U.S. patent application number 10/013328 was filed with the patent office on 2003-01-30 for materials and methods for improved bone tendon bone transplantation.
Invention is credited to Carter, Diane, Carter, Kevin C., Ferguson, Richard.
Application Number | 20030023304 10/013328 |
Document ID | / |
Family ID | 26684708 |
Filed Date | 2003-01-30 |
United States Patent
Application |
20030023304 |
Kind Code |
A1 |
Carter, Kevin C. ; et
al. |
January 30, 2003 |
Materials and methods for improved bone tendon bone
transplantation
Abstract
Disclosed herein is an improved Bone Tendon Bone graft for use
in orthopedic surgical procedures. Specifically exemplified herein
is a Bone Tendon Bone graft comprising one or more bone blocks
having a groove cut into the surface thereof, wherein said groove
is sufficient to accommodate a fixation screw. Also disclosed is a
porcine bone tendon bone graft for use in orthopedic procedures.
Also disclosed are multiple embodiments of assembled bone tendon
bone blocks for use in orthopedic surgeries. Additionally, a method
of harvesting grafts that has improved efficiency, increases the
quantity of extracted tissue and minimizes time required by surgeon
for implantation is disclosed.
Inventors: |
Carter, Kevin C.; (Alachua,
FL) ; Ferguson, Richard; (Alachua, FL) ;
Carter, Diane; (Gainesville, FL) |
Correspondence
Address: |
McAndrews, Held & Malloy, Ltd.
500 West Madison Street, #34
Chicago
IL
60661
US
|
Family ID: |
26684708 |
Appl. No.: |
10/013328 |
Filed: |
November 5, 2001 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10013328 |
Nov 5, 2001 |
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09481319 |
Jan 11, 2000 |
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09481319 |
Jan 11, 2000 |
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09528034 |
Mar 17, 2000 |
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09528034 |
Mar 17, 2000 |
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09924110 |
Aug 7, 2001 |
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Current U.S.
Class: |
623/13.14 ;
623/13.17 |
Current CPC
Class: |
A61F 2002/0882 20130101;
A61B 17/1635 20130101; A61F 2002/0829 20130101; A61F 2002/2839
20130101; A61B 2217/007 20130101; A61F 2002/087 20130101; A61F
2002/0858 20130101; A61F 2002/4649 20130101; A61B 17/1637 20130101;
A61F 2/0811 20130101; A61F 2/08 20130101 |
Class at
Publication: |
623/13.14 ;
623/13.17 |
International
Class: |
A61F 002/08 |
Claims
What is claimed:
1. An assembled bone tendon bone graft useful in orthopedic surgery
comprising one or more assembled blocks and a tendon affixed to
said one or more assembled blocks.
2. The assembled bone tendon bone graft of claim 1, wherein said
one or more blocks comprise segments of cortical bone, cancellous
bone, cortico-cancellous bone, or combinations thereof, wherein
said bone segments are mineralized or partially or fully
demineralized; or wherein said one or more blocks comprise segments
of a synthetic material; or combinations of bone and synthetic
material.
3. The assembled bone tendon bone graft of claim 2, wherein said
tendon is derived from an Achilles tendon, patellar tendon, or
quadriceps tendon of a donor, or other tendon or ligament from a
donor, or is comprised of a synthetic material.
4. The assembled bone tendon bone graft of claim 3, wherein said
one or more blocks are shaped into a dowel, wherein said dowel
comprises an interior and an exterior.
5. The assembled bone tendon bone graft of claim 4, wherein said
exterior comprises at least one graft manipulation hole.
6. The graft of claim 5, wherein said exterior comprises a grove
sufficient to accommodate an interference screw.
7. The assembled bone tendon bone graft of claim 6, wherein said
interior comprises a proximal receiving chamber and a distal
fixation chamber, wherein said fixation chamber comprises a chamber
having first and second fasteners to retain a tendon placed
therein.
8. The assembled bone tendon bone graft of claim 6, wherein said
first and second fasteners are first and second dowel shaped
rollers.
9. The assembled bone tendon bone graft of claim 8, wherein said
first and second rollers are different is size.
10. The assembled bone tendon bone graft of claim 9, wherein one of
said first and second rollers is fixed in place.
11. The assembled bone tendon bone graft of claim 10, wherein one
of said first and second rollers is movable.
12. The assembled bone tendon bone graft of claim 11, wherein a
terminal portion of said tendon is looped around said first and
second rollers in opposing directions such that said first and
second rollers form a cam over locking arrangement to restrict
movement of said tendon.
13. The assembled bone tendon bone graft of claim 12, wherein said
tendon is impregnated with bone chips.
14. The assembled bone tendon bone graft of claim 13, wherein said
bone chips are particles of cortical bone, cancellous bone,
cortico-cancellous bone or combinations thereof.
15. The assembled bone tendon bone graft of claim 14, wherein said
bone chips increase friction between said tendon and said first and
second rollers to reduce tendon movement.
16. The assembled bone tendon bone graft of claim 15, wherein said
bone chips promote attachment of tendon to bone.
17. The assembled bone tendon bone graft of claim 16, wherein said
tendon impregnated with bone chips is inserted through said
proximal receiving chamber and into said distal fixation chambers
for fixation to said rollers.
18. The assembled bone tendon bone graft of claim 17, wherein said
fixation of said tendon impregnated with bone chips comprises
looping said tendon around said first and second rollers in
opposite directions such that a cam over affect is achieved to lock
said tendon in place between said rollers, and wherein said bone
chips become positioned between said rollers and said tendon to
increase friction between said rollers and said tendon thereby
further restricting movement of said tendon.
19. The assembled bone tendon bone graft of claim 18, wherein said
bone block comprises two or more separable segments.
20. The assembled bone tendon bone graft of claim 19, wherein said
segments are held together through insertion of a one or more press
pins between said two or more segments.
21. The assembled bone tendon bone graft of claim 20, wherein said
pins are segments cortical bone, cancellous bone,
cortico-cancellous bone or combinations thereof.
22. The assembled bone tendon bone graft of claim 21, wherein said
two or more separable segments are machined such that when joined
together a single bone graft is created having an interior distal
fixation chamber and an interior proximal receiving chamber,
wherein said distal fixation chamber contains first and second
rollers for fixing a tendon in place.
23. The assembled bone tendon bone graft of claim 4, wherein said
interior comprises an inclined distal fixation chamber and a
proximal receiving chamber.
24. The assembled bone tendon bone graft of claim 23, wherein said
inclined distal fixation chamber is partially threaded to
accommodate a modified interference screw.
25. The assembled bone tendon bone graft of claim 24, wherein said
modified interference screw has smooth threads.
26. The assembled bone tendon bone graft of claim 25, wherein said
inclined plane of said distal fixation chamber produces a space
between said interference screw placed in said fixation chamber and
a wall of said fixation chamber, such that said fixation chamber
may accommodate a portion of said tendon and said modified
interference screw without significantly increasing wall load on
said graft.
27. The assembled bone tendon bone of claim 26, wherein said
exterior comprises a groove sufficient to accommodate a fixation
screw.
28. The assembled bone tendon bone graft of claim 27, wherein said
exterior comprises at least one graft manipulation hole.
