U.S. patent application number 10/658351 was filed with the patent office on 2005-03-10 for orthopaedic implant and screw assembly.
Invention is credited to Ferrante, Joseph, James, Anthony H., Mines, Angie.
Application Number | 20050055024 10/658351 |
Document ID | / |
Family ID | 34226764 |
Filed Date | 2005-03-10 |
United States Patent
Application |
20050055024 |
Kind Code |
A1 |
James, Anthony H. ; et
al. |
March 10, 2005 |
Orthopaedic implant and screw assembly
Abstract
Systems, devices and methods are disclosed for treating
fractures. The systems, devices and methods may include one or both
of an implant, such as an intramedullary nail, and a fastening
assembly, such as a lag screw and compression screw assembly. The
implant in some embodiments has a proximal section with a
transverse aperture and a cross-section that may be shaped to more
accurately conform to the anatomical shape of cortical bone and to
provide additional strength and robustness in its lateral portions,
preferably without requiring significant additional material. The
fastening assembly may be received to slide, in a controlled way,
in the transverse aperture of the implant. In some embodiments, the
engaging member and the compression device are configured so that
the compression device interacts with a portion of the implant and
a portion of the engaging member to enable controlled movement
between the first and second bone fragments. This configuration is
useful for, among other things, compressing a fracture.
Inventors: |
James, Anthony H.;
(Bartlett, TN) ; Ferrante, Joseph; (Bartlett,
TN) ; Mines, Angie; (Mason, TN) |
Correspondence
Address: |
CHIEF PATENT COUNSEL
SMITH & NEPHEW, INC.
1450 BROOKS ROAD
MEMPHIS
TN
38116
US
|
Family ID: |
34226764 |
Appl. No.: |
10/658351 |
Filed: |
September 8, 2003 |
Current U.S.
Class: |
606/64 |
Current CPC
Class: |
A61B 17/1604 20130101;
A61B 17/1633 20130101; A61B 17/725 20130101; A61B 17/8061 20130101;
A61B 17/7283 20130101; A61B 17/1728 20130101; A61B 17/72 20130101;
A61B 17/1615 20130101; A61B 17/164 20130101; A61B 17/1668 20130101;
A61B 17/7258 20130101; A61B 17/746 20130101; A61B 17/1684 20130101;
A61B 17/7233 20130101; A61B 17/744 20130101 |
Class at
Publication: |
606/064 |
International
Class: |
A61B 017/58 |
Claims
What is claimed is:
1. Apparatus for treating bone fractures, comprising: a.
stabilizing structure adapted to be connected to a first bone
portion and containing a transverse aperture; and b. a fastening
assembly having an engaging member and a compression member, the
fastening assembly being adapted to slide within the transverse
aperture; c. wherein the engaging member is adapted to engage a
second bone portion, and the engaging member and the compression
member are configured so that the compression member contacts and
interacts with a portion of the implant and a portion of the
engaging member to enable controlled movement between the first and
second bone portions; and d. wherein when installed the compression
device contacts the second bone portion.
2. Apparatus according to claim 1 in which the controlled movement
between the first and second bone portions includes preclusion of
rotation of the portions relative to each other.
3. Apparatus according to claim 1 in which the controlled movement
between the first and second bone portions further includes
application of compression of the bone portions relative to each
other.
4. Apparatus according to claim 1 in which the stabilizing
structure is adapted to connect to bone outer surface.
5. Apparatus according to claim 1 in which the stabilizing
structure is a bone implant.
6. Apparatus according to claim 1 in which the compression member
is adapted, when adjusted, to apply tension to the engaging member
and thereby apply compression between the first bone portion and
the second bone portion.
7. Apparatus according to claim 1 in which the compression member
is at least partially nested with a portion of the engaging
member.
8. Apparatus according to claim 1 in which the compression member
includes a threaded portion, and the engaging member includes a
threaded portion adapted to cooperate with the compression member
threaded portion in order to control sliding of the engaging member
in the stabilizing structure transverse aperture.
9. Apparatus according to claim 1 further comprising a set screw
received in said stabilizing structure, said set screw adapted to
preclude sliding of the engaging member in the transverse
aperture.
10. Apparatus according to claim 1 in which the transverse aperture
is asymmetrical in cross section and includes a first portion
adapted to receive at least part of the engaging member and a
second portion adapted to receive at least part of the compression
member.
11. Apparatus according to claim 5 in which the implant includes a
proximal section that is asymmetrical in cross-section about at
least one axis.
12. Apparatus for treating a bone fracture, comprising: a. a
stabilizing structure adapted to be connected to a first bone
portion and containing a transverse aperture; b. a fastening
assembly adapted to be received in the transverse aperture,
comprising: 1. an engaging member adapted to slide in the
stabilizing structure transverse aperture and to engage a second
bone portion; the engaging member including cooperation structure
adapted to cooperate with a compression member; 2. a compression
member adapted to be received in the stabilizing structure
transverse aperture, and adapted to contact and cooperate with the
engaging member to preclude the engaging member from rotating in
the transverse aperture, and to control sliding of the engaging
member in the transverse aperture, c. wherein the compression
member 1. contacts the second bone portion when installed in order,
together with the engaging member, to preclude the second bone
portion from rotating relative to the engaging member; and 2.
cooperates with the engaging member to preclude rotation of the
engaging member relative to the stabilizing structure, and thus
preclude the second bone portion from rotating relative to the
first bone portion.
13. Apparatus according to claim 12 in which the stabilizing
structure is adapted to connect to bone outer surface.
14. Apparatus according to claim 12 in which the stabilizing
structure is a bone implant.
15. Apparatus according to claim 12 in which the compression member
is adapted, when adjusted, to apply tension to the engaging member
and thereby apply compression between the first bone portion and
the second bone portion.
16. Apparatus according to claim 12 in which the compression member
is at least partially nested with a portion of the engaging
member.
17. Apparatus according to claim 12 in which the compression member
includes a threaded portion, and the engaging member includes a
threaded portion adapted to cooperate with the compression member
threaded portion in order to control sliding of the engaging member
in the stabilizing structure transverse aperture.
18. Apparatus according to claim 12 further comprising a set screw
received in said stabilizing structure, said set screw adapted to
preclude sliding of the engaging member in the transverse
aperture.
19. Apparatus according to claim 12 in which the transverse
aperture is asymmetrical in cross section and contains a first
portion adapted to receive at least part of the engaging member and
a second portion adapted to receive at least part of the
compression member.
20. Apparatus according to claim 14 in which the implant includes a
proximal section which is asymmetrical in cross section about at
least one axis.
21. A device for treating a bone fracture, comprising: a. an
elongated distal section adapted to be inserted into the medullary
canal of a bone; b. a transition section which provides a shaped
coupling between the distal section and a proximal section; and c.
a proximal section including: 1. a transverse aperture adapted to
receive structure that is in turn adapted to engage bone; 2. a
lateral aspect; 3. a medial aspect; and 4. at least one cross
section oriented substantially perpendicular to the length of the
device, wherein the cross section features a moment of inertia that
extends toward the lateral aspect from the midpoint of a line that
extends in the cross section from the intersection of a tangent on
the lateral aspect and the line to the intersection of a tangent on
the medial aspect and the line.
