous bridge regions and bone fixation regions arranged in a variety of shapes so as to produce a plate with a configuration capable of coupling a large or irregularly shaped region of severed bones, the bones terminating at various different angles to each other. To aid in the coupling of such severed bone regions, the bridge regions and the bone fixation regions may extend at a variety of different angles. Further, the bone fixation regions and the bridge regions may be in differing planes so as to couple severed bone regions that terminate at differing planes to each other.
Further areas of applicability of the present teachings will become apparent from the detailed description provided hereinafter. It should be understood that the detailed description and specific examples, while indicating the preferred embodiments of the teachings, are intended for purposes of illustration only and are not intended to limit the scope of the teachings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective post-operative anterior illustration of a human thorax. Specifically, FIG. 1 illustrates a previously severed sternum coupled by a plate in one possible placement scheme according to the teachings;
FIG. 2 is a perspective view of the plate of FIG. 1;
FIG. 3 is a cross-sectional view taken along line 3-3 of FIG. 2;
FIG. 4A is a perspective view of a one-piece, self-tapping fastener used to secure the plate of FIG. 1 to a severed bone portion;
FIG. 4B is a perspective view of the fastener of FIG. 4A incorporating a self-drilling tip;
FIG. 4C is a cross-sectional view of the fastener of FIG. 4A, the fastener seated within a threaded aperture of the plate of FIG. 1;
FIG. 4D is a cross-sectional view of the fastener of FIG. 4A, the fastener seated within an aperture of the plate of FIG. 1;
FIG. 5A is an exploded perspective view of a two-piece fastener used to secure the plate of FIG. 1 to a severed bone portion;
FIG. 5B is a side view of the fastener of FIG. 5A, the fastener seated within an aperture of the plate of FIG. 1;
FIG. 6 is a partially sectioned side view of the plate of FIG. 1 illustrating the cooperation of the plate with the fasteners of FIG. 4 for securing the plate to the previously severed sternum halves, wherein the previously severed sternum halves have been reapproximated using the illustrated surgical forceps;
FIG. 7 is a perspective view of a plate according to the present teachings, the plate having four bone securing regions and a bridge region spanning between each bone securing region;
FIG. 8A is a side view of the plate of FIG. 7 showing a bridge design in accordance with the principals of the present teachings;
FIG. 8B is a side view of the plate of FIG. 7 showing a bridge design in accordance with the principals of the present teachings;
FIG. 8C is a side view of the plate of FIG. 7 showing a bridge design in accordance with the principals of the present teachings;
FIG. 9 is a perspective view of a plate according to the present teachings, the plate having four bone securing regions and a bridge region spanning between each bone securing region;
FIG. 10A is a side view of the plate of FIG. 9 showing a bridge design in accordance with the principals of the present teachings;
FIG. 10B is a side view of the plate of FIG. 9 showing a bridge design in accordance with the principals of the present teachings;
FIG. 10C is a side view of the plate of FIG. 9 showing a bridge design in accordance with the principals of the present teachings;
FIG. 11 is a perspective view of a plate according to the present teachings, the plate having two bone securing regions and a bridge region;
FIG. 12A is a side view of the plate of FIG. 11 showing a bridge design in accordance with the principals of the present teachings;
FIG. 12B is a side view of the plate of FIG. 11 showing a bridge design in accordance with the principals of the present teachings;
FIG. 12C is a side view of the plate of FIG. 11 showing a bridge design in accordance with the principals of the present teachings;
FIG. 13 is a perspective view of a plate according to the present teachings, the plate having two bone securing regions and a bridge region;
FIG. 14A is a side view of the plate of FIG. 13 showing a bridge design in accordance with the principals of the present teachings;
FIG. 14B is a side view of the plate of FIG. 13 showing a bridge design in accordance with the principals of the present teachings;
FIG. 14C is a side view of the plate of FIG. 13 showing a bridge design in accordance with the principals of the present teachings;
FIG. 15 is a perspective view of a plate according to the present teachings, the plate having two bone securing regions and a bridge region;
FIG. 16A is a side view of the plate of FIG. 15 showing a bridge design in accordance with the principals of the present teachings;
FIG. 16B is a side view of the plate of FIG. 15 showing a bridge design in accordance with the principals of the present teachings;
FIG. 16C is a side view of the plate of FIG. 15 showing a bridge design in accordance with the principals of the present teachings;
FIG. 17 is a perspective view of the plate of FIG. 7 with a bridge region of the plate engaged by plate cutter, wire cutter, or surgical scissors;
FIG. 18 is a perspective view of the plate of FIG. 7 with a bridge region of the plate engaged by another plate cutter, wire cutter, or pair of surgical scissors; and
FIG. 19 is a perspective view of the plate of FIG. 7 with a bridge region of the plate engaged by another plate cutter, wire cutter, or pair of surgical scissors.