29. The assembled bone tendon bone graft of claim 28, wherein said
exterior comprises a ported window.
30. The assembled bone tendon bone graft of claim 29, wherein said
tendon is inserted through said proximal receiving chamber and into
said distal fixation chamber such that upon insertion of said
modified interference screw into said distal chamber, said tendon
is captured and fixed between said screw and a wall of said distal
fixation chamber, and wherein a portion of said tendon protrudes
through said ported window and contacts canal bone to promote blood
flow and attachment.
31. The assembled bone tendon bone graft of claim 4, wherein said
bone block graft is shaped into a dowel having an interior and an
exterior, wherein said interior comprises a proximal receiving
chamber and a distal fixation chamber having a positional
encapsulated locking key.
32. The assembled bone tendon bone graft of claim 31, wherein the
top of said positional encapsulated locking key is tapered such
that it declines in the direction of the receiving chamber.
33. The assembled bone tendon bone graft of claim 32, wherein said
top of said positional encapsulated locking key is machined to form
multiple angled saw tooth ridges.
34. The assembled bone tendon bone graft of claim 33, wherein said
positional encapsulated key slides out of said bone block to unlock
said block, and slides into said bone block to lock in place
material placed into said block.
35. The assembled bone tendon bone graft of claim 34, wherein said
exterior comprises a ported window.
36. The assembled bone tendon bone graft of claim 35, wherein said
tendon is inserted through said proximal receiving chamber into
said distal fixation chamber for interface with said positional
encapsulated key, such that said ridges on said positional
encapsulated locking key interface with said tendon to fasten said
tendon inside said graft when said positional encapsulated locking
key is slid into said locking position.
37. The assembled bone tendon bone graft of claim 36, wherein said
interface between said tendon and said encapsulated locking key
forces a section of said tendon through said ported window thereby
permitting contact between said tendon and canal bone to promote
blood flow and attachment.
38. The assembled bone tendon bone graft of claim 37, wherein said
interface between said tendon and said encapsulated locking key
places minimal load on said bone block during loading.
39. The assembled bone tendon bone graft of claim 4, wherein said
graft comprises a single bone block machined to form an exterior
groove to accommodate a portion of a tendon placed thereon.
40. The assembled bone tendon bone graft of claim 39, wherein said
exterior groove comprises at least one graft manipulation hole.
41. The assembled bone tendon bone graft of claim 40, wherein said
single bone block is segmented into upper and lower halves.
42. The assembled bone tendon bone graft of claim 41, wherein said
upper and lower halves are joined together through insertion of one
or more press pins between said upper and lower halves.
43. The assembled bone tendon bone graft of claim 42, wherein said
tendon is folded and looped around said bone block such that a
portion of said tendon rests on the upper and lower halves of said
bone block leaving two trailing sections of tendon for fixation at
a remote site.
44. The assembled bone tendon bone graft of claim 43, wherein said
tendon is is connected to said tendon by one or more sutures.
45. The assembled bone tendon bone graft of claim 44 wherein said
sutures are welded sutures.
46. The assembled bone tendon bone graft of claim 44, wherein said
one or more sutures permit movement of said tendon, such that when
said trailing edges of said tendon are fixed at said remote site, a
pulley affect is achieved that allows natural cyclic creep of said
tendon under said sutures.
47. The assembled bone tendon bone graft of claim 46, wherein said
natural cyclic creep balances mechanical forces on both ends of the
tendon.
48. The assembled bone tendon bone graft of claim 47, wherein said
looping and use of said natural cyclic creep provides mechanical
advantage to said bone graft by increasing the tensile strength of
said tendon, and reducing shear on said tendon.
49. The assembled bone tendon bone graft of claim 48, wherein said
looping of said tendon permits normal stretching and eliminates
crimping of the collagen backbone of said tendon, thereby reducing
failure.
50. The assembled bone tendon bone graft of claim 48, wherein
looping permits use of semitendinosus, gracilis, or hamstring
tissue in anterior or posterior cruciate ligament repair.
51. The assembled bone tendon bone graft of claim 2, wherein said
synthetic segment is comprised of stainless steel, titanium, cobalt
chromium-molybdenum alloy, and a plastic of one or more members
selected from the group consisting of nylon, polycarbonate,
polypropylene, polyacetal, polyethylene oxide and its copolymers,
polyvinylpyrolidone, polyacrylates, polyesters, polysulfone,
polylactide, poly(L-lactide) (PLLA), poly(D,L-lactide) (PLA),
poly(glycolide) (PGA), poly(L-lactide-co-D,L-Lactide) (PLLA/PLA),
poly(L-lactide-co-glycolide) (PLA/PGA),
poly(glocolide-co-trimethylene carbonate) (PGA/PTMC), polydioxanone
(PDS), polycaprolactone (PCL), polyhydroxybutyrate (PHBT),
poly(phosphazenes), poly(D,L-lactide-co-caprolactone) (PLA/PCL),
poly(glycolide-co-caprolactone) (PGA/PCL), poly(phosphase ester),
polyanhydrides, polyvinyl alcohol, hydrophilic polyurethanes, and a
combination of one or more bioabsorbable polymers.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation in part of copending
application Ser. No. 09/924,110, filed Aug. 7, 2000 which is a
continuation in part of copending application Ser. No. 09/528,034,
filed Mar. 17, 2000, which is a continuation in part of copending
application Ser. No. 09/481,319, filed Jan. 11, 2000. The benefit
of priority under 35 USC .sctn.120 is claimed for foregoing
applications.
BACKGROUND OF THE INVENTION
[0002] Orthopedic medicine is increasingly becoming aware of the
vast potential and advantages of using bone/tendon/bone grafts to
repair common joint injuries, such as Anterior Cruciate Ligament
(ACL) or Posterior Cruciate Ligament (PCL) tears. One technique
that is currently used for repairing these types of injuries
involves surgically reconnecting the torn portions of a damaged
ligament. However, this technique is often not possible, especially
when the damage to the ligament is extensive. To address situations
where the damage to the joint ligaments is severe, another
technique commonly performed involves redirecting tendons to
provide increased support to a damaged knee. These conventional
techniques are not without their shortcomings; in most cases, the
repaired joint lacks flexibility and stability.
[0003] The recent utilization of bone/tendon grafts has
dramatically improved the results of joint repair in cases of
severe trauma. Even in cases of extensive damage to the joint
ligaments, orthopedic surgeons have been able to achieve 100
percent range of motion and stability using donor bone/tendon
grafts.
[0004] Despite these realized advantages, there have been some
difficulties encountered with utilizing bone/tendon grafts. For
example, surgical procedures involving transplantation and fixation
of these grafts can be tedious and lengthy. Currently,
bone/tendon/bone grafts must be specifically shaped for the
recipient during surgery, which can require thirty minutes to over
an hour of time. Further, surgeons must establish a means of
attaching the graft, which also takes up valuable surgery time.
[0005] Another difficulty associated with using bone/tendon grafts
is that there is a limited supply and limited size range available.
This can result in a patient having to choose an inferior procedure
simply based on the lack of availability of tissue. Accordingly,
there is a need in the art for a system that addresses this and the
foregoing concerns.