22. A device according to claim 21 further comprising a
longitudinal aperture extending substantially parallel to the
longitudinal axis of the device.
23. A device according to claim 21 in which the cross section is
asymmetrical with respect to at least one axis.
24. A device according to claim 21 in which the device is adapted
to fit completely within the bone whose fracture is being
repaired.
25. A device according to claim 21 in which at least a portion of
the surface of the lateral aspect is substantially planar.
26. A device according to claim 21 in which the device is adapted
to be at least partially implanted in a first bone portion and
further comprising: d. a fastening assembly having an engaging
member and a compression member, the fastening assembly being
adapted to slide within the transverse aperture; e. wherein the
engaging member is adapted to engage a second bone portion, and the
engaging member and the compression member are configured so that
the compression member interacts with a portion of the device and a
portion of the engaging member to enable controlled movement
between the first and second bone portions; and f. wherein when
implanted the compression device contacts the second bone
portion.
27. A nail for treating a femoral fracture, comprising: a. an
elongated distal section adapted to be inserted into the medullary
canal of a bone; b. a transition section which provides a shaped
coupling between the distal section and a proximal section; and c.
a proximal section including: 1. a transverse aperture adapted to
receive structure that is in turn adapted to engage bone; 2. a
lateral aspect; 3. a medial aspect; and 4. at least one
cross-section oriented substantially perpendicular to the length of
the device, wherein the cross-section is noncircular in shape and
includes a medial-lateral axis, wherein the cross-section is
symmetrical with respect to the medial-lateral axis and wherein the
linear dimension of the cross-section along the medial-lateral axis
is greater than any linear dimension of the cross-section along an
axis perpendicular to the medial-lateral axis.
28. Apparatus for treating bone fractures, comprising: a. an
elongated distal section; b. a transition section which provides a
shaped coupling between the distal section and a proximal section;
and c. a proximal section adapted to be connected to a first bone
portion, including: 1. a transverse aperture, which transverse
aperture includes a longitudinal axis; 2. a lateral aspect; 3. a
medial aspect; 4. at least one cross section oriented substantially
perpendicular to the length of the device, wherein the cross
section features a moment of inertia that extends toward the
lateral aspect from the midpoint of a line that is coplanar with
the transverse aperture axis and extends in the cross section from
the intersection of a tangent on the lateral aspect and the line to
the intersection of a tangent on the medial aspect and the line;
and 5. a fastening assembly including an engaging member and a
compression member, the fastening assembly being adapted to slide
within the transverse aperture; (i) wherein the engaging member is
adapted to engage a second bone portion, and the engaging member
and the compression member are configured so that the compression
member interacts with a portion of the implant and a portion of the
engaging member to enable controlled movement between the first and
second bone portions; and (ii) wherein when installed the
compression device contacts the second bone portion.
29. Apparatus according to claim 28 in which the controlled
movement between the first and second bone portions includes
preclusion of rotation of the portions relative to each other.
30. Apparatus according to claim 28 in which the controlled
movement between the first and second bone portions further
includes application of compression of the bone portions relative
to each other.
31. Apparatus according to claim 28 in which the stabilizing
structure is a bone implant.
32. Apparatus according to claim 28 in which the compression member
is adapted, when adjusted, to apply tension to the engaging member
and thereby apply compression between the first bone portion and
the second bone portion.
33. Apparatus according to claim 28 in which the compression member
is at least partially nested with a portion of the engaging
member.
34. Apparatus according to claim 28 in which the compression member
includes a threaded portion, and the engaging member includes a
threaded portion adapted to cooperate with the compression member
threaded portion in order to control sliding of the engaging member
in the stabilizing structure transverse aperture.
35. Apparatus according to claim 28 further comprising a set screw
received in said stabilizing structure, said set screw adapted to
preclude sliding of the engaging member in the transverse
aperture.
36. Apparatus according to claim 28 further comprising a
longitudinal aperture extending substantially parallel to the
longitudinal axis of the apparatus.
37. Apparatus according to claim 28 in which the cross section is
asymmetrical with respect to at least one axis of the cross
section.
38. Apparatus according to claim 28 in which the apparatus is
adapted to fit completely within the bone whose fracture is being
repaired.
39. A device according to claim 28 in which at least a portion of
the surface of the lateral aspect is substantially planar.
40. A tool adapted to prepare bone for introduction of a device
which includes a proximal portion whose cross section is
asymmetrical with respect to at least one axis of the cross
section, comprising: a. a mortise chisel which corresponds in
shape, and is adapted to shape bone in a shape corresponding at
least partially to the shape of the device's cross section; and b.
a bit adapted to rotate within the mortise chisel and prepare
portions of the bone's medullary canal located distally of the
portions of bone shaped by the mortise chisel
41. A system for repairing bone, comprising a. an implant that
includes a lateral aspect; a medial aspect; and at least one cross
section oriented substantially perpendicular to the length of the
implant, wherein the cross section features a moment of inertia
that extends toward the lateral aspect from the midpoint of a line
that extends in the cross section from the intersection of a
tangent on the lateral aspect and the line to the intersection of a
tangent on the medial aspect and the line; and b. a tool adapted to
prepare the bone for introduction of the implant, comprising: 1. a
mortise chisel which corresponds in shape, and is adapted to shape
bone in a shape corresponding at least partially to the shape of
the implant's cross section; and 2. a bit adapted to rotate within
the mortise chisel and prepare portions of the bone's medullary
canal located distally of the portions of bone shaped by the
mortise chisel.
42. A process for repairing bone, comprising: a. providing a device
for treating bone fractures, comprising: 1. stabilizing structure
adapted to be connected to a first bone portion and containing a
transverse aperture; and 2. a fastening assembly having an engaging
member and a compression member, the fastening assembly being
adapted to slide within the transverse aperture; and 3. wherein the
engaging member is adapted to engage a second bone portion, and the
engaging member and the compression member are configured so that
the compression member contacts and interacts with a portion of the
device and a portion of the engaging member to enable controlled
movement between the first and second bone portions; b. connecting
the device to the first bone portion; c. preparing at least one
opening in the first bone portion corresponding in location and
orientation to the engaging member and to the compression member;
d. engaging the second bone portion with the engaging member; e.
inserting the compression member so as to contact the second bone
portion; and f. causing the compression member to interact with a
portion of the engaging member and thereby apply compression to the
second bone portion relative to the first bone portion.
43. A process according to claim 42 in which connecting the device
to the first bone portion comprises attaching the device to an
outer surface of the first bone portion.
44. A process according to claim 42 in which connecting the device
to the first bone portion comprises inserting the device in the
first bone portion.
45. A process according to claim 42 in which the second bone
portion is a femoral head.
46. A process according to claim 42 in which preparing at least one
opening in the first bone portion corresponding in location and
orientation to the engaging member and to the compression member
comprises preparing openings in the bone portion which are not
coaxial with respect to each other.
47. A process according to claim 42 in which the device is an
implant which includes a proximal portion that includes a cross
section which is asymmetrical with respect to at least one axis of
the cross section, and connecting the device to the first bone
portion includes: a. preparing interior portions of the bone using
a tool which in turn includes a mortise chisel adapted to shape the
bone corresponding at least in part to the shape of the implant
proximal portion cross section; and b. inserting the implant into
the bone as shaped by the tool.