DETAILED DESCRIPTION

The following description is merely exemplary in nature and is in no way intended to limit the teachings, its application, or uses.
Referring to FIG. 1, a system constructed in accordance with the present teachings is generally identified with reference numeral 10. The system 10 is shown operatively associated within a human body 12 and specifically a human thorax 14. However, it will become apparent to those skilled in the art that certain aspects of the present teachings have applicability to other surgical applications.
The anterior of the thorax 14 is formed by a sternum 16, xyphoid 18, manubrium 20, costal cartilage, and ribs 24. In addition, the clavicle 22 is shown connecting the sternum 16 to the scapula and humerus (neither shown). The sternum 16, as shown, has previously undergone a medical procedure known as a median sternotomy. As a result of this procedure, the sternum 16 has been severed, thus permitting physician access to the tissues or organs located in thoracic cavity 26. However, the sternum 16 has since been reapproximated with previously severed portions A and B now bound together by the system 10 of the present teachings.
With continued reference to FIG. 1 and additional reference to FIGS. 2 through 19, the system 10 of the present teachings is shown to include a plate 28. The plate 28 is shown to include an upper surface 30, a lower surface 32, and a perimeter surface 34. The perimeter surface 34 may be specifically defined, as seen in FIG. 2, or may simply be the point at which the upper surface 30 and the lower surface 32 meet. The plate 28 is divided into varying regions such as at least two bone fixation regions 36 and at least one bridge region 38.
The bridge region 38 joins the bone fixation regions 36 and may be disposed generally flush with either, or both, of the upper or lower surfaces 30, 32 or may be offset from both of the upper and lower surfaces 30, 32, as will be discussed further below. Each bone fixation region 36 defines at least one aperture 40. The apertures 40 may be threaded or simply formed as non-threaded through holes. The apertures 40 may extend symmetrically from the bridge region 38 or may be arranged asymmetrically. Further, the apertures 40 may optionally include a circular or an oval countersink 42 and may be internally threaded, as best shown in FIGS. 2 and 3. The apertures 40 are adapted to receive a fastener 44 a-c for interconnecting the plate 28 with a severed bone region, such as severed halves A and B of the sternum 16. More specifically, the bridge region 38 spans the fracture while bone fixation regions 36 are fastened to the bone regions on either side of the fracture once the severed halves A and B have been reapproximated.
The plate 28 described in any of the embodiments of the present teachings may be made of a variety of bio-resorbable materials. One resorbable material of particular interest is marketed by Biomet, Inc. (Warsaw, Ind.) under the tradename LACTOSORB®. LACTOSORB® is an absorbable co-polymer synthesized from all-natural ingredients: 82% L-lactic acid and 18% glycolic acid, and is substantially amorphous (i.e., without crystallinity), meaning that its degradation is uniform, precluding the crystalline release associated with degrading copolymers that have been associated with late inflammatory reactions. Furthermore, the LACTOSORB® copolymer ratio permits the polymer to retain most of its strength for six to eight weeks. Such a time period is appropriate for healing, but not so long as to raise concerns about long-term stress shielding of bone. In addition to LACTOSORB®, other resorbable materials may be used such as PLA, PGA, and others including various polymers, ceramics, etc.
The plate 28 may also be made from a variety of bio-compatible materials. Examples of bio-compatible materials that may be used are the implantable plastics PEEK or PET. In addition to PEEK or PET, implantable surgical metals may also be used. Alloys that may be implanted are, but not limited to, stainless steel, titanium, or cobalt chrome molybdenum. Specifically, commercially pure titanium, listed as grade 1, 2, 3, or 4 or titanium alloy such as titanium 6-aluminum/4-vanadium may be used. The plate 28 may be inelastically deformable so as to retain its shape once contoured to cooperate with the shape of the bone regions to be secured.
With particular reference to FIGS. 4A-4D, a fastener 44 a is provided for use with the plate 28. The fastener 44 a is a one-piece, locking fastener and is designed so as to matingly engage the threaded apertures 40 of bone fixation regions 36. The fastener 44 a is considered a locking fastener as the engagement between threads 52 on the fastener 44 a and the threaded aperture 40 prevents relative movement therebetween. As can be appreciated, preventing relative movement between the plate 28 and the fastener 44 a helps ensure that the plate 28 remains in a desired position relative to the bone halves A, B.
With particular reference to FIGS. 4A-4D, a second fastener 44 b is provided for use with the plate 28. The fastener 44 b is a one-piece, non-locking fastener and is received by apertures 40 b formed through the respective bone fixation regions 36 of the plate 28. The fastener 44 b is substantially identical to fastener 44 a, but is considered a non-locking fastener due to the relationship between the plate 28 and the fastener 44 b. Specifically, because apertures 40 b are simply bores formed through the respective bone fixation regions 36 of the plate 28, and as such, do not include threads, the relationship between the fasteners 44 b and the plate 28 is considered “non-locking.” As can be appreciated, such a relationship may provide a cost advantage to the plate 28 as the additional cost associated with forming threads in the apertures 40 b is obviated.
With reference to FIGS. 5A-5B, a third fastener 44 c of the present teachings is shown to generally include a main body 46 and a head member 48. The main body 46 includes an upper shaft portion 50 and a lower shaft portion 52. The lower shaft portion 52 is externally threaded, fluted, and preferably fitted with a pointed end portion 54 so as to permit self-drilling of the sternum 16 by fastener 44. Insertion of the lower shaft portion 52 into sternum 16 is limited by a flange 56 interdisposed between the upper and lower shaft portions 50 and 52. The upper shaft portion 50 is also externally threaded and adapted to engage an internally threaded aperture 58 of the head member 48. The head member 48 is externally threaded for engaging one of the plurality of internally threaded apertures 40 of the plate 28.
In one application, the thread pitches of the upper shaft portion 50, lower shaft portion 52, and the thread pitch of the external threads of the head member 48 are common. The external threads of the head member 48 and the externally threaded lower shaft portion 52 have a common thread lead. In the exemplary embodiment illustrated, the externally threaded lower shaft portion 52 has a single lead configuration while the external threads of the upper shaft portion 50 and head member 48 have a double lead configuration. The use of faster 44 c is advantageous because it allows the plate 28 to be removed while the lower portion 52 remains in place in the event that the plate 28 must be removed. This retains the integrity of each hole formed in the bone and eliminates the need to remove and re-insert different fastening devices into the bone each time the plate 28 is removed and re-seated.