SUMMARY OF THE INVENTION
[0006] The subject invention concerns a novel bone tendon bone
graft (BTB) that facilitates an easier and more efficient surgery
for reconstructing ligaments in a joint. One aspect of the subject
invention pertains to a BTB that comprises a tendon and two bone
blocks positioned at opposite ends of the tendon, wherein the bone
blocks are pre-shaped for uniform and consistent alignment into a
recipient bone.
[0007] In a specific aspect, the subject invention pertains to a
bone tendon bone graft useful in orthopedic surgery comprising one
or more bone blocks, and a tendon attached to said one or more bone
blocks; wherein said one or more bone blocks is cut to provide a
groove sufficient to accommodate a fixation screw. Alternatively,
the subject invention pertains to a bone tendon bone graft useful
in orthopedic surgery comprising one or more bone blocks and a
tendon attached to said one or more bone blocks, wherein said one
or more bone blocks is pre-shaped into a dowel.
[0008] A further aspect of the subject invention pertains to a
method of obtaining a plurality of bone tendon bone grafts
comprising excising a first bone plug having attached thereto a
tendon or ligament; and excising a second bone plug having attached
thereto a tendon or ligament; wherein said first bone plug and said
second bone plug are derived from contiguous bone stock and overlap
such that excision of said first bone plug or said second bone plug
forms a groove in the bone plug that is excised subsequent to the
other.
[0009] Another aspect of the subject invention pertains to a BTB
that comprises a tendon and one bone block, wherein the tendon is
looped around a bone to create a tendon, bone, tendon layer held in
place with sutures, and having two trailing portions of the tendon
available for fixation at a remote location. This embodiment takes
advantage of the natural cyclic creep associated with tendon
movement to balance opposing forces in a pulley type fashion. This
can increase tissue strength while decreasing shear that may cause
tissue failure.
[0010] In yet another aspect, the subject invention pertains to a
method of conducting orthopedic surgery on a human or an animal
comprising obtaining a bone tendon bone graft, said graft
comprising a tendon or ligament having two ends, and one or more
bone blocks attached to said tendon or ligament, wherein at least
one of said one or more bone blocks has a groove suitable for
accommodating a fixation screw.
[0011] An alternative aspect of the invention pertains to an
implant comprising a bone block and a tendon, wherein the bone
block comprises a groove for accommodating a fixation screw.
[0012] Yet a further aspect of the invention pertains to a BTB
having one or more segments that may be assembled to create
different sized bone blocks.
[0013] Yet a further aspect of this invention pertains to a BTB
that permits use of different types of tendons for ACL and PCL
repair.
[0014] Yet a further aspect of the subject invention pertains to a
BTB core cutter for harvesting BTB grafts in accordance with the
principles of the subject invention.
[0015] Further still, another aspect of the subject invention
pertains to a BTB obtained from xenogenic sources. Preferred
sources include, but are not limited to, porcine, bovine, goat and
equine.
[0016] These and other advantageous aspects of the subject
invention are described in further detail below.
DETAILED DESCRIPTION OF THE DRAWINGS
[0017] FIG. 1 shows an embodiment of a BTB having a groove with a
thread profile disposed thereon.
[0018] FIG. 2 shows a side view of three different embodiments of
BTBs in accordance with the subject invention.
[0019] FIG. 3 depicts a frontal view of a donor area for harvesting
BTBs in accordance with the teachings herein.
[0020] FIG. 4 is a depiction of another embodiment of the invention
illustrating a reconstruction of an injured area through
implantation of a BTB in accordance with the teachings herein.
[0021] FIG. 5 shows a side view of a BTB core cutter of the subject
invention designed for harvesting BTB grafts.
[0022] FIG. 6A shows a close up view of a teeth configuration that
is less desired for use with the subject invention.
[0023] FIG. 6B shows a close up view of a preferred embodiment of
the teeth of the embodiment shown in FIG. 5.
[0024] FIG. 7 is a blown up view of the circled region as shown in
FIG. 5.
[0025] FIG. 8 is three dimensional side view of a further
embodiment of the subject BTB that comprises one block that is
tapered on both ends.
[0026] FIG. 9A is a photograph showing the posterior side of a
single porcine Bone Tendon Bone graft traditionally cut and not
pre-shaped. The longer bone is the tibia and the shorter bone is
the patella. The tendon is also shown.
[0027] FIG. 9B is a photgraph showing the anterior view of the
porcine BTB shown in FIG. 9A. The tibia is on the left and the
patella is on the right.
[0028] FIG. 9C is a side view of the porcine BTB shown in FIG. 9A
to show the thickness of the tendon. The patella is shown on the
left and the tendon is shown on the right.
[0029] FIG. 10A is a side cross-sectional view of a solid Looped
Locking Assembled BTB bone block.
[0030] FIG. 10B is a three dimensional side view of a solid Looped
Locking Assembled BTB bone block showing a distal opening into a
distal interior fixation chamber.
[0031] FIG. 10C is a three dimensional side view of a solid Looped
Locking Assembled BTB bone block showing a proximal opening into a
proximal interior receiving chamber.
[0032] FIG. 10D is a side cross-sectional view of a solid Looped
Locking Assembled BTB bone block with tendon inserted.
[0033] FIG. 11A is a three dimensional view of a segmented Looped
Locking Assembled BTB bone block.
[0034] FIG. 11B is a view of one section of a segmented Looped
Locking Assembled BTB bone block showing first and second
fasteners.
[0035] FIG. 11C is one half of a segmented Looped Locking Assembled
BTB bone block cut longitudinally to reveal contours interior
fixation and receiving chambers.
[0036] FIG. 11D is a distal section of a segmented Looped Locking
Assembled BTB bone block showing rectangular opening of distal
fixation chamber and holes for pins.
[0037] FIG. 11E is one proximal section of a segmented Looped
Locking Assembled BTB bone block showing a circular opening for
receipt of a tendon and holes for pins.
[0038] FIG. 11F is a side cross-sectional view of a segmented
Looped Locking Assembled BTB bone block with tendon inserted.
[0039] FIG. 12A shows a side cross-sectional view of a Solid Screw
Wedge Assembled BTB bone block with modified interference screw
partially inserted.
[0040] FIG. 12B shows a side cross-sectional view of a Solid Screw
Wedge Assembled BTB bone block showing partially a threaded portion
and a smooth portion of the distal chamber.
[0041] FIG. 12C is a side cross-sectional view of a Solid Screw
Wedge Assembled BTB bone block with the screw completely threaded
into cavity and showing gap between the block and the screw.
[0042] FIG. 12D is a side view of Solid Screw Wedge Assembled BTB
bone block with the screw completely out showing a screw head
shaped for ratcheting.
[0043] FIG. 12E is an angled front view of the Solid Screw Wedge
Assembled BTB bone block with a screw completely out and showing
the space between the screw and the block created by the inclined
plane.
[0044] FIG. 12F is an angled front view of the Solid Screw Wedge
Assembled BTB bone block with a screw inserted showing space
between screw and block created by inclined plane.
[0045] FIG. 12G is a side view of the screw used in the Solid Screw
Wedge Assembled BTB bone block showing the smooth edges.
[0046] FIG. 13A is side view of a Solid Screw Wedge Assembled BTB
bone block having a ported window not blocked by a screw.