48. A process for stabilizing bone, comprising: a. providing an
implant which includes a distal portion and a proximal portion that
includes a cross section which is asymmetrical with respect to at
least one axis of the cross section; b. preparing interior portions
of the bone using a tool which includes a mortise chisel adapted to
shape the bone corresponding at least in part to the shape of the
implant proximal portion cross section a bit adapted to rotate
relative to the mortise chisel for preparing at least part of the
bone to receive the distal portion of the implant, the preparation
including shaping portions of the bone with the mortise chisel and
further including causing the bit to rotate relative to the mortise
chisel and thus prepare at least part of the bone to receive the
distal portion of the implant; and c. inserting the implant into
the bone.
49. A process according to claim 48 in which the implant includes a
transverse aperture and a fastening assembly having an engaging
member and a compression member, the fastening assembly being
adapted to slide within the transverse aperture; and wherein the
engaging member is adapted to engage a femoral head, and the
engaging member and the compression member are configured so that
the compression member contacts and interacts with a portion of the
implant and a portion of the engaging member to enable controlled
movement between the bone and the femoral head; the process further
comprising: a. preparing at least one opening in the bone
corresponding in location and orientation to the engaging member
and to the compression member; b. engaging the femoral head with
the engaging member; c. inserting the compression member so as to
contact the femoral head; and d. causing the compression member to
interact with a portion of the engaging member and thereby apply
compression to the femoral head relative to the bone.
Description
FIELD OF THE INVENTION
[0001] The present invention generally relates to a system for
coupling bone portions across a fracture and, more specifically, to
an intramedullary nail or plate and screw assembly used to treat
fractures of long bones such as the femur, humerus and tibia, and
various periarticular fractures of these and other bones.
BACKGROUND OF THE INVENTION
[0002] There are a variety of devices used to treat fractures of
the femur, humerus, tibia, and other long bones. For example,
fractures of the femoral neck, head, and intertrochanteric region
have been successfully treated with a variety of compression screw
assemblies, which include generally a compression plate having a
barrel member, a lag screw and a compressing screw. Examples
include the AMBI.RTM. and CLASSIC.TM. compression hip screw systems
offered by Smith & Nephew, Inc. In such systems, the
compression plate is secured to the exterior of the femur, and the
barrel member is inserted in a predrilled hole in the direction of
the femoral head. The lag screw has a threaded end, or another
mechanism for engaging bone, and a smooth portion. The lag screw is
inserted through the barrel member so that it extends across the
break and into the femoral head. The threaded portion engages the
femoral head. The compression screw connects the lag screw to the
plate. By adjusting the tension of the compression screw, the
compression (reduction) of the fracture can be varied. The smooth
portion of the lag screw is free to slide through the barrel member
to permit the adjustment of the compression screw. Some assemblies
of the prior art use multiple screws to prevent rotation of the lag
screw relative to the compression plate and barrel member and also
to prevent rotation of the femoral head on the lag screw.
[0003] Intramedullary nails in combination with lag screws or other
screw assemblies have been successfully used to treat fractures of
the femur, humerus, tibia, and other long bones as well. A
significant application of such devices has been the treatment of
femoral fractures. One such nailing system is the IMHS.RTM. system
offered by Smith & Nephew, Inc., and covered at least in part
by U.S. Pat. No. 5,032,125 and various related international
patents. Other seminal patents in the field include U.S. Pat. Nos.
4,827,917, 5,167,663, 5,312,406, and 5,562,666, which are all
assigned to Smith & Nephew, Inc. These patents are all hereby
incorporated by reference A typical prior art intramedullary nail
may have one or more transverse apertures through its distal end to
allow distal bone screws or pins to be screwed or otherwise
inserted through the femur at the distal end of the intramedullary
nail. This is called "locking" and secures the distal end of the
intramedullary nail to the femur. In addition, a typical
intramedullary nail may have one or more apertures through its
proximal end to allow a lag screw assembly to be screwed or
otherwise inserted through the proximal end of the intramedullary
nail and into the femur. The lag screw is positioned across the
break in the femur and an end portion of the lag screw engages the
femoral head. An intramedullary nail can also be used to treat
shaft fractures of the femur or other long bones.
[0004] As with compression hip screw systems, intramedullary nail
systems are sometimes designed to allow compression screws and/or
lag screws to slide through the nail and thus permit contact
between or among the bone fragments. Contact resulting from sliding
compression facilitates faster healing in some circumstances. In
some systems, two separate screws (or one screw and a separate pin)
are used in order, among other things, to prevent rotation of the
femoral head relative to the remainder of the femur, to prevent
penetration of a single screw beyond the femoral head, and to
prevent a single screw from tearing through the femoral neck and
head. When an additional screw or pin is used, however, unequal
forces applied to the separated screws or pins can cause the
separate screws or pins to be pressed against the sides of the
holes through which the separate screws or pins are intended to
slide. This may result in binding, which reduces the sliding of the
screws or pins through the nail. Conversely, a problem can result
from excessive compression of the femoral head toward or into the
fracture site. In extreme cases, excessive sliding compression may
cause the femoral head to be compressed all the way into the
trochanteric region of the femur.
[0005] Furthermore, overly rigid nails sometimes generate
periprosthetic fractures in regions away from a fracture site.
Therefore, it is important that intramedullary nails be adequately
flexible in comparison to the bones in which they are
implanted.
[0006] The harder, generally outer portion of a typical bone is
referred to as cortical bone. Cortical bone is usually a
structurally sound load-bearing material for support of an implant.
A cross-section of a long bone that shows the typical anatomical
shape of cortical bone generally reveals a non-circular ring of
cortical bone which surrounds a medullary canal. Accordingly, the
medullary canal generally features a non-circular cross section.
Intramedullary nails of the prior art, however, are usually round
or square in cross-section, and therefore not anatomically
consistent with the cortical bone or the medullary canal. Some have
addressed this problem by reaming the medullary canal of the bone
with a round reamer in order to cause the nail to fit the cortical
bone. This approach, however, can remove significant portions of
healthy cortical bone.
[0007] The problem of providing an effective load bearing physical
relationship between an implant and cortical bone in the proximal
femur has been addressed in the art of hip replacement devices.
Various hip stems have been developed which feature generally
non-circular cross sections along their length, in order better to
fit the anatomically shaped cortical bone of the proximal femur and
thus more evenly and effectively distribute the load between the
stem and the bone. However, none of these hip stems have been
incorporated into a nail or configured to accept a screw or screws
useful in repairing substantially all of the portions of the
treated bone. Instead, hip stems as a general matter have been
considered as a device for replacing portions of a long bone, and
designed and used for that purpose. For example, the typical
application of a hip stem includes completely removing a femoral
head and neck, implanting a hip stem, and using the hip stem to
support an artificial femoral head.