Fasteners 44 a-c may be formed of a suitably rigid biocompatible material. However, if the intent is to insert fasteners 44 a-c into the bone for a temporary period of time, it may be formed from a bio-resorbable material. Fasteners 44 a-c formed from bio-resorbable materials degrade within the body, thus eliminating the need for subsequent removal of the fasteners 44 a-c.
It should be noted that any of the foregoing fasteners 44 a-c may include a self-tapping feature and/or a self-drilling feature. A self-tapping tip 55 is used to create a series of threads in the receiving bone, as best shown in FIG. 4A while a self-drilling tip 57 is used to create a bore in the receiving bone, as best shown in FIG. 4B. It should be understood that while the fasteners 44 a, 44 b may include either tip 55, 57, that the self-drilling tip 57 may further incorporate a self-tapping feature such that as the generally sharp tip 57 creates a bore in the receiving bone, the tip 57 concurrently cuts a series of threads therein for engagement with the threads 52 of the respective fastener 44 a, 44 b. Because each fastener 44 a-c is inserted through an aperture 40 formed in the bone fixation region 36 of the plate in a similar fashion, fastener 44 a will be used herein after when discussing the attachment of the plate 28 to the respective bone halves A, B.
In use, before the plate 28 may be secured to severed halves A and B of sternum 16, the severed halves A and B must be reapproximated. Reapproximation of severed sternum halves A and B may be carried out using, as seen in FIG. 6, a reapproximation device, such as surgical forceps 60. The surgical forceps 60 are comprised of two jaws 61, 62 that are interconnected at actuation point 63. The jaws 61, 62 are able to laterally hook separated bone halves A and B. By pivoting the jaws 61, 62 about actuation point 63, a physician is able to decrease the distance between the jaws 61, 62 and thus, in turn, decrease the distance between the separated bone halves A and B.
Once the separated bone halves A and B have been reapproximated, the plate 28 is positioned on the bone surfaces to be coupled so that certain apertures 40 may be selectively used as a guide for drilling holes (not specifically shown) in the bone surfaces for receiving the fasteners 44 a.
A first of the fasteners 44 a is passed through a selected one of the apertures 40 and rotated so that the externally threaded lower portion 52 is driven into the hole (not shown) in one of the halves A or B of the sternum 16. For example, as the externally threaded lower portion 52 of the fastener 44 a is driven into the sternum 16, the external threads 52 simultaneously engage the internally threaded aperture 40 of the plate 28. In addition, the fastener may also self-drill and/or self-tap the bone half A, B, depending on the particular tip 55, 57 of the fastener 44 a, as previously discussed.
Additional fasteners 44 a are used to interconnect the plate 28 with the sternum 16 in a substantially identical manner. However, it will become appreciated by those skilled in the art that any number of fasteners 44 a may be employed depending on a particular application.
After the plate 28 has been secured into place, it may be necessary to remove the plate 28 so as to allow a physician to re-separate the sternum 16 and gain access to either the sternum 16 or the thoracic cavity 26 to provide treatment (e.g., emergency or planned secondary cardiac surgery). To facilitate removal of the plate 28, the fasteners 44 a are unthreaded and removed from the apertures 40 of the respective bone fixation regions 36. When the plate 28 is removed, it retains its shape due to the inelastic deformation.
When the secondary surgical procedure is complete, the separated halves A and B of the sternum 16 are again reapproximated using the surgical forceps 60 in the manner described above. Once the separated halves A and B of sternum 16 are reapproximated to a desired distance, the halves A and B are held into place by replacing plate 28. The plate 28 is replaced by inserting the fasteners 44 a through the selective apertures 40 of the bone fixation regions 36 and simultaneously threading the internal threads of the aperture 40 with the external threads 52 of the fastener 44 a.
Referring to FIGS. 9 and 10 a-10 c, a plate 28 a according to the present teachings is shown. Plate 28 a is generally similar to plate 28 and thus a detailed description of plate 28 a is not necessary. However, unlike plate 28, plate 28 a contains extended bone fixation regions 36 a having a plurality of apertures 40. It should be noted that plate 28 a also includes bridge regions 38 that connect the respective bone fixation regions 36 a.
Referring to FIGS. 11 and 12 a-12 c, a plate 28 b according to the present teachings is shown. Plate 28 b is generally similar to plate 28 and thus a detailed description of plate 28 b is not necessary. However, unlike plate 28, plate 28 b includes a single bridge region 38 extending between two bone fixation regions 36 b. Again, the bridge region 38 extends generally over the bone fracture region while the bone fixation regions 36 b are securely attached to respective halves A and B by fasteners 44.
Referring to FIGS. 13 and 14 a-14 c, a plate 28 c according to the present teachings is shown. Plate 28 c is generally similar to plate 28 and thus a detailed description of plate 28 c is not necessary. However, unlike plate 28, plate 28 c includes a single bridge region 38 extending between two bone fixation regions 36 c. The bone fixation regions 36 c are formed at an angle relative to the bridge region 38, as best shown in FIG. 13. The bone fixation regions 36 c are formed at an angle relative to the bridge region 38 to better fit onto the sternum 16 and to allow for the fixation of transverse fractures. It should be noted that any of the other embodiments of the present teachings may have an orientation between the bone fixation regions 36 c and bridge region 38 similar to that of plate 28 c.
Plate 28 d is illustrated in FIGS. 15 and 16 a-16 c and is in accordance with the present teachings. Plate 28 d is generally similar to plate 28 and thus a detailed description of plate 28 d is not necessary. Plate 28 d is different from plate 28 in that plate 28 d includes a single bridge region 38 extending generally between two bone fixation regions 36 d. The bone fixation regions 36 d are substantially similar to those of plate 28, except that the bone fixation regions of plate 28 d are disposed in an opposite relationship relative to one another. Specifically, a first bone fixation region 36 d′ runs generally perpendicular to the bridge region 38 while a second bone fixation region 36 d″ runs generally parallel with the bridge region 38, as best shown in FIG. 15.
Bone fixation region 36 d″ includes a total of three apertures 40 while bone fixation region 36 d′ includes two apertures 40 for use in attachment to respective bone halves A, B. The extra aperture 40 provided on fixation region 36 d″ allows for an extra fastener to securely fix the fixation region 36 d″ to a respective bone halve A, B. Therefore, the extra aperture 40 and corresponding fastener 44 a serves to restrict fastener pull-through and helps to ensure that the plate 28 remains fixed to the bone halves A, B.