[0047] FIG. 13B is side view of a Solid Screw Wedge Assembled BTB
bone block having a ported window partially blocked by a screw.
[0048] FIG. 13C is an angled side view of a Solid Screw Wedge
Assembled BTB bone block showing an orifice to receive a
tendon.
[0049] FIG. 14A is a three dimensional cross-sectional view of a
Key Wedge Assembled BTB bone block showing the key in an unlocked
position.
[0050] FIG. 14B is a three dimensional cross-sectional view of a
Key Wedge Assembled BTB bone block showing the key in a locked
position.
[0051] FIG. 14C is a three dimensional front view of a Key Wedge
Assembled BTB bone block showing the key in the unlocked position
and unobstructed ported window.
[0052] FIG. 14D is an angled front view of a Key Wedge Assembled
BTB bone block showing an orifice to receive a tendon.
[0053] FIG. 14E is an angled front view of a Key Wedge Assembled
BTB bone block with the key in a locked position and a partially
obstructed ported window.
[0054] FIG. 15A is an exploded view of an assembled segmented
looped pulley bone tendon showing all component parts including
solid sutures.
[0055] FIG. 15B is an exploded view of an assembled segmented
looped pulley bone tendon showing all component parts including an
open sutures.
[0056] FIG. 15C shows an assembled segmented looped pulley bone
tendon having an open suture design.
[0057] FIG. 15D shows an assembled segmented looped pulley bone
tendon having an closed suture design.
DETAILED DISCLOSURE OF THE INVENTION
[0058] Referring to FIG. 1, there is shown an embodiment directed
to a BTB 100 comprising a first bone block 110 and a second bone
block 120 interconnected by a tendon 130, wherein each bone block
has been pre-shaped into dowels. The term "tendon" as used herein
is intended in its broad sense and refers to fibrous connective
tissue for use in grafts, such as, but not limited to, tendons,
ligaments and demineralized bone. The terms "BTB" or "bone tendon
bone graft" as used herein refer to a graft implant that comprises
one or more tendon portions and one or more bone portions. The BTB
is preferably isolated from the knee of a donor. However, in view
of the teachings herein, those skilled in the art will readily
appreciate that other areas of the body are suitable, albeit less
preferred, for harvesting BTBs according to the subject invention,
such as, but not limited to, the Achilles tendon/calcaneus region
or shoulder region. In addition to BTBs having a tendon portion
derived from naturally occurring tendon or ligament harvested from
a donor, other examples of suitable implants would be readily
appreciated by those skilled in the art, such as, but not limited
to, segmentally demineralized bone (International Pub. No.
WO/99/21515). In a more preferred embodiment, one of the bone
blocks is derived from the patella while the other is derived from
the end of the tibia, and the tendon is derived from the patellar
tendon.
[0059] To facilitate placement of a fixation screw, the dowels are
preferably machined down the length of the bone block to form
radius cuts 115, 125. The radius cuts 115, 125 aid in the
attachment of the graft to recipient bone because they provide a
groove to position a fixation screw, which results in increased
surface area at the contact between the bone block and the screw.
The radius cuts 115, 125 provide the additional advantage of
increasing the pull out loads of the bone block, as well as filling
of "dead" space in the tunnel.
[0060] Fixation methods known in the art can be used in accord with
the principles of the subject invention, which include, but are not
limited to, staples, buttons, screw and washer, interference
screws, and self-taping screws. In a preferred embodiment, fixation
is accomplished by interference screws and/or self-taping screws.
In an even more preferred embodiment, the radius cuts 115, 125
contain a thread profile 135 that matches the thread profile of the
fixation screw, thereby further increasing the stability of
fixation.
[0061] Referring now to FIG. 2, three different embodiments of the
subject BTBs are shown. FIG. 2A shows an embodiment that comprises
a basic configuration of the subject BTBs. Bone blocks 210 and 220
are in a pre-shaped dowel form with no groove thereon, and are
connected by tendon 100. FIG. 2B shows another version of the BTB,
wherein the bone blocks are pre-shaped into dowels with tapered
ends. Bone block 212 is a dowel that has a proximal tapered region
216 in relation to tendon 200, and bone block 214 is pre-shaped
into a dowel that has a distal tapered region 218 in relation to
tendon 200. FIG. 2C illustrates a preferred version of the
invention, which has a bone block 230 with a proximal tapered
region 239 and a groove 238 positioned on the bone block 230. This
version also comprises a second bone block 234 with a distal
tapered region and a groove 236 positioned on bone block 234 as
well. The embodiments shown in FIGS. 2B-C are tapered such that
implantation into a pre-formed tunnel in recipient bone is
preferred to occur in the direction of the arrow (see also FIG.
4).
[0062] Referring to FIG. 3, an illustration of a donor area 300 is
depicted, wherein three separate grafts 335, 345, and 355 are
harvested. As shown, the three different grafts individually have
at least one bone block 330, 340, and 350. While the sequence of
harvesting the grafts is not critical, preferably, graft 335 is
excised first, followed by excision of the outside grafts 345, 355.
Excising graft 335 first results in the automatic cut in the other
donor areas, thereby producing a groove in the bone blocks 340, 350
of the other grafts upon excision. In a preferred embodiment, the
donor area is located at the top of the Tibia at the insertion of
the patellar tendon 320. In an even more preferred embodiment, the
donor area extends the length of the patellar tendon to the
patella, wherein bone blocks are excised from the patella.
[0063] The bone blocks can be extracted with the use of
conventional tools and protocols routinely practiced in the art,
such as core cutter and hole saws. In a preferred embodiment, the
bone blocks can be extracted through the use of a BTB bone cutter
according to the teachings further described below.
[0064] The extracted bone blocks 330, 340, and 350 are generally
shaped like a plug or dowel and are preferably further shaped by
machining through conventional methods known in the art. In a
specific embodiment the dowel is machined into dimensions suitable
for various surgical procedures. The machining is preferably
conducted on a graduated die, a grinding wheel, a lathe, or
machining tools may be specifically designed and adapted for this
purpose in view of the teachings herein. Preferred dimensions for
the dowels include 8 mm, 9 mm, 10 mm, 11 mm, and 12 mm in diameter.
Reproducibility of the product dimensions is an important feature
for the successful use of such grafts in the clinical setting.
[0065] In a specific embodiment, the subject invention is directed
to a method of repairing an injured cruciate ligament in the knee
involving the implantation of a BTB. FIG. 4 illustrates this
procedure, and shows a femur 400 and tibia 410 having tunnels
formed therein, 466 and 462, respectively, for receiving BTB 430,
which comprises two bone blocks 432 and 434 connected by tendon
433. To aid in guiding the BTB 430 through tunnel 462, sutures 460
are optionally engaged to bone block 432, which allow a surgeon to
pull the BTB 430 through tunnel 462 where the sutures 460 can then
be removed. Once the BTB 430 is properly situated in tunnels 462
and 466, the BTB 430 is secured in the recipient bone by
interference screws 440. The interference screws 440 are preferably
self taping and are engaged by rotation in the space between
grooves 438 and 436 and the inner walls of tunnels 466 and 462,
respectively. In an even more preferred embodiment, the BTB can be
pre-marked with alignment markings. Such markings can be positioned
on the BTB to aid the surgeon in visualizing the depth of the BTB
in the tunnels formed for receiving the BTB, as well as visualizing
bone ligament junctions and rotation of the BTB.