[0008] In summary, and without limitation, the foregoing shows some
of the shortcomings of the state of the art in this field. Among
other things, what is needed is an orthopaedic implant system that
includes a superior sliding screw or other mechanism for applying
compression across a fracture. Some embodiments would also provide
a sliding screw or other mechanism that obtains adequate bone
purchase while reducing the incidence of cut-out, rotational
instability, and excessive sliding. An anatomically appropriately
shaped implant for achieving improved cortical bone contact would
also be advantageous. Where the implant is an intramedullary nail,
the nail would provide for reduced reaming and removal of healthy
bone. An improved nail may also have a cross-section that provides
a greater area of material on the side of the nail that is placed
under a greater tensile load when the nail is subjected to a
typical bending load. Additionally, an improved implant system
could include a sliding screw in combination with intramedullary
nails of various designs, or in combination with plates.
Combinations of any of these with each other or combinations of
each other, and/or with other devices or combinations of them also
present opportunities for advancement beyond the state of the art
according to certain aspects of the present invention.
SUMMARY OF THE INVENTION
[0009] Methods, devices and systems according to certain aspects of
this invention allow treatment of bone fractures using one or both
of an structure configured to be implanted in or stabilize a first
bone fragment and a fastening assembly. The structure may take the
form of a plate or other device for at least partial application to
the outer surface of bone, or an implant for at least partial
implantation within bone. Such implants may include a proximal
section having a transverse aperture, and an aperture substantially
along their length. Preferably, they include at least one
cross-section in their proximal portions which features a shape
that imparts additional strength and resistance to tension. Such
shapes can be provided, for instance, by one or both (i) adding
additional mass in lateral portions of the cross section, and (2)
strategically adding and reducing mass in the cross section to take
advantage of flange effects similar to the way flanges add
structural benefits to I-beams and channels. One way to
characterize such cross-sections, which can but need not be
asymmetrical with respect to at least one axis, is that they
generally feature a moment of inertia extending in a lateral
direction from a point that is the midpoint of a line from a
lateral tangent to a medial tangent of the cross section. In some
structures, that line is coplanar with the axis of the transverse
aperture and coplanar with the cross section and thus defined by
the intersection of those planes. The endpoints of that line can be
defined as the intersection of the line with tangents to the medial
aspect and the lateral aspect of the cross section, respectively.
Such implants also typically include a distal section and a
transition section that provides a coupling between the proximal
section and the distal section.
[0010] Fastening assemblies of methods, devices and systems
according to certain embodiments of the invention preferably
include an engaging member and a compression device. The fastening
assemblies are adapted to be received in the transverse aperture of
the implant in a sliding relationship, so that the fastening
assembly is adapted to slide with respect to the transverse
aperture, and thus apply compression to a fracture and for any
other desired purpose. The engaging member is adapted to gain
purchase in a second bone fragment. The engaging member and the
compression device are configured so that the compression device
interacts with a portion of the implant and also with a portion of
the engaging member so that adjustment of the compression device
controls sliding of the engaging member relative to the implant and
thereby enables controlled movement between the first and second
bone fragments. In some embodiments, the compression device at
least partially directly contacts the second bone fragment when
implanted.
BRIEF DESCRIPTION OF THE DRAWINGS
[0011] FIG. 1 is a perspective view of an intramedullary nail
according to one embodiment of the present invention shown
installed in a femur.
[0012] FIG. 1A is a perspective view of an intramedullary nail
according to one embodiment of the present invention in greater
detail.
[0013] FIG. 1B is a perspective view of an intramedullary nail
according to another embodiment of the present invention.
[0014] FIG. 1C is a cross-sectional view of a portion of the nail
of FIG. 1B.
[0015] FIG. 2 is an elevation view of the intramedullary nail of
FIG. 1.
[0016] FIG. 3 is a cross-section view of the intramedullary nail of
FIG. 2 taken through the line 3-3.
[0017] FIG. 4 is a side view of the intramedullary nail of FIG.
2.
[0018] FIG. 5 is a cross-section view of the intramedullary nail of
FIG. 4 taken through the line 5-5.
[0019] FIG. 6 is a cross-section of the intramedullary nail of FIG.
4 taken through the line 6-6.
[0020] FIG. 7 is a perspective view of an intramedullary nail
according to an alternative embodiment of the invention.
[0021] FIG. 8 is a perspective view of an intramedullary nail
according to an alternative embodiment of the invention.
[0022] FIG. 9 is a perspective view of an intramedullary nail
according to an alternative embodiment of the invention.
[0023] FIG. 10 is a perspective view of an intramedullary nail
according to an alternative embodiment of the invention.
[0024] FIG. 11 is a perspective view of an intramedullary nail
according to an alternative embodiment of the invention.
[0025] FIG. 12 is a perspective view of an intramedullary nail
according to an alternative embodiment of the invention.
[0026] FIG. 13 is a cross-section view of the intramedullary nail
of FIG. 7 taken through line 13-13.
[0027] FIG. 14 is a cross-section view of the intramedullary nail
of FIG. 8 taken through line 14-14.
[0028] FIG. 15 is a cross-section view of the intramedullary nail
of FIG. 9 taken through line 15-15.
[0029] FIG. 16 is a cross-section view of the intramedullary nail
of FIG. 10 taken through line 16-16.
[0030] FIG. 17 is a cross-section view of the intramedullary nail
of FIG. 11 taken through line 17-17.
[0031] FIG. 18 is a cross-section view of the intramedullary nail
of FIG. 12 taken through line 18-18.
[0032] FIG. 19 is a perspective view of a tool according to an
embodiment of the present invention for preparing bone to receive
certain devices according to certain embodiments of the present
invention.
[0033] FIG. 20 is a perspective view of a device which includes a
version of a fastener assembly according to one embodiment of the
present invention.
[0034] FIG. 21 is an exploded view of the intramedullary device and
fastener assembly shown in FIG. 20.
[0035] FIG. 22 is a perspective view of the fastener assembly shown
in FIG. 20.
[0036] FIG. 23 is an exploded view of the fastener assembly of FIG.
20.
[0037] FIG. 24 is an elevation view of the engaging member of the
fastener assembly of FIG. 23.
[0038] FIG. 25 is a side view of the engaging member of FIG.
24.
[0039] FIG. 26 is a cross-section view of the engaging member of
FIG. 24 taken through line 26-26.
[0040] FIG. 27 is an end view of one end of the engaging member of
FIG. 24.
[0041] FIG. 28 is an end view of the other end of the engaging
member of FIG. 24.
[0042] FIG. 29 is an elevation view of the compression device of
the fastener assembly of FIG. 22.
[0043] FIG. 30 is a cross-section view of the compression device of
FIG. 29 shown through line 30-30.
[0044] FIG. 31 is an end view of one end of the compression device
of FIG. 29.
[0045] FIG. 32 is an end view of the other end of the compression
device of FIG. 29.
[0046] FIG. 33 is a cross-section view of an intramedullary nail
and screw assembly according to another embodiment of the present
invention.
[0047] FIG. 34 is a perspective view of a fastener assembly
according to another embodiment of the invention.
[0048] FIG. 35 is a perspective view of the lag screw of the
fastener assembly of FIG. 34.
[0049] FIG. 36 is a perspective view of a fastener assembly
according to another embodiment of the invention.
[0050] FIG. 37 is a perspective view of the lag screw of the
fastener assembly of FIG. 36.
[0051] FIG. 38 is a perspective view of a fastener assembly
according to another embodiment of the invention.
[0052] FIG. 39 is an exploded view of the fastener assembly of FIG.
38.