In each of the foregoing plates 28, 28 a, 28 b, 28 c, and 28 d, the bridge region 38 may be offset from the bone fixation regions so as to form a recess 70 either between the upper surface 30 and the bridge region 38, between the lower surface 32 and the bridge region 38, or between both surfaces 30, 32 and the bridge region 38, as best shown in FIGS. 8 a-c, 10 a-c, 12 a-c, 14 a-c, and 16 a-c. However, it should be noted that the bridge region 38 could include upper and lower surfaces 76, 78 that are generally planar with the upper and lower surfaces 30, 32 of the bone fixation regions 36, whereby the width W is small enough so as to allow the bridge region 38 to be severed in an emergency, as will be discussed further below. The bridge region 38 provides each plate 28, 28 a, 28 b, 28 c, and 28 d with the requisite strength between the bone halves A, B while the recess 70, or with W of the bridge region 38, concurrently provides a physician or surgeon with the ability to quickly cut the bridge region 38 to quickly remove the plate 28, 28 a, 28 b, 28 c, and 28 d. Because each plate 28, 28 a, 28 b, 28 c, and 28 d includes a substantially identical bridge region 38, reference will be made to plate 28 when describing the bridge region 38 hereinafter.
The recess 70 may be easily engaged by a cutting device such as surgical scissors 72, wire cutters, plate cutters, or a cautery (only applicable for non-metal fixation) so as to permit the scissors 72, wire cutters, plate cutters, or cautery to sever the bridge region 38, as best shown in FIG. 17. Consequently, the plate 28 permits a physician or surgeon access to the thoracic cavity 26 by removing the fasteners 44 a or by severing the bridge region 38.
The bridge region 38 may be tapered at its perimeter surface 74, its upper surface 76, or its lower surface 78 to allow the bridge region 38 to be severed more easily and to provide a smooth surface for added patient comfort. Tapering of the upper surface 76 and the perimeter surface 74 relatively weakens the bridge region 38 and forms the recess 70 generally between upper surface 30 of the bone fixation regions 36 and the upper surface 76 of the bridge region 38, as best shown in FIG. 8 a. Tapering of the lower surface 78 results in the formation of the recess 70 generally between the lower surface 32 of the bone fixation regions 36 and the lower surface 78 of the bridge region 38, as best shown in FIG. 8 b. In addition, the recess 70 may be formed proximate to both the upper and lower surfaces 76, 78 of the bridge region 38, as best shown in FIG. 8 c. It should be noted that while FIG. 17 illustrates plate 28 as having a generally rectangular bridge region 38, alternate embodiments may contain a bridge that is elliptical, oval, or of another cross-section shape that will facilitate engagement of the bridge by a suitable cutting device such as surgical scissors 72 or wire cutters. Further, it is envisioned that any of the other embodiments of the present teachings may include a bridge region 38 that is cylindrical, elliptical, oval, square, or of another cross-section shape so as to facilitate engagement of the bridge by a suitable cutting device.
While the bridge region 38 may include a plurality of varying cross-sectional shapes such as elliptical, oval, or rectangular, the bridge region 38 must be designed so as to accommodate the force requirements with respect to holding the bone halves A, B together while concurrently allowing a physician or surgeon to easily and quickly remove the plate 28 under exigent circumstances. The bridge region 38 is designed to accommodate both requirements (i.e., strength and severability), by balancing strength requirements with cutability requirements in designing the cross-sectional shape. The latter design feature maintains requisite strength properties while providing for quick and easy removal.
The relationship between the requisite force required to sever the bridge region 38 and the cross-sectional area of the bridge region 38 is substantially linear. Therefore, the larger the cross-sectional area of the bridge region 38, the greater the force required to sever the bridge region 38. The cross-sectional area of the bridge region 38 is deigned to both accommodate the strength requirements of the system 10 and to optimize the severability of the bridge region 38.
Optimum bridge severability can be substantially manipulated for a given cross-sectional area, accomplished mainly through manipulation of the aspect ratio of the cross-section of the bridge region 38. The aspect ratio is generally defined as the height H of the plate 28 in the cutter 72 divided by the width W of the plate 28 in the cutter 72. The height of the bridge region 38 is generally defined between upper and lower surfaces 76, 78 of the bridge region 38, while the width is generally measured perpendicular to the upper and lower surfaces 76, 78, as best shown in FIGS. 7 and 8 a-c. The height of the bridge section may or may not correspond to the height of the plate in the cutter depending on the orientation of the cutter on the bridge section. In this manner, the width of the bridge region 38 is generally measured perpendicular to the height of the region 38. Generally speaking, for a constant cross-sectional area or for a given tensile load carried by the bridge section, as the width of the bridge region 38 is increased, the height of the bridge region 38 is decreased. For a given cross-sectional area, as the cutting aspect ratio increases (H/W), the force required to sever the bridge section is reduced.
Because the cut force is directly attributable to the size, shape, and aspect ratio of the cross-section of the bridge region 38, an Aspect Ratio Factor (ARF) is calculated for use in determining a desirable aspect ratio (i.e., height and width) of a bridge region 38. The ARF is determined by dividing the cut force in a tested orientation of a bridge portion by an average of the cut forces measured in both directions. As previously discussed, the aspect ratio of the bridge region 38 is defined as the height of the bridge region 38 in a cutter 72 divided by the width of the bridge region 38 in a cutter 72. Therefore, a given bridge region 38 having an aspect ratio of A would have an aspect ratio of 1/A when rotated 90 degrees in the cutter 72. Therefore, the ARF may be determined by the following equations for each aspect ratio:
ARF _A=Cut Force_A/((Cut Force_A+Cut Force_1/A)/2)
ARF _1/A=Cut Force_1/A/((Cut Force_A+Cut Force_1/A)/2)
For example, a force required to cut a square cross-section will be the same regardless of the orientation of the section in the cutter 72 as the width of the section is generally equal to the height. For a plate of the same cross-sectional area, but with an aspect ratio of 2 (i.e., the bridge region 38 is twice as wide as it is high), the cut force required to sever the bridge is reduced.
For example, the natural log of the aspect ratio for a plate having an aspect ratio of 2 is 0.69. From a regression of experimental data relating the aspect ratio to the ARF for cross sections made from Grade IV titanium, the natural logarithm of the ARF corresponding to the aspect ratio of 2 is approximately −0.1, which corresponds to an ARF of 0.904. Substituting the ARF value into the above ARFA equation and solving for Cut ForceA yields a cut force that is roughly 83% of the load required to cut the same cross-section having an aspect ratio of ½. The cross-section having an aspect ratio of ½ has the same cross-sectional area as the section having an aspect ratio of 2, but the section having an aspect ratio of ½ is rotated 90 degrees in the cutting tool 72 (such that the above equation is solved for Cut Force_1/Aand the aspect ratio is 1/A), and is thus more difficult to cut.