[0066] Referring now to FIGS. 5-7, another embodiment of the
subject invention is shown that is directed to a BTB harvesting
device, such as core cutter 500 that comprises a shaft 502 having a
first end 503 and a second end 505. The first end 503 of the shaft
502 preferably has a cavity 501 longitudinally disposed thereon,
which is designed for engaging a drill, such as by insertion of a
Jacob's chuck attached to a power drill (e.g., Dupuy). The second
end 505 of the shaft 502 can be attached to a first end 512 of a
hollow cylinder 504. The second end 514 of the cylinder 504
preferably has teeth 510 disposed thereon. In a preferred
embodiment the cylinder has at least one slot 506 disposed on its
surface to aid in the removal of the cut graft tissue from the core
cutter 500. The slot 506 also provides a means to wash the graft
during the extraction procedure to thereby decrease the chance of
frictional burning of the graft. In a preferred embodiment, the
shaft 502 is approximately 90 mm in length, the cylinder 504 is
approximately 50 mm in length, and the slot 506 is approximately 30
mm in length. In an even more preferred embodiment, the first end
of the hollow cylinder 512 has a chamfered portion 522 which angles
down to the shaft 502.
[0067] A blown up view of the core cutter teeth 510 is illustrated
in FIG. 6. It is preferred that the radius of the teeth A and rake
angle of the teeth B ( also referred to as a bottom angle) are of
appropriate values as to avoid failure (e.g. bending or breaking)
of the teeth, as well as undesired damage to the graft. For
example, FIG. 6A shows an unacceptable tooth pattern wherein the
radius A and bottom angle B are too large, resulting in
insufficient support structure for the tooth and inevitable
failure. According to the subject invention, a core cutter having a
diameter of approximately 10-11 mm preferably has approximately 14
teeth, with a tooth radius A of approximately 20-30 mm (25 mm being
more preferred) and a bottom angle B of approximately 10-20 degrees
(15 degrees being more preferred). For core cutters designed for
smaller or larger bone blocks, the foregoing dimensions are
preferably maintained, while the number of teeth are appropriately
decreased or increased. In a preferred embodiment, the number of
teeth are decreased or increased by two for every millimeter below
or above, respectively, the 10-11 mm cylinder diameter. For
example, a core cutter having a 12 mm cylinder diameter would
preferably have about 16 teeth.
[0068] A blown up view of an end section (circle shown in FIG. 5)
of the cylinder 504, is shown in FIG. 7, which illustrates a
preferred embodiment of the cylinder 504 wherein the internal
diameter (ID) is decreased slightly by adding a relief thickness
520 to the inner surface of the cylinder 504. This embodiment
provides an additional convenience when using a size gauging device
(e.g. ring) for selecting extracted bone blocks that are within
desired parameters. For example, the selection of a BTB through a
10 mm sized gauging device would preferably require the BTB to be a
slight fraction smaller in diameter than the gauging device,
otherwise any insignificant irregularity in the shape of the BTB
might cause it to fail to pass through the gauging device. The
relief thickness 520 decreases the ID of the cylinder 504, thereby
effectuating this slight modification to the BTB.
[0069] Shown in FIG. 8 is a further embodiment 800 of the subject
BTB that is especially adapted for implantation during knee
surgery, wherein the implantation and securement of the BTB is
bi-directional. BTB embodiment 800 comprises one bone block portion
810 and one tendon portion 820. A preferred area from which
embodiment 800 is harvested would be the heel, thigh, or shoulder.
More preferably, the area from which embodiment 800 is harvested is
the heel or thigh, whereby tendon portion 820 is derived from an
Achilles tendon or quadriceps tendon of a donor. The bone block
portion 810 comprises two ends 812 and 814 which both comprise a
tapered region 816 and 818, respectively. The presence of the two
tapered regions 812 and 814 allows for the BTB embodiment 800 to be
inserted and secured bi-directionally, which means, for example,
implantation in either the tibial 462 or femoral 466 tunnels as
discussed above in reference to the method diagrammed in FIG. 4. Of
course, the site of implantation could be approached from a
superior point of entry, i.e., establishing a through-tunnel in the
femur as opposed to the tibia; BTB embodiment 800 would be suitable
for securement in either tunnels in such alternative procedure as
well. Further, the bone block 810 can be provided with a groove 850
to aid in the securement of the implant. In addition, during
implantation, it may be desirable to have a means for manipulating
the implant, such as by sutures or graft insertion tools.
Accordingly, BTB embodiment 800 is provided with preformed graft
manipulation holes 852 and 854 for receiving a suture and/or graft
insertion tools. By way of example of illustrating the orientation
of the graft manipulation holes, holes 852 and 854 are shown as
being vertical or horizontal, respectively, to the axis of the bone
block 810. The preformed graft manipulation holes can be made by
conventional methods, such as by drilling. Appropriate tools for
insertion into preformed holes 852 and 854 will easily be
appreciated by those skilled in the art. Preferably, the graft
insertion tool(s) used comprise an end having a shape and size
suitable for insertion into the graft manipulation holes.
[0070] A BTB obtained from a pig knee according to the disclosed
method is shown in FIGS. 9A, 9B and 9C. The BTB is traditionally
cut and not pre-shaped. FIG. 9A shows a posterior view of the BTB
graft generally indicated at 900 comprising a section of tibia bone
901 bone, and a section of patella bone 902 connected together by a
patella tendon 903. FIG. 9B shows the same graft from an anterior
perspective showing the tibia bone 901, patella bone 902 and tendon
903. FIG. 9C is a picture of the BTB of FIG. 9A from the side to
demonstrate the thickness of the tendon 903 between the tibia bone
901 and patella bone 902.
[0071] In alternate embodiments assembled bone blocks for use in
BTB's is presented. FIG. 10A shows a side cross sectional view of a
Looped Locking Buckle assembled BTB bone block generally
represented at 1000. The block has solid exterior 1001 and an
interior having multiple compartments to accommodate and hold in
place a tendon placed therein. An interior receiving chamber 1002
funnels down to an interior fixation chamber opening 1003 leading
to an interior fixation chamber 1004. A first fastener device 1005
and a second fastener device 1006 are situated such that one of the
fasteners is fixed longitudinally and laterally while the other
fastener is allowed to rock over it. Preferably each fastener
device is a dowel shaped roller with one dowel being larger that
the other. Ideally the smaller fastener has a diameter of
approximately 2.7 mm and a length of approximately 6 mm, while the
larger fastener has a diameter of approximately 3.3 mm and a length
of approximately 6 mm. The size of the fasteners may vary depending
upon the particular application and dimensions of the bone block.