[0053] FIG. 40 is a perspective view of a fastener assembly
according to another embodiment of the invention.
[0054] FIG. 41 is an exploded view of the fastener assembly of FIG.
40.
[0055] FIG. 42 is a perspective view of a compression plate
according to an embodiment of the present invention which includes
a fastener assembly according to an embodiment of the
invention.
[0056] FIG. 43 is a perspective view of a periarticular plate
according to an embodiment of the present invention which includes
a fastener assembly according to an embodiment of the
invention.
[0057] FIG. 44 is a perspective view of a device according to an
embodiment of the present invention used in the context of humeral
repair in a shoulder joint.
DETAILED DESCRIPTION
[0058] Methods, devices and systems according to embodiments of
this invention seek to provide improved treatment of femur
fractures. FIGS. 1-6 illustrate various views of one embodiment of
an intramedullary nail 100 of the present invention. The
intramedullary nail 100 has a longitudinal bore 130 throughout to
aid in insertion in the bone. The intramedullary nail 100 has a
proximal section 102, a transition section 104 and a distal section
106.
[0059] The proximal section 102 of the particular structure shown
in FIGS. 1-6 preferably features an anatomically inspired shape
that corresponds more accurately to typical cortical bone. One
version of such shape is shown in the cross-sectional view of the
proximal section 102 in FIG. 6. The particular cross-section of the
proximal section 102 shown in FIG. 6 is generally non-circular
along at least some portions of its length, and has a lateral side
or aspect 108 that is larger than a medial side or aspect 109. The
lateral side 108 and medial side 109 are joined by a first side 110
and a second side 116. At the intersection of the first side 110
with the lateral side 108 is a first radiused corner 112 and at the
intersection of the second side 116 with the lateral side 108 is a
second radiused corner 114. The first side 110, second side 116 and
lateral side 108 are of approximately equal length. The first side
110 and second side 116 are oriented at acute angles relative to
the lateral side 108, so that the medial side 109 is smaller than
the lateral side 108. By having the lateral side 108 larger than
the medial side 109 the rotational stability of the intramedullary
nail 100 is increased, and resistance to bending and twisting can
also be enhanced.
[0060] The medial side 109 shown in FIG. 6 can be radiused. As can
be seen in FIG. 4, the radiused medial side 109 protrudes out from
the transition section 104 and continues to the proximal end of the
intramedullary nail 100. The protrusion of the medial side 109
corresponds to the calcar region of the femur and improves the
evenness of load distribution between the bone and intramedullary
nail 100. Furthermore, the general cross-section geometry of the
proximal section reduces peak stresses in the proximal section.
More specifically, the typical failure mode of an intramedullary
nail and screw assembly combination is failure of the nail in
tension on its lateral side. The tension is created by bending
moment induced by body weight load that is applied to the screw
assembly. Therefore, it would be beneficial in reducing stress in
the proximal section of a nail to include more material on the side
of the nail that is in tension, the lateral side, to shape the
cross section more effectively to enhance strength and robustness
in the lateral area, or both. The design illustrated in FIG. 6
accomplishes this objective. The lateral side 108 is wider than the
medial side 109, thus imparting, at least partially, a flange-like
effect. Stress per unit area induced in the material on the lateral
side 108 is less than would be the case if the lateral side was
featured a smaller cross-sectional area, such as medial side
109.
[0061] A structure according to another embodiment of the invention
that benefits from the same principle, is shown in FIGS. 1B and 1C
which illustrate a intramedullary nail 1100 with a generally
circular cross section whose generally circular aperture 1128 is
disposed other than concentric with the periphery of the cross
section. In the particular structure shown in these two Figures,
the offset aperture 1128 is offset toward the medial side 1109 such
that a greater portion of material is available to take load, and
reduce stress, on the lateral side 1108. Likewise, any
cross-section that provides more material on the lateral side of
the section reduces stress per unit area in the nail on that
side.
[0062] Regardless of the particular manner in which material or
mass may be added to some portions of the lateral parts of the
cross section of proximal portion 102, material may be added and
removed from some portions of the cross section in order to
increase the strength and robustness of the lateral parts, or both,
the effect can be characterized as imparting a moment of inertia to
the cross section oriented at least partially in the direction of
the lateral side or aspect 108. In a preferred embodiment, the
moment of inertia (shown denoted by the letter M on FIG. 6) can be
characterized as extending in a lateral direction, or at least
partially toward lateral aspect or side 108 from a point P that is
the midpoint of a line L extending from the intersection 11 of that
line with a tangent T1 to the lateral aspect 108, to the
intersection 12 of that line with a tangent T2 to the medial aspect
109. Stated another way, the effect in at least some cases is to
create a cross section that features a moment of inertia extending
in at least partially lateral direction from a center of the cross
section. Preferably, that center can be a midpoint between the
lateral and medial edges of the cross section. Alternatively, that
center can be the center of mass of the cross section. The radius
of gyration reflected by the moment of inertia, which is a function
of the square of the distance of the incremental mass from the
center, reflects additional strength in lateral parts of the
proximal portion 102 caused by more mass or more strategically
placed mass in the cross section. In some structures, line L is
coplanar with the axis of the transverse aperture and coplanar with
the cross section and thus defined by the intersection of those
planes. As FIGS. 1A, on the one hand, and 1B and 1C on the other
hand reflect, and bearing in mind that these are only two of a
myriad of structures that can impart such lateral additional
strength and robustness, the cross section can but need not be
asymmetrical with respect to at least one of its axes.
Additionally, the longitudinal opening 130 can be located to share
its central axis with that of the cross section, or it can be
offset in order to help impart the lateral strength or for other
purposes.
[0063] In the particular device shown in FIGS. 1-6, the first side
110, second side 116 and lateral side 108 are flat. Alternatively,
these sides could be radiused or otherwise not flat. In the
embodiment shown in FIGS. 1-6, the medial side 109 is radiused, but
as one skilled in the art could appreciate, the medial side could
be flat.
[0064] The proximal section 102 has a transverse aperture 118 that
receives a fastening or screw assembly 200 (various versions of
which are shown in FIGS. 19-41) through the intramedullary nail
100. One embodiment of the proximal transverse aperture 118, shown
in FIGS. 1-4, is formed from two overlapping circular apertures
120, 122, where the proximal circle aperture 120 is smaller in
diameter than the distal circle aperture 122. The proximal circle
aperture 120 shown has a shoulder 132 for constraining the
insertion depth of the screw assembly as will be explained in more
detail below. Various other apertures allowing insertion of various
screw assemblies could be used as would be known to those skilled
in the art. For example, FIG. 33 illustrates the intramedullary
nail with a circular aperture. The embodiment of FIG. 33 is
described in greater detail below.
[0065] The proximal section 102 illustrated in FIG. 3 has a
proximal end aperture 128. The proximal end aperture 128 is
threaded to allow for the insertion of a set screw that can be used
to fix the rotational and sliding position of a screw assembly. A
set screw may also include mechanisms for spanning a compression
screw 204 (FIG. 19) and interfering with a lag screw 202 (FIG. 19)
to independently restrict the rotation or sliding of the lag screw
202.