Therefore, a bridge region 38 having an aspect ratio of 2 (i.e., the bridge region 38 is twice as wide as it is high) is easier to cut than a bridge portion having an aspect ratio of ½ (i.e., the bridge region 38 is twice as high as it is wide). It should be noted that when the bridge region 38 has an aspect ratio of either 2 or ½, that the bridge region 38 will have an identical cross-sectional area. In other words, the relationship between the width and height remains the same. For example, a plate 28 having a bridge region 38 measuring 2 mm in one direction and 1 mm in the other direction will yield a cross-sectional area of 2 mm². The aspect ratio only changes from 2 to ½ when the plate 28 is rotated 90 degrees in the cutting tool 72. When the bridge region 38 is cut along the 2 mm surface, the aspect ratio is 2 and the plate 28 is easily severed. Conversely, when the plate 28 is cut along the 1 mm section, the aspect ratio is ½ and the plate 28 requires a higher cut force in order to sever the bridge region 38. Therefore, cut force and aspect ratio are directly related.
Based on the inventors' research with a particular cutter, a cut force (i.e., applied to the handles of a cutter) with a particular cutter of 55.1 lbf is generally considered an acceptable force, allowing most surgeons to easily sever a plate 28 using cutting tools 72 commonly found in a crash cart of an emergency room. As previously discussed, the force required to cut or sever a given bridge region 38 of a plate 28 is, in part, dependent on the aspect ratio of the bridge region 38 to be cut. The plate 28 can be easily cut without reducing the cross-sectional area of the bridge region 38 beyond an acceptable limit by optimizing the aspect ratio of the bridge region's cross-section.
Typically, most devices used in sternal closure procedures are designed to withstand loads ranging from 400N (90 lbf) to 1200N (270 lbf). Such loads are generally applied by the patient during breathing, coughing, etc. and must be safely transmitted by one or more plates 28 to halves A, B via bridge fixation regions 36 and one or more bridge regions 38. Therefore, the first step in designing a plate 28 is to ensure that the bridge region 38 is large enough to carry such loads with an appropriate factor of safety. Once an adequate cross-sectional area is determined, the aspect ratio of the section is adjusted to facilitate severability of the section when quick removal of the plate 28 is required.
In adjusting the aspect ratio (i.e., height and width) of the bridge region 38, the following equations (A-H) are useful in determining the maximum cut height for a given bridge region 38, where h_maxis the maximum height of the bridge region 38, w is the width of the bridge region 38, and a is the area of the cross-section of the bridge region 38. It should be noted that while the following equations apply for any orientation of the plate 28 in the cutter 72, the use of the bridge width and maximum bridge section height is dependent on relating it to the cutting orientation as shown in FIG. 18. More generally, the height could be considered the height of the bridge region in the cutter 72 (and likewise the width of the bridge region in the cutter) and then the specific orientation of cutting drops out: $\begin{matrix} A . 63.7 = ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140} \\ B . 55.1 = ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140} \\ C . 22.2 = ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140} \\ D . 19.2 = ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140} \\ E . 63.7 = ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124} \\ F . 55.1 = ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124} \\ G . 22.2 = ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124} \\ H . 19.2 = ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124} \end{matrix}$
The constants on the left-hand side of the equations A-H (i.e., 63.7, 55.1, 22.2, and 19.2) refer to experimentally determined acceptable cut force values for a given bridge region 38. The following equation may be used to determine an acceptable cut force where CF refers to a Maximum allowable cut force; S1 refers to a slope of a cut force vs. cross-sectional area (determined experimentally); S2 refers to a slope of Ln(ARF) vs. Ln(aspect ratio) (determined experimentally); and C1 refers to a Y-intercept of the cut force vs. cross-sectional area data (determined experimentally): $C F = ((S1) (a) + C1) {(\frac{w}{h_{\max}})}^{S2}$
For the actual cut force to be less than or equal to the maximum allowable cut force given a defined width w, the height H must be less than or equal to Hmax. For a rectangular cross section a=h*w the equation becomes: $C F = ((S1) (w) (h_{\max}) + C1) {(\frac{w}{h_{\max}})}^{S2}$
The cut force (applied to the handle of an instrument by a doctor or physician) requirements are 63.7 lbf, 55.1 lbf, 22.2 lbf, and 19.2 lbf, respectively, and generally provide a scale on which a plate designer may choose to set the cut force. The 63.7 lbf and 55.1 lbf cut force refer to the largest clinically relevant cutter. The 22.2 lbf and 19.2 lbf cut force refer to the smallest clinically relevant cutter. The constants S1, C1 and S2 are dependent on the material chosen. The cut force is initially determined for the largest relevant cutter. However, the following equation can be scaled using the experimentally determined ratio (L1 over L2) of cut force required to sever a given section using a first cutter (L1) versus experimentally determined cut force required to sever the same given section using a second cutter (L2). In this manner, the plate can be severed by other clinically relevant cutters, (e.g., the small cutter) with the scaled equation describing the required cut force is given as: $C F (\frac{C F_{1}}{C F_{2}}) = ((S1) (a) + C1) {(\frac{w}{h_{\max}})}^{S2}$
Using several plate shape sections to determine L1/L2 and regressing the data, the appropriate relationship was experimentally determined to determine the 22.2 lbf and 19.2 lbf on the left hand side of the equation for the small clinically relevant cutter. In essence, this modification to the equation shows that a smaller cutter with the same hand force on the cutter requires a section that can be cut more easily.
While technically, it most correct to multiply S1 and C1 each by the ratio of cut force using the small cutter over cut force using the large cutter, the above equation is equivalent to dividing CF by the quantity (cut force using small cutter over cut force using the large cutter). This is how the equations A and B were scaled to obtain the equations C and D and how the equations E and F were scaled to obtain the equations G and H.
For example, equations A and E are both set to yield a cut force of 63.7 lbf with the area, width, and height as variables. Using this maximum cut force, for a rectangular section and using Grade 4 titanium with the largest clinically relevant cutter, equation A gives the relationship between height and width of the bridge section. If the maximum cut height (which may be the same as the width of the bridge section, as shown in FIG. 18) is set at 0.05 inches, the maximum height of the bridge will be determined to be 0.0784 inches. From the assigned width and determined height, the cross-sectional area can be determined to be 0.00392 square inches. Any height of the bridge less than 0.0784 inches will allow for cutting at a cut force.