FIG. 10B shows a "look through" view of the bone block taken from
the side to show all components in three dimensions and showing a
distal opening 1007 that allows access to said tendon when placing
it over the fastener. FIG. 10C is an angled front "look through"
view in three dimensions showing a proximal opening 1008 for
insertion of a tendon of other tissue. FIG. 10D shows a side
cross-sectional view of the bone block with a tendon retained
therein. A tendon 1020 is inserted into the proximal opening of the
bone block, and into a receiving chamber 1002 and into the interior
fixation chamber 1004 The tendon is squeezed down to a smaller
diameter and then spread flatly around a first fastener device 1005
and then around a second fastener device 1006. One of the fasteners
devices is fixed longitudinally and laterally while the other is
allowed to rock over it. Because the fixation devices are of
different sizes, at the point of highest tension, the fixation
devices create a cam over-locking arrangement to hold the tendon in
place. It is also preferable to impregnate the tendon with small
cancellous chips 1030. As the tendon is pulled, the cancellous
chips pack around the tendon giving additional grip to the surface
of the fastener device and become tiny breaks that help attach the
tissue to the bone with frictional force. This solves the problem
of slippage present in other BTB devices.
[0072] FIG. 11A shows a side "look through" three-dimensional view
of a segmented Looped Locking Buckle Assembled BTB bone block
generally represented at 1100. A series of machined proximal
segments 1101 and distal segments 1102 are held in place by dowels
1103 that are stretch the length of the implant. The sections are
put together to create a bone block that is structurally identical
to the solid version described above in FIGS. 10A-D. Each proximal
section 1101 and distal section 1102 has a hole 1104 machined
therethrough, such that when joined together, a passageway is
created for insertion and retention of a tendon. A tendon enters
through the proximal opening 1107 and looped around first 1105 and
second 1106 fastener devices in an identical fashion to that
described above. A distal opening 1108 that allows access to the
tendon from the distal side is also shown
[0073] FIG. 11B shows one distal 1101 segment of a segmented bone
block. The segment is machined to form a first section of a
rectangular opening 1110 of an interior chamber containing a first
fastener device 1105 and a second fastener device 1106 FIG. 11C
shows one half of a segmented bone block. A proximal opening 1107
leads to an interior receiving chamber 1109. A distal opening 1108
leads to an internal fixation chamber 1110. FIG. 11D shows one
section of a distal segment 1102 of the segmented bone block having
a section of a rectangular opening 1110 cut therethrough and an
opening 1103 for receipt of a dowel. FIG. 11E shows one section of
a proximal segment 1101 of a segmented bone block having a circular
opening cut therethrough and an opening for receipt of a dowel
1103. FIG. 11F shows a segmented bone block with tendon 1120
attached. The tendon 1120 enters through a proximal opening 1107
into a receiving chamber 1109 and then into a fixation chamber 1110
where it is looped around a first fastener device 1105 and then a
second fastener device 1106 in a direction opposite to that used on
the first fastener device. The tendon may be manipulated by
accessing the distal opening 1108. To help retain the tendon
cancellous bone particles 1130 are coated onto the tendon such that
through rolling over the fixation devices, the particles become
positioned to act as brakes to the tendon. The individual segments
are held in place by 1103 dowels running the length of the bone
block
[0074] The operation of this device is identical to that described
for the solid bone block of FIGS. 10A-D, with the major difference
being segmentation which allows for the production of larger
grafts.
[0075] FIGS. 12A-F show cross-sectional views of an embodiment of a
Solid Screw Wedge Assembled BTB bone block generally indicated at
1200. FIG. 12A shows a solid bone block 1201 having distal 1202 and
proximal 1203 chambers. The distal chamber 1202 has a partially
threaded segment 1204, and an unthreaded segment 1205 that is
inclined and tapers away distally. A modified interference screw
1210 is used to retain a tendon placed into the bone block via the
proximal chamber 1203. FIG. 12B shows a cross section of the Solid
Screw Wedge Assembled BTB bone block with the screw 1210 threaded
into the distal chamber 1202. FIG. 12C shows the screw 1210
completely screwed into the distal chamber and reveals a space 1206
between the screw and the wall of the bone block. In use, a portion
of a tendon is threaded through the proximal end of the bone block
and is fixed in place through insertion of the screw 1210. As the
screw is inserted the terminal end of the tendon is forced against
the distal wall of the bone block and held in place. A groove 1207
is formed on the exterior of the bone block to accommodate an
interference screw during implantation. FIG. 12D shows a side view
rotated to reveal a lengthwise ridge 1208 on the bone block 1201
that may accommodate an interference screw. As shown the modified
interference screw 1210 has a pentagonal shaped depressed head
1211, which accommodate a socket device for ratcheting it into the
bone block. FIG. 12E shows an angled front view of the same
embodiment. FIG. 12F shows an angled front view with the screw 1210
inserted to reveal the space 1206 that accommodates a portion of a
tendon and a lengthwise ridge 1208 which may accommodate an
interference screw during implantation. FIG. 12G shows a side
profile of the modified interference screw 1210 having smooth
threads 1212. The solid screw wedge design offers the increased
wedging capabilities of an inclined plane without significant wall
loading. The smooth threads of the modified interference screw
offers strength without the risk of tearing the tendon. The tendon
is pulled into a partial threaded area and the screw is used to
tighten the tendon to the side as well as anchoring it to the
bottom using the interference screw's natural shape on its end to
act as a socket head cap screw. The inclined plane of the screw has
more mechanical advantage than the wedge, and the solid design
lends itself to less lateral loading. The end of the modified
interference screw has a cup like feature similar to a cup style
set screw. The landing is smooth and should reduce tearing at that
point. In this embodiment the wedge is eliminated and a rotary
incline takes its place. Thus, the surgeon could pre-tighten the
tendon to a desired torque. Loads are distributed evenly over the
length of the dowel. The tendon is wedged and set when the screw is
tightened.
[0076] FIGS. 13A-C shows a solid ported screw assembled BTB bone
block. This is embodiment is identical to that disclosed in FIGS.
12A-G, except that is has a ported window. FIG. 13A shows a side
profile of a solid ported screw assembled BTB bone block generally
depicted at 1300 having a modified interference screw 1210
partially threaded into the block. A ported window 1301 permits
tissue contact with the formed canal. FIG. 13B shows a side profile
of a solid ported screw assembled BTB bone block with the screw
inserted to partially block the ported window. FIG. 13C shows an
angled front view of the bone block showing a proximal opening 1302
into which a tendon is placed. This embodiment retains the features
of the solid screw wedge assembled BTB described in FIGS. 12A-G,
with the addition of a ported window that allows a portion of the
tendon to contact the surgeons canal. The screw applies more
pressure and has less chance of backing out. The inclined plane
reduces the tendancy to crack the wall under stress loading
longitudinally. Further, the ported window allows tissue to extend
the length of the dowel so as to contact the wall surface of the
surgeons canal allowing for better blood flow and attachment.
[0077] FIG. 14A is a side, cross-sectional view of a solid core
Encapsulated Locking Key Wedge assembled BTB bone block generally
indicated at 1400. The block is machined to have a proximal opening
1401 and distal opening 1402 and a ported window 1403. A tapered
key 1404 is shown having saw toothed teeth 1405 along its top edge.
The key decreases in height moving from its distal end 1406 towards
its proximal end 1407. The saw tooth teeth are designed to grip the
tendon and hold it in place. As shown, the bone block is in an
unlocked position. FIG. 14B shows the bone block in a locked
position.