[0066] As shown in FIGS. 1-6, the transition section 104 is tapered
from the proximal section 102 to the distal section 106. The
tapered nature of the transition section 104 creates a press fit in
the intramedullary canal that controls subsidence. The tapered
transition section 104 assists in preventing the nail 100 from
being pressed further down into the intramedullary canal of the
femur than intended.
[0067] In the embodiment of the intramedullary nail 100 shown in
FIGS. 1-6, the cross-section of the transition section 104 is
circular, but the cross-section could vary as known to those
skilled in the art. The cross-section could be anatomically
derived, similar to the cross-section of the proximal section 102,
oval or non-circular. In the embodiment shown in FIGS. 1-6, the
transition section 104 contains a distal transverse aperture 124.
The distal aperture 124 allows the insertion through the
intramedullary nail 100 of a distal locking screw for locking of
the intramedullary nail 100.
[0068] The distal section 106 of the intramedullary nail 100 is
generally cylindrical and is configured to provide a reduced
bending stiffness. The embodiment shown in FIGS. 1-5 has a
longitudinal slot 126 through the center of the distal section 106
that forms two sides 134, 136. The slot reduces bending stiffness
at the distal end of the intramedullary nail 100 and reduces the
chances of periprosthetic fractures.
[0069] FIG. 1D shows an intramedullary nail 100 according to
another embodiment of the invention. This nail features, in its
proximal portions, a noncircular cross section that is symmetrical
with respect to its lateral-medial axis (in this case, preferably
but not necessarily, oval shaped in cross-section), and which
features a centered longitudinal bore (in this case, preferably but
not necessarily, circular in cross-section). This nail achieves
additional stability to the extent it resists twisting in the
medullary canal. It also accomplishes the aim of placing more mass
toward the lateral edge or aspect of the proximal cross section.
Furthermore, it places additional mass toward the medial edge or
aspect, and thus provides additional structure that acts as a
fulcrum to decrease the mechanical advantage of the fastening
assembly which when loaded is the component that imposes tensional
stress on the lateral edge or aspect.
[0070] FIGS. 7-18 illustrate intramedullary nails 100 according to
other embodiments of the invention. FIGS. 7 and 13 illustrate an
intramedullary nail 100 having no longitudinal bore throughout.
[0071] FIGS. 8 and 14 illustrate an intramedullary nail 100 having
stiffness reduction slots 140 in the transition section 104 and the
distal section 106. The stiffness reduction slots 140 reduce the
bending stiffness at the distal end of the intramedullary nail 100
and could be used to receive locking screws in some
embodiments.
[0072] FIGS. 9 and 15 illustrate an intramedullary nail 100 having
three longitudinal slots 138 in the distal section 106 and a
portion of the transition section 104 forming a cloverleaf pattern.
This pattern more readily permits blood flow near the
intramedullary nail 100 and also reduces bending stiffness at the
distal end of the nail 100.
[0073] FIGS. 10 and 16 illustrate an intramedullary nail 100 in
which the distal section 106 and a portion of the transition
section 104 have a series of longitudinal grooves 146. The
longitudinal grooves 146 reduce bending stiffness at the distal
end, provide rotational resistance, and enhance blood flow near the
intramedullary nail 100.
[0074] FIGS. 11 and 17 illustrate an intramedullary nail 100 where
the transition section 104 and the distal section 106 have fins
144. The fins 144 provide rotational resistance for the
intramedullary nail 100.
[0075] FIGS. 12 and 18 illustrate an intramedullary nail 100 having
barbs 142 located on the distal section 106 and a portion of the
transition section 104. The barbs 142 provide rotational resistance
for the intramedullary nail 100.
[0076] Intramedullary nails according to the present invention may
be inserted into a patient by any suitable known technique.
Generally, the intramedullary canal of the bone is prepared with an
appropriate tool to create a void for insertion of the nail. Some
portions of the void may be prepared to be about 1 millimeter
larger than the perimeter of the nail to permit sufficient space
for blood flow after insertion of the nail. A guide pin or wire is
optionally inserted into the prepared medullary canal. The nail is
then introduced into the desired position. If the nail is
cannulated, the nail can be introduced over the guide wire. The
position of the nail may be confirmed by image intensification.
[0077] FIG. 19 shows one embodiment of a tool 300 for preparing a
medullary canal. The tool has a drill bit 302 for reaming and also
a mortise chisel 304. In operation, the drill bit 302 reams out the
medullary canal of the femur and the mortise chisel 304 cuts out a
larger section in the more proximal end of a bone. As shown in FIG.
19, the mortise chisel 304 has an anatomically derived
cross-section of approximately the same shape as the proximal
section of the intramedullary nail. By applying this type of
shaped, mortise chisel, the proximal end of the nail will be better
enabled to seat on cortical bone that has been only minimally
altered. The mortise chisel 304 may be of a wide variety of shapes,
even complicated, asymmetrical shapes. This is advantageous because
it enables a device and method for preparing voids able to accept a
wide variety of shapes of intramedullary nails without merely
over-reaming circular voids. Preparation of an accurately
conforming void is valuable in avoiding unnecessary removal of
healthy bone, and in ensuring stable seating of the nail.
[0078] In operation, the tool 300 of the embodiment shown is
advanced as a unit, with the drill bit 302 reaming and the mortise
chisel 304 cutting simultaneously. The drill bit 302 may be turned
with a power driver, or by hand. Likewise, the entire tool 300 may
be advanced into a medullary canal manually, or advanced with the
assistance of mechanical advantage or power equipment. In other
configurations, the drill bit 302 may be cannulated (not shown)
such that the entire tool 300 is operable over and guided by a
guide wire that has been inserted into the medullary canal.
[0079] In other embodiments, the bit for reaming is a more
traditional reamer that is separate from a cutting tool such as the
mortise chisel 304. The method for preparing a void in such an
instance would include first reaming an opening with a traditional
reamer. A device such as a chisel or a broach, shaped similar to
the intramedullary nail to be implanted, would then be used to
prepare the void. The chisel or broach may be driven in by hand,
with the assistance of a hammer or mallet, or with the use of other
power equipment. A nail consistent with the void prepared would
then be implanted.
[0080] Other custom instruments such as a contoured broach or a
custom router bit and template could be used as well. Broaches have
long been used to prepare openings for hip stems, and the use of a
broach would be familiar to one of skill in the art. A router bit
and template could be use, in effect, to mill out the desired shape
in the bone. Such a method might also be used in combination with
reaming or broaching to create the desired void.
[0081] The intramedullary nail of the present invention can be used
to treat proximal femoral fractures and femoral shaft fractures,
among other fractures of long bones. When used to treat femoral
shaft fractures, the intramedullary nail is secured in the femur by
one or more fastening devices. When used for the treatment of
proximal femoral fractures the intramedullary nail is preferably
used in conjunction with a proximal screw assembly.
[0082] FIGS. 20 and 21 illustrate an intramedullary nail 100
according to one embodiment of the present invention used in
conjunction with a fastener assembly 200 according to one
embodiment of the present invention. This type of fastener assembly
may be used in various other bones and to treat a number of other
indications, but for the purpose of providing an example, it is
being described here in use with the proximal femur. In general,
the screw assembly is useful in any situation where one fragment of
a bone is to be drawn back toward or pushed away from another
fragment of the bone in a controlled manner. The fastener assembly
provides the additional advantage of being configurable to allow
sliding of the assembly in a desired direction after the movement
of the bone fragments has been accomplished.