In contrast, using the same equation A based on the same maximum cut force, a rectangular section, and the same cutter, if the height of the plate in the cutter (Corresponding to the width of the bridge section in proposed FIG. 18A) were set at 0.0784 inches (equivalent to the maximum bridge height of the bridge section determined in the prior example), then the maximum height of the bridge section would be determined to be 0.0567 inches. From the set width and the determined height, the cross-sectional area can be determined to be 0.00445 square inches. For the same cut force, the geometry determined in the second example has a cross-sectional area 13.4% larger than the geometry of the first example. This directly translates into the ability of the bridge section of example 2 to transmit a tensile load 13.4% higher than the bridge section of example 1. In this manner, if a plate must withstand a specified load, and the cross-sectional area needed to withstand the load is known, the aspect ratio can be adjusted using equations A-H to optimize the plate design (i.e., height and width) for both strength and severability. The following table summarizes examples 1 and 2:



	Example 1	Example 2

Maximum Cut Force	63.7	63.7
Set Width	0.05	0.0784
Determined Height	0.0784	0.0567
Area of Cross Section	0.00392	0.00445

Section Shape

In the same way, the experimentally measured force on the handle can be translated to the actual force seen by the plate using the mechanical advantage of the given cutter. For the double action cutter used as the largest clinically relevant cutter, the mechanical advantage was determined to be 6.1 to 7.1 depending on hand position, with the plate positioned so that up to 2 mm of cutter extended beyond the plate. In the tested position, the mechanical advantage was determined to be 6.8. From this, the actual force seen by the plate associated with an applied cut force of 63.7 lbf can be determined in the range of 388 lbf to 452 lbf depending on user hand position, and 433 lbf in the test fixture position. The same determination could be made for the small cutter.
Based on this calculation, the cut force equation can be rewritten to describe the force applied to the plate (P_CF), using the mechanical advantage (MA) of the cutter: $P_{C F} = ((S1) (a) + C1) {(\frac{w}{h_{\max}})}^{S2} (M A)$
Since P_CF=(CF)(MA), it is readily apparent that this equation is equivalent to the previously described relationship. Using the maximum of the range of mechanical advantages measured for the large cutter, equations A, B, E, and F are can be rewritten as A′, B′, E′ and F′ as shown below. $\begin{matrix} A^{'} . 452 = ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140} (7.1) \\ B^{'} . 391 = ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140} (7.1) \\ E^{'} . 452 = ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124} (7.1) \\ F^{'} . 391 = ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124} (7.1) \end{matrix}$
By similar means, this principle could be applied to the small cutter tested or to any other relevant cutter to determine the maximum severing force seen by a given plate. This method could also be applied to model the cut force of materials other than Grade 2 or Grade 4 commercially pure titanium using the same characteristic equation and similar testing.
The description of the teachings is merely exemplary in nature and, thus, variations that do not depart from the gist of the teachings are intended to be within the scope of the teachings. Such variations are not to be regarded as a departure from the spirit and scope of the teachings.