[0078] FIG. 14C shows an angled top view of the bone block in an
unlocked position. The distal end of the key extends beyond the
distal opening 1402 leaving the ported window 1403 unobstructed.
FIG. 14D shows an angled top view showing a proximal opening 1401
to receive a tendon. FIG. 14E shows a bone block in a locked
position. The distal end 1406 of the key 1404 is flush with the
distal opening 1402. The grooved teeth 1405 are shown filling a
portion of the ported window 1403. In use, a tendon is inserted
into the proximal opening and pushed toward the distal end. The key
is moved in a proximal direction such that the teeth engage the
tendon and hold it in place by pressing it against the interior
walls. A portion of the tissue is then forced through the ported
window to interact with the canal created by the surgeon. This
interaction will result in better blood flow and faster
attachment.
[0079] Previously used two sided wedges have caused splitting of
the bone section of the assembly long before optimal loads were
reaches. In this embodiment, the encapsulated key design places
less exterior pressures on the dowel during loading. The key may
function on its own, or using a drying process on the tendon, be
kept under pressure until seated and then trimmed off. In the event
the key slips, pre-loading and side pinning remain viable options.
This solid design allows for longitudinal force transfer rather
than lateral which will make it more difficult to crack.
[0080] FIGS. 15A-D show an assembled Segmented Looped Pulley bone
tendon block. FIG. 15A shows a side profile exploded view of the
bone tendon block. An upper bone block 1501 and a lower bone block
1502 are held together through insertion of press pins 1503 which
are inserted through holes 1504 in both upper 1501 and lower 1502
bone blocks Ideally, these press pins are 2 mm in length, but may
vary depending upon specific needs. A pull hole 1505 is machined
into the upper 1501 or lower 1502 bone block. The upper bone block
is machined to have a depressed groove 1506 running the length of
the bone block. The lower bone block 1502 is also machined to have
depressed groove 1507 running the length of the bone block. A
tendon 1508 and welded sutures 1509 are also shown. FIG. 15B shows
the same picture, except that an open suture 1510 design replaces
the welded suture 1509 design. FIG. 15C is an assembled view
showing a tendon 1508 looped around an upper 1501 and lower 1502
bone block and held in place by an open suture. FIG. 15D is the
same picture, except that the tendon is held in place by multiple
welded sutures.
[0081] This embodiment is not a BTB, but a modified bone tendon for
anterior cruciate ligament (ACL) or posterior cruciate ligament
(PCL) repair that provides solutions to multiple problems
encountered in these types of repairs. Traditional ACL or PCL
repair techniques utilize a single semitendinosus which becomes
prone to failure when connected by mechanical means to any one bone
block. The reason for this is cyclic creep and fibril backbone
breakdown which occurs due to the means of attachment which, in
turn, disrupts the natural tendency for the tissue to slip or creep
which ultimately leads to shear and failure. In contrast, the
present embodiment takes advantage of this natural action without
compromising the integrity of the implant. By looping the tendon a
pulley design is created. The cross sectional area of the tendon is
doubled, thereby doubling the strength of the single tendon to meet
or exceed the 1000N force desired for tendons used is these
surgeries. This allows use of a host of other tendons that do not
have the strength of a single ACL or PCL. The pulley design
overcomes the difficulty of getting two different tendons to bear
the same stresses because, through use of a single looped tendon,
forces are equalized by natural slippage of the tendon under
stress. Another advantage of the present embodiment is that
fixation points are reduced to one, thereby reducing cycling creep
by as much as 80% of the gross common when two points of fixation
and no stitch augmentation is employed. Double hamstring and double
semitendenousus have been used before, but nothing in use today
employs cyclic creep to gain a mechanical advantage. In this
embodiment, the pulley affect of the mounted bone graft allows the
tendon fixed at one point to creep naturally under the sutures,
thereby minimizing damage to the fibril structure and the
likelihood of shear. Further, using the tendon as a form of rope
through a pulley uses the same forces that defeat the attachment
problems associated with artificial attachment. In the present
embodiment the segmented bone block bears no load along its sides
and is in fact aided by the tissue being on both sides of the bone
block. Doubling also assures that the upper portion of the tendon
receives adequate blood flow from the surrounding tissue.
[0082] Using this embodiment two types of fixation are possible
based on the length of the tendon; internal interference screw
tibial fixation, and exterior fixation. Because the block comprises
two segments, bone considered to narrow, too short or too thin for
other applications such as an interference screw, may be utilized
to create differently sized bone blocks, thereby increasing the
yield of this limited resource. Thus, donor specific problems such
as finding bone blocks large enough for use is made easier.
Further, the use of both long and short tendons of all
cross-sectional sizes when paired with different sized segments,
allows a physician to attach the block in any fashion of two well
accepted methods in use today. Also, because the length may be
varied, more tissue would become available for ACL or PCL
grafts.
[0083] Those skilled in the art will appreciate that the graft may
be an autograft, allograft, or xenograft. Xenograft implants may
further require treatments to minimize the level of antigenic
agents and/or potentially pathogenic agents present in the graft.
Techniques now known, or those, which are later developed, for
preparing tissue such that it is suitable for and not rejected by
the recipient are incorporated herein. In cases where the graft is
an allograft or xenograft, a donor is preferably screened for a
wide variety of communicable diseases and pathogens, including
human immunodeficiency virus, cytomegalovirus hepatitis B,
hepatitis C and several other pathogens. These tests may be
conducted by any of a number of means conventional in the art,
including, but not limited to, ELISA assays, PCR assays, or
hemagglutination. Such testing follows the requirements of the
following associations: (a) American Association of Tissue Banks.
Technical Manual for Tissue Banking, Technical
Manual-Musculoskeletal Tissues, pages M19-M20; (b) The Food and
Drug Administration, Interim Rule, Federal Register, Vol. 58, No.
238, Tuesday, December 14, Rules and Regulations, 65517, D.
Infectious Disease Testing and Donor Screening; (c) MMWR, Vol.43,
No. RR-8, Guidelines for Preventing Transmission of Human
Immunodeficiency Virus Through Transplantation of Human Tissue and
Organs, pages 4-7; (d) Florida Administrative Weekly, Vol. 10,
No.34, Aug. 21, 1992, 59A-1.001-014, 59A-1.005(12)(c), F.A.C.,
(12)(a)-(h), 59A-1.005(15, F.A.C., (4) (a)-(8). In addition to a
battery of standard biochemical assays, the donor, or their next of
kin can be interviewed to ascertain whether the donor engaged in
any of a number of high risk behaviors such as having multiple
sexual partners, suffering from hemophilia, engaging in intravenous
drug use etc. Where allogenic and/or xenogenic sources are used,
the grafts are preferably treated by techniques described in
WO/0009037 and WO/01/08715. Once a donor has been ascertained to be
acceptable, the tissue for obtention of the BTBs as described above
are recovered and cleaned.
[0084] The present invention provides a source for obtaining a
quantity of BTBs sufficient to meet the increasing demand for BTBs
that heretofore has not been possible through use of human grafts
alone. Furthermore, while Applicants have discovered that the
anatomical status of non-human knees (e.g., porcine) provide a
viable alternative source for procuring BTBs. While the procurement
of BTBs from porcine sources is specifically exemplified, it is
understood to those skilled in the art, in view of the teachings
herein, that other xenograft sources can be used as well including,
but not limited to, bovine, equine and other ruminant animals.