[0083] As shown in FIG. 21, the axis of the proximal transverse
aperture 118 in the intramedullary nail 100 is angled relative to
the proximal section 102 and in use, is directed towards the
femoral head. In this embodiment of the fastener assembly 200, an
engaging member such as a lag screw 202 is used in conjunction with
a compression device, such as a compression screw 204 or a
compression peg. The screws are configured such that when in use
the circumference of the lag screw 202 partially intersects with
the circumference of the compression screw 204, so that the
compression screw 204 nests partially within the circumference of
the lag screw 202. This particular combination of lag screw 202 and
compression screw 204 are further illustrated in FIGS. 22 through
32. Briefly, the lag screw 202 shown in these figures is intended
to engage the femoral head and to slide in the transverse aperture
118 of the nail 100. The compression screw 204 engages a shoulder
or other structure in nail 100's transverse aperture 118 and also
threads in the portion of lag screw 202 within which compression
screw 204 nests, so that rotation of compression screw 204 controls
sliding of the lag screw 202 relative to the nail 100 and thus
compression of the femoral head against the fracture site.
[0084] The lag screw 202 shown in these drawings includes an
elongate body 206 and threaded end 208. As shown in FIGS. 24 and
25, the threaded end 208 does not include a sharp end, which
reduces the possibility of the cut out through the femoral head.
The elongate body 206 includes a channel 212 that allows for the
positioning of the compression screw 204 partially inside the
circumference of the lag screw 202. The channel 212 includes a
threaded portion 210 that compliments and cooperates with a
threaded section 214 of the compression screw 204. The compression
screw 204 includes a threaded section 214 and a head section 215
The threaded section 214 of the compression screw 204 is configured
such that the threads are relatively flat and smooth at the
exterior surface so that they can easily slide in the aperture and
also reduce the possibility of cut out.
[0085] The lag screw 202 is received in the proximal transverse
aperture 118 and into a pre-drilled hole in the femur so that the
lag screw 202 extends across the break and into the femoral head.
The threaded end 208 of the lag screw 202 engages the femoral head
as the lag screw 202 is rotated within aperture 118 causing its
threaded end 208 to engage the femoral head. The threaded end 208
may be any device for obtaining purchase in the femoral head, and
includes but is not limited to, threads of any desired
configuration including helices, barbs, blades, hooks, expanding
devices, and the like. The placement depth of the lag screw 202
into the femoral head differs depending on the desired compression
of the fracture.
[0086] The compression screw 204 can also be received through the
proximal transverse aperture 118 into a predrilled hole in the
femoral head. The threaded section 214 of the compression screw 204
engages with the threaded portion of the channel 212 of the lag
screw 202. The proximal transverse aperture 118 has an interior
shoulder 132 (FIG. 21) to limit the sliding of the compression
screw 204 in the general medial direction and, therefore, the lag
screw 202, through the aperture 118. When the compression screw 204
is tightened, the compression screw threads 214 engage with the lag
screw channel threaded portion 210 and the compression screw 204
moves in the generally medial direction down the lag screw 202. The
head section 215 of the compression screw 204 engages the shoulder
132 of the proximal transverse aperture 118 preventing the
compression screw 204 from moving further in the general medial
direction. As the compression screw 204 is tightened, the lag screw
202 is drawn in the general lateral direction toward the
intramedullary nail providing compression to the fracture. The
compression screw 204 partially intersecting the circumference of
the lag screw 202 provides greater surface resistance and aids in
the prevention of femoral head rotation. The compression screw 204
therefore acts not only as a part of the mechanism for moving
fragments of the fractured bone relative to one another, but also
directly contacts bone of the femoral head to help prevent the
femoral head from rotating about the axis of the lag screw 202.
[0087] In one embodiment, a set screw (not shown), positioned in
the proximal end aperture 128 of the intramedullary nail, is used
to engage the compression screw 204 and fix the compression screw
204 and lag screw 202 in place. The use of the set screw to fix the
fastener assembly 200 in place is fracture pattern dependent. If a
set screw is not used to engage the fastener assembly, the fastener
assembly 200 can slide within the proximal aperture limited by the
shoulder 132.
[0088] In the embodiment of the lag screw and compression screw
shown in FIGS. 20-32, the diameter of the compression screw 204 is
smaller than the diameter of the lag screw 202. The diameters of
the lag screw and compression screw could be the same or the
diameter of the lag screw could be smaller than the diameter of the
compression screw. The threads of the lag screw and the compression
screw could be a variety of different shapes as known to those
skilled in the art. In general, the purpose of the lag screw is to
obtain purchase in bone, and the purpose of the compression screw
is to engage with and draw or move the lag screw. Any configuration
that permits these functions is within the scope of the
invention.
[0089] The fastener assembly could additionally be configured to
allow the addition of a prosthetic femoral head and neck. In such
an embodiment, the lag screw 202 would be replaced with a
prosthetic head and neck. The neck would fit into the proximal
transverse aperture 118 in the nail 100. The design would be
beneficial where degeneration or re-injury of a repaired femoral
fracture and hip joint later necessitated a total hip arthroplasty
(THA). The decision to accomplish a THA could be made
interoperatively, or after some period of time. Instead of having
to prepare a femur to accept a hip stem as is known in association
with THA, only a small portion of bone would need to be removed,
along with the fastener assembly 200. The prosthetic head and neck
could then be inserted into the proximal transverse aperture 118,
the acetabulum prepared, and the remainder of the THA
completed.
[0090] FIG. 33 is a cross-section view of an intramedullary nail
100 according to another embodiment of the invention with an
alternate fastener assembly 400. The fastener assembly illustrated
is very similar to the compressing fastener assembly of Smith &
Nephew's IMHS.RTM. system, as is more thoroughly disclosed in U.S.
Pat. No. 5,032,125, which is hereby incorporated by reference, and
various related international patents. The improvement of the
device illustrated is that it includes the intramedullary nail 100
with an anatomically derived shape and its multiple advantages as
discussed above. In operation, a sleeve 401 fits through the
intramedullary nail 100, and may be secured to the nail by set
screw, or other effective mechanisms. A sliding lag screw 402 is
able to move axially within the sleeve 401. A compressing screw 404
is threaded into the sliding lag screw 402 such that tightening of
the compressing screw 404 draws the sliding lag screw 402 back into
the sleeve 401. With this mechanism, a bone fragment may be brought
into a desired position, but still permitted to achieve sliding
compression once positioned.
[0091] FIGS. 34-35 illustrate a fastener assembly 200 according to
another embodiment of the invention having a lag screw 202 and a
compression peg 502. As shown in FIG. 34, the lag screw 202 and the
compression peg 502 are configured such that, when in use, the
circumference of the lag screw 202 partially intersects with the
circumference of the compression peg 502, although in some
embodiments the circumferences might be adjacent rather than
intersecting. The lag screw 202 includes an elongate body 206 and
threaded end 208. The lag screw 202 has a key 504 on the channel
212. The compression peg 502 has a slot 503 that is adapted to
receive the key 504 of the lag screw 202. The key 504 and slot 503
can be a variety of complimentary shapes, such as, when considered
in cross section, triangular, D-shaped, key-holed and other shapes
as are apparent to those skilled in the art. In operation, the
compression peg 502 may be moved relative to the lag screw 202 by a
compression tool (not shown) that applies disparate forces between
the compression peg 502 and the lag screw 202, or between the
entire assembly and the intramedullary nail 100.