Claims

1. A device for coupling bone across an osteotomy, comprising:

a plate having at least two bone fixation regions and at least one bridge region, said bridge region having an aspect ratio defining an optimum height and width of said bridge region to accommodate a load applied across the osteotomy and minimize a cut force required to sever said bridge region.

2. The device of claim 1, wherein said at least two bone fixation regions includes at least one aperture.

3. The device of claim 2, wherein the apertures are internally threaded.

4. The device of claim 1, further including a fastening device adapted to engage said bone fixation regions to secure said bone fixation regions to one or more portions of bone,

5. The device of claim 4, wherein said fastening device includes an externally threaded lower shaft portion for engaging the bone, an externally threaded upper shaft portion, and a head member that is internally threaded for engaging said upper shaft portion.

6. The device of claim 5, wherein said head member is externally threaded for engaging one of said internally threaded apertures.

7. The device of claim 5, wherein said fastener includes a flange portion between said lower shaft portion and said upper shaft portion.

8. The device of claim 4, wherein said fastening device is made from a bio-resorbable material.

9. The device of claim 4, wherein said fastening device is made from a bio-compatible material.

10. The device of claim 4, wherein said fastening device includes a pointed end portion.

11. The device of claim 4, wherein said fastening device is self-drilling

12. The device of claim 1, wherein said bridge region spans the osteotomy.

13. The device of claim 1, wherein said bridge region spans the bone.

14. The device of claim 1, wherein said bridge region is longitudinally disposed at an angle relative to at least one of said bone fixation regions.

15. The device of claim 1, wherein said bridge region is longitudinally disposed at an angle relative to two or more of said bone fixation regions.

16. The device of claim 1, wherein an additional bridge region extends from said bridge region, said additional bridge region terminating in an additional bone fixation region.

17. The device of claim 1, wherein an additional bridge region extends from said bone fixation region, said additional bridge region terminating in an additional bone fixation region.

18. The device of claim 1, wherein said at least two bone fixation regions includes an angled portion extending upwardly in a plane of said bridge region.

19. The device of claim 1, wherein said plate includes at least four bridge regions, each of said bridge region coupled to two or more bone fixation regions.

20. The device of claim 19, wherein said bone fixation regions extend angularly from said bridge region.

21. The device of claim 20, wherein said bone fixation regions have at least two apertures.

22. The device of claim 1, wherein said bone fixation region is coupled on one or more ends to one or more intersecting bridge regions.

23. The device of claim 1, wherein said bone fixation regions are coupled on one or more ends to one or more bridge regions, one of said bridge regions defining a common bridge region.

24. The device of claim 1, wherein said bridge region includes multiple bridge regions terminating in bone fixation regions and disposed in a parallel relationship to each other.

25. The device of claim 1, wherein said bone fixation regions include a portion disposed generally linearly with said upper surface and a stepped portion offset from said upper surface.

26. The device of claim 1, wherein said plate includes bio-resorbable material.

27. The device of claim 1, wherein said plate includes bio-compatible material.

28. The device of claim 27, wherein said biocompatible material is an implant grade metal.

29. The device of claim 28, wherein said implant grade metal is selected from among: commercially pure titanium, titanium alloys, stainless steel and zirconium.

30. The device of claim 1, wherein said bridge region includes a height less than about 0.55 times a width of said bone fixation regions.

31. The device of claim 1, wherein said height of said bridge region is greater than about 1.1 times said width of said bone fixation region.

32. The device of claim 1, wherein a maximum distance between a lower surface and an upper surface of said bone fixation region is less than about 0.12 inches.

33. The device of claim 1, wherein said height of said bridge region is less than about 0.055 inches.

34. The device of claim 1, wherein said height and width of said bridge region are given by the following equation, wherein X is said cut force in pounds-force and ‘a’ is the area:

X \geq ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140}

35. The device of claim 34, wherein said cut force X is chosen from a group comprising: 63.7, 55.1, 22.2, and 19.2.

36. The device of claim 34, wherein a cross-section of said bridge region is generally rectangular.

37. The device of claim 1, wherein said height and width of said bridge region are given by the following equation, wherein X is said cut force in pounds-force and ‘a’ is the area:

X \geq ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124}

38. The device of claim 37, wherein said cut force X is chosen from a group comprising: 63.7, 55.1, 22.2, and 19.2.

39. The device of claim 37, wherein a cross-section of said bridge region is generally rectangular.

40. The device of claim 1, wherein a cross-section of said bridge region is generally rectangular.

41. The device of claim 1, wherein said cut force required to sever said bridge region is less than 452 pounds-force.

42. The device of claim 1, wherein said cut force required to sever said bridge region is less than 387 pounds-force.

43. The device of claim 1, wherein said cut force required to sever said bridge region is less than 335 pounds-force.

44. The device of claim 1, wherein said cut force required to sever said bridge region is less than 157 pounds-force.

45. The device of claim 1, wherein said cut force required to sever said bridge region is less than 136 pounds-force.

46. The device of claim 1, wherein said cut force required to sever said bridge region is less than 116 pounds-force.

47. A device for coupling bone across an osteotomy, comprising:

at least two bone fixation regions, said at least two bone fixation regions having an upper surface, a lower surface, and a perimeter surface; and

at least one bridge region having a height and a width, said bridge region generally disposed between said at least two bone fixation regions and offset from at least one of said upper surface, or said lower surface.