[0085] The teachings of all patents and publications cited
throughout this specification are incorporated by reference in
their entirety to the extent not inconsistent with the teachings
herein.
[0086] It should be understood that the examples and embodiments
described herein are for illustrative purposes only and that
various modifications or changes in light thereof will be suggested
to persons skilled in the art and are to be included within the
spirit and purview of this application and the scope of the
appended claims.
EXAMPLE 1
Procedure for Harvesting of Crude BTB for Patellar Tendon Tibial
Donor
[0087] A BTB was harvested according to the following
procedure:
[0088] 1. Using blunt and sharp dissection remove the three layers
of connective tissue from the anterior portion of the tendon.
[0089] 2. Using scalpel or scissors cut along the medial and
lateral borders of the tendon. Use the scissors to bluntly dissect
under the tendon to separate it from the fat layer.
[0090] 3. Cut around the Patellar block to separate it form the
proximal tibia and distal femur. Leave approximately 4 cm of
quadriceps tendon attached to the patellar if required. If no
quadriceps tendon attachment is specified then remove quadriceps
from patellar completely using sharp dissection.
[0091] 4. Pull tendon away from capsule and remove all excess
adipose tissue to the point of tibial insertion.
[0092] 5. With a saw make a transverse cut through approximately
the tibial tuberosity about 30 mm from the tendon insertion point.
Make a similar cut about 5 mm proximal to the insertion point,
which will remove the tibial plateau.
[0093] 6. With a saw, cut and square the sides of the tibia bone
block even with the tendon.
[0094] 7. With a saw cut and square the patella block on three
sides (if quadriceps tendon is still attached square off only the
medial and lateral sides).
[0095] 8. Remove all extraneous soft tissue and cartilage from the
patella, tibial tuberosity and tendon.
[0096] 9. To hemisect the patellar tendon use a scalpel to divide
the tendon into a medial half and a lateral half. Each half should
be 14 mm or greater unless otherwise specified.
[0097] 10. Using a saw, split the patella block and the tibia block
in half following the same medial/lateral line used to split the
tendon.
[0098] 11. Thoroughly lavage the bone blocks with sterile water or
saline.
EXAMPLE 2
Procedure for Forming Patellar Tendons with Pre-shaped Dowels for
Patellar Tendon Tibial Donor
[0099] A BTB was harvested according to the following
procedure:
[0100] 1. Using blunt and sharp dissection remove the three layers
of connective tissue from the anterior portion of the tendon.
[0101] 2. Using a scalpel or scissors cut along the medial and
lateral borders of the tendon to separate it from the fat
layer.
[0102] 3. Cut around the Patellar block to separate it from the
proximal tibia and distal femur.
[0103] 4. Pull tendon away from capsule and remove all excess
adipose tissue to the point of tibial insertion.
[0104] 5. With a saw make a transverse cut through the tibial
tuberosity about 30 mm from the tendon insertion point. Make a
similar cut just proximal to the insertion point removing the
tibial plateau. Make another cut across the coronal plane 20-30 mm
posterior from the insertion point.
[0105] 6. With a saw square the sides of the tibia bone block.
[0106] 7. With a saw cut and square the patella block on the three
sides.
[0107] 8. Attach a vice to the tabletop. Place the tibia bone block
in the vice so that it holds it along the proximal and distal
sides. The distal side of the bone block should be facing the
processor with the tendon going away from them. Tighten the vice so
that it holds the bone securely but does not crush it.
[0108] 9. Attach a Jacob's chuck to a drill and insert the
appropriate size cutter. Tighten the chuck with the chuck key.
Note: At least two plugs should be cut from each bone block.
[0109] 10. Position the cutter against the bone block so the teeth
of the cutter will skim just over the top of the tendon without
catching the tendon. Position the cutter so that the maximum
attachment is obtained throughout the length of the bone plug.
[0110] 11. Turn drill on and begin drilling the plug. When the
cutter nears the end of the plug, slow the drill until the cutter
just breaks through the proximal end of the bone block. Remove the
plug from the cutter and drill without damaging the tendon.
[0111] 12. Repeat steps 10 and 11 for the second plug.
[0112] 13. Using scissors or a scalpel hemisect the tendon into
medial and lateral halves.
[0113] 14. Remove the excess bone from the table vice and place the
patella bone block into the vice so that it holds it along the
medial and lateral sides of the block. The proximal side of the
patella should be facing the processor with the tendon going away
from them. Tighten the vice so that it holds the bone block
securely but does not crush it.
[0114] 15. Repeat steps 10 and 11 for both plugs.
[0115] 16. When the plugs are completed, remove the excess patella
bone from the vice and detach the vice from the table.
[0116] 17. Remove the cutter from the Jacob's chuck and place a 1.5
mm drill bit into the chuck. Tighten with the chuck key.
[0117] 18. Using a saw, cut each plug to approximately 30 mm in
length (no less than 25 mm)
[0118] 19. Using the Arthrex clamp, place the plug into it with the
end of the plug flush with the end of the clamp. Position the plug
in the anterior/posterior position. Using the first guide hole
nearest the flush end of the plug, drill a hole through the plug
with the 1.5 mm drill bit. Turn the plug 180 degrees so that it is
positioned in the medial/lateral position. Use the second guide
hole from the flush end of the plug to drill a second hole through
the plug.
[0119] 20. Repeat step 19 for all bone plugs.
[0120] 21. Using a sizing apparatus insert each bone plug into the
appropriate size gauge. The entire BTB should slide completely
through easily. Trim if necessary.
[0121] 22. Thoroughly lavage bone plugs with sterile water or
saline.
EXAMPLE 3
Production of Porcine BTB
[0122] A tissue sample was harvested from a pig knee to form a
traditionally shaped BTB shown in FIGS. 9A, 9B and 9C according to
the above disclosed method. The graft measured 65 mm (l).times.14
mm (w), with a total length of 131 mm and thickness of 6 mm. The
tibia block measured 35 mm (l).times.16 mm (w).times.12 mm (h) and
the patellar block measured 32 mm (l).times.16 mm (w).times.17 mm
(h). The graft looked similar to a human BTB graft, and had a very
dense, cancellous bone on the patella and tibia.
EXAMPLE 4
Load to Failure Data for Two Porcine Grafts
[0123] Two porcine BTBs were harvested and pre-shaped according to
the disclosed method from pig knees for testing of maximum
strength. Specimen 1 measured 79 mm (l).times.11 mm (w), and was
4.5 mm thick. The tibia bone block measured 21 mm (l).times.9.5 mm
(w).times.9.5 mm (h) and the patella bone block measured 3.6 mm
(l).times.9.6 (w).times.9.5 mm (h). The graft failed at the tendon
at maximum load of 1055N. Specimen 2 measured 63 mm (l).times.13 mm
(w), and was 6.0 mm thick. The tibial bone block measured 26 mm
(l).times.9.6 mm (w).times.9.5 mm (h), while the patellar bone
block measured 29 mm (l).times.9.7 mm (w).times.9.5 mm (h). The
graft failed at a maximum load of 1187N.
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