[0092] In the fastener assembly 200 shown in FIGS. 34-35, the lag
screw 202 is received to slide in a proximal aperture of the
intramedullary nail so that the lag screw 202 extends across the
break and into the femoral head. The threaded end 208 of the lag
screw 202 engages the femoral head. Once the lag screw 200 has been
properly engaged with the femoral head, the compression peg 502 is
inserted in the proximal aperture into a predrilled hole in the
femoral head, in order to prevent further rotation of the lag screw
202 as the slot 503 of the compression peg 502 receives the key 504
of the lag screw 202. By providing more area for resistance, the
compression peg 502 helps to prevent the rotation of the femoral
head on the lag screw 202. The compression peg 502 is fixed in
position in the intramedullary nail 100 by a set screw positioned
in the proximal end aperture of the nail. The lag screw 202 can
slide on the compression peg 502 through the proximal aperture. In
another embodiment, the compression peg 502 has barbs on its
surface.
[0093] A fastener assembly 200 according to another embodiment of
the invention is illustrated in FIGS. 36-37. The fastener assembly
200 of this embodiment has a compression peg 502 and a lag screw
202 similar to the embodiment illustrated in FIGS. 34-35 except
that the key 504 of the lag screw 202 and the slot 503 of the
compression peg 502 have complimentary ratchet teeth 506. The
compression peg 502 is fixed in position in the intramedullary nail
by a set screw positioned in the proximal end aperture. Compression
of the fracture can be achieved by pulling the lag screw in the
general lateral direction. The ratchet teeth 506 allow the lag
screw 202 to move in the general lateral direction, but prevent the
lag screw 202 from moving in the general medial direction. A
compression tool similar to the tool describe in association with
FIGS. 34-35 may be used to accomplish the movement.
[0094] FIGS. 38-39 a fastener assembly 200 according to another
embodiment of the invention having a lag screw 602, a cross hair
screw 610 and a compression screw 604. The lag screw 602 includes
an elongate body 606 and threaded end 608. The elongate body 606 is
semi-circular shaped in cross section. The screws 602, 604, 610 are
configured so that the circumference of the lag screw 602
intersects with the circumferences of the cross hair screw 610 and
the compression screw 604. The elongate body 606 of the lag screw
602 is threaded to compliment and cooperate with a threaded section
602 of the cross hair screw 610. The cross hair screw 610 is
threaded to engage with the lag screw 602 and the compression screw
604. The compression screw 604 includes a threaded portion 614 and
a head portion 612.
[0095] In this embodiment, the lag screw 602, the cross hair screw
610 and the compression screw 604 are received simultaneously to
slide in a proximal aperture of an intramedullary screw. The lag
screw 602 extends across the break and into the femoral head. The
threaded end 608 of the lag screw 602 engages the femoral head. As
compression screw 604 is tightened, the threads 614 of the
compression screw engage the threads of the cross hair screw 610
and lag screw 602, thereby moving the lag screw 602 in the general
lateral direction toward the intramedullary nail providing
compression to the femoral head. The cross hair screw 610 is then
turned causing the compression screw 604 to move in the distal
direction away from the lag screw 602. The fastener assembly 200
can alternatively be configured so that the compression screw 604
moves proximally relative to the lag screw 602. The compression
screw 604 separate from the lag screw 602 helps to prevent rotation
of the femoral head on the lag screw 602 by adding more area for
resistance.
[0096] FIGS. 40-41 illustrate a fastener assembly 200 according to
another embodiment of the invention having a lag screw 702 and a
compression peg 704. The lag screw 702 includes an elongate body
706 and a threaded end 708. The elongate body 706 is semi-circular
shaped in order to allow the compression peg 704 to be positioned
partially inside the circumference of the lag screw 702 for
insertion into the femur and has a key 712 positioned on the
interior side of the elongate body 706. The elongate body 706 also
has an aperture 710 through the body. The compression peg 704 is
generally cylindrical and is sized to fit within the semi-circular
body 706 of the lag screw. The key 712 of the lag screw is received
by a slot 714 in the compression peg 704. The key 712 and slot 714
contain complimentary ratchet teeth.
[0097] In this embodiment, the lag screw 702 and the compression
peg 704 are received simultaneously to slide in a proximal aperture
of an intramedullary screw into a pre-drilled hole in the femur.
The lag screw 702 extends across the break and into the femoral
head. The threaded end of the lag screw 702 engages the femoral
head. A compression tool similar to the tool describe in
association with FIGS. 34-35 may be used to accomplish movement
between the compression peg 704 and the lag screw 702, or between
the entire assembly and the intramedullary nail 100. A set screw
may used to fix the position of the fastener assembly. The set
screw is configured such that when the set screw is tightened a
protrusion on the set screw is received through the slot 710 of the
lag screw 702 and moves the compression screw 704 away from the lag
screw 702. The compression screw 704 separate from the lag screw
702 helps to prevent rotation of the femoral head on the lag screw
by adding more area for resistance.
[0098] FIG. 42 illustrates another embodiment of the invention
where a fastener assembly 200 is employed in cooperation with a
compression plate 150. As illustrated, the devices are being
applied to a femur. The various embodiments of the fastener
assembly 200 disclosed above may be used with a similar compression
plate, and various compression plates may be configured to be
applicable to other parts of the anatomy.
[0099] FIG. 43 illustrates another embodiment of the invention
where a fastener assembly 200 is being used with a periarticular
plate 170. The plate and fastener assembly shown are being applied
to a proximal tibia. The various embodiments of the fastener
assembly 200 disclosed above may be used with a similar
periarticular plate and various periarticular plates may be
configured to be applicable to other parts of the anatomy.
[0100] FIG. 44 illustrates another embodiment of the invention
where a fastener assembly 200 is used in combination with a humeral
nail 190. As illustrated, a head section 212 of compression screw
204 bears against the humerus to draw compression against the
humerus. With the compression force applied to lag screw 202, and
the lag screw 202 affixed to a bone fragment through its threaded
end 208, the bone fragment may be drawn into position for proper
healing. In some circumstances, it may be advantageous to place a
washer or bearing surface (not shown) between the head section 212
and the humeral bone against which the head section 212 compresses.
In yet another variant, the opening in the humerus may be enlarged
such that head section 212 is permitted to penetrate the humerus
and bear against a portion of the humeral nail 190. In such an
embodiment, the fastener assembly 200 would be shorter than
illustrated in FIG. 45 to obtain purchase in the same area of bone
with the threaded end 208. The various embodiments of the fastener
assembly 200 disclosed above may be used with a similar nail and
various nails may be configured to be applicable to other parts of
the anatomy.
[0101] As those skilled in the art will appreciate, the particular
embodiments of this invention described above and illustrated in
the figures are provided for explaining the invention and various
alterations may be made in the structure and materials of the
illustrated embodiments without departing from the spirit and scope
of the invention as described above and in the following
claims.
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