48. The device of claim 47, wherein said height and width of said bridge region are given by the following equation, wherein X is said cut force in pounds-force:

X \geq ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140}

49. The device of claim 48, wherein said cut force X is chosen from a group comprising: 63.7, 55.1, 22.2, and 19.2.

50. The device of claim 48, wherein a cross-section of said bridge region is generally rectangular.

51. The device of claim 47, wherein said height and width of said bridge region are given by the following equation, wherein X is said cut force in pounds-force:

X \geq ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124}

52. The device of claim 51, wherein said cut force X is chosen from a group comprising: 63.7, 55.1, 22.2, and 19.2.

53. The device of claim 51, wherein a cross-section of said bridge region is generally rectangular.

54. The device of claim 47, wherein a cross-section of said bridge region is generally rectangular.

55. The device of claim 47, further including a fastening device adapted to engage said bone fixation regions to secure said bone fixation regions to one or more portions of bone, said fastening device adapted to be disposed through apertures formed through said bone fixation regions to secure said bone fixation regions to one or more portions of bone.

56. The device of claim 55, wherein said fastening device is capable of engaging said apertures and securing said bone fixation regions to one or more portions of severed bone.

57. The device of claim 55, wherein said fastening device is includes an externally threaded lower shaft portion for engaging a bone, an externally threaded upper shaft portion, and a head member that is internally threaded for engaging said upper shaft portion.

58. The device of claim 57, wherein said head member is externally threaded for engaging one of said internally threaded apertures.

59. The fastening device of claim 57, wherein said fastener includes a flange portion between said lower shaft portion and said upper shaft portion.

60. The device of claim 55, wherein said fastening device is made from a bio-resorbable material.

61. The device of claim 55, wherein said fastening device is made from a bio-compatible material.

62. The device of claim 55, wherein said biocompatible material is an implant grade metal.

63. The device of claim 62, wherein said implant grade metal is selected from among: commercially pure titanium, titanium alloys, stainless steel and zirconium.

64. The device of claim 55, wherein said fastening device includes a pointed end portion.

65. The device of claim 55, wherein said fastening device is self-drilling.

66. The device of claim 55, wherein said internal apertures are arranged in an asymmetric pattern.

67. The device of claim 55, wherein said apertures are internally threaded.

68. The device of claim 47, wherein one or more of said bridge regions span the osteotomy.

69. The device of claim 47, wherein one or more of said bridge regions span the bone.

70. The device of claim 47, wherein said bridge region is longitudinally disposed at an angle relative at least one of said bone fixation regions.

71. The device of claim 47, wherein said bridge region is longitudinally disposed at an angle relative both of said bone fixation regions.

72. The device of claim 47, wherein an additional bridge region extends from said bridge region, said additional bridge region terminating in a bone fixation region.

73. The device of claim 47, wherein said bone fixation region includes an angled portion extending upwardly in a plane of said bridge region.

74. The device of claim 73, wherein said bone fixation region includes said angled portion and a planar portion generally coplanar with said bridge region.

75. The device of claim 47, wherein the device is comprised of at least four bridge regions with each bridge region coupled to two or more bone fixation regions.

76. The device of claim 75, wherein said bone fixation regions extend angularly from said bridge region.

77. The device of claim 76, wherein said bone fixation regions have at least two apertures.

78. The device of claim 47, wherein said bone fixation regions are coupled on one or more ends to one or more intersecting bridge regions.

79. The device of claim 47, wherein said bone fixation regions are coupled on one or more ends to one or more bridge regions, one of the one or more bridge regions defining a common bridge region.

80. The device of claim 47, wherein said bridge region is multiple bridge regions terminating in bone fixation regions and disposed in a parallel relationship to each other and interconnected by a backbone.

81. The device of claim 47, wherein said bone fixation regions include a portion disposed generally linearly with said bridge region and a stepped portion offset from said linear portion.

82. The device of claim 47, wherein said bridge region and said bone fixation regions include bio-resorbable material.

83. The device of claim 47, wherein said bridge region and said bone fixation regions bio-compatible material.

84. The device of claim 47, wherein said cut force required to sever said bridge region is less than 452 pounds-force.

85. The device of claim 47, wherein said cut force required to sever said bridge region is less than 387 pounds-force.

86. The device of claim 47, wherein said cut force required to sever said bridge region is less than 335 pounds-force.

87. The device of claim 47, wherein said cut force required to sever said bridge region is less than 157 pounds-force.

88. The device of claim 47, wherein said cut force required to sever said bridge region is less than 136 pounds-force.

89. The device of claim 47, wherein said cut force required to sever said bridge region is less than 116 pounds-force.

90. A method comprising:

determining a load applied across separated bone regions;

determining a cross-sectional area of a bridge region of a plate secured to said separated bone regions, said cross-sectional area capable of withstanding said determined load;

determining an acceptable cut force for said bridge region; and

calculating an aspect ratio to determine an optimum height and width of said bridge region to accommodate said load applied across the bone regions and said cut force required to sever said bridge region.

91. The method of claim 90, further comprising providing a bone reapproximation device to laterally hook and reapproximate the separated bone regions prior to applying said plate.

92. The method of claim 90, further comprising fastening the bone coupling device to the reapproximated bone regions using a fastener.

93. The device of claim 90, wherein calculating said aspect ratio is performed by the following equation, wherein X is said cut force in foot-lb:

X \geq ((1.30 \times 10^{4}) (a) + 8.76) {(\frac{w}{h_{\max}})}^{- 0.140}

94. The device of claim 93, wherein calculating said aspect ratio includes choosing said cut force X from a group comprising: 63.7, 55.1, 22.2, and 19.2.

95. The device of claim 93, wherein calculating said aspect ratio is performed by the following equation, wherein X is said cut force in pounds-force:

X \geq ((1.224 \times 10^{4}) (a) + 3.68) {(\frac{w}{h_{\max}})}^{- 0.124}

96. The device of claim 95, wherein calculating said aspect ratio includes choosing said cut force X from a group comprising: 63.7, 55.1, 22.2, and 19.2.