U.S. patent number RE42,837 [Application Number 10/625,390] was granted by the patent office on 2011-10-11 for spinal nucleus implant.
This patent grant is currently assigned to Replication Medical, Inc.. Invention is credited to Gerald Gontarz, Jr., Vladimir Stoy.
United States Patent |
RE42,837 |
Stoy , et al. |
October 11, 2011 |
**Please see images for:
( Certificate of Correction ) ** |
Spinal nucleus implant
Abstract
The present invention is a spinal nucleus implant for
replacement of at least a portion of nucleus pulposus tissue
removed from a spinal disc of a living vertebrate to restore
function of the spinal disc and related vertebral joint. The
implant is an anisotropically swellable, biomimetic xerogel
plastic, having a two phase structure with a hydrophobic phase
having high crystallinity and low water content and with
hydrophilic phase having low crystallinity and high water content
and having a negatively charged lubricious surface. The xerogel
plastic is capable of rehydration and of osmotic movement of liquid
therethrough in response to osmotic pressure change to thereby
increase and decrease liquid content in its hydrated state. The
present invention also relates to surgical implant procedures
utilizing this spinal nucleus implant.
Inventors: |
Stoy; Vladimir (Praha Zapad,
CZ), Gontarz, Jr.; Gerald (Spotswood, NJ) |
Assignee: |
Replication Medical, Inc.
(Cranbury, NJ)
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Family
ID: |
23623986 |
Appl.
No.: |
10/625,390 |
Filed: |
July 23, 2003 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
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Reissue of: |
09410268 |
Sep 30, 1999 |
6264695 |
Jul 24, 2001 |
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Current U.S.
Class: |
623/17.16 |
Current CPC
Class: |
A61L
27/52 (20130101); A61L 27/16 (20130101); A61L
27/50 (20130101); A61L 27/20 (20130101); A61L
27/18 (20130101); A61L 27/44 (20130101); A61F
2/441 (20130101); A61L 27/16 (20130101); A61L
27/52 (20130101); A61L 27/50 (20130101); C08L
33/00 (20130101); C08L 31/00 (20130101); C08L
29/00 (20130101); C08L 27/00 (20130101); C08L
23/00 (20130101); A61L 27/18 (20130101); A61L
27/52 (20130101); A61L 27/50 (20130101); C08L
85/02 (20130101); C08L 83/04 (20130101); C08L
67/00 (20130101); C08L 75/00 (20130101); A61F
2002/30075 (20130101); A61F 2002/4435 (20130101); A61L
2430/38 (20130101); A61F 2/442 (20130101); A61F
2210/0061 (20130101); A61F 2002/444 (20130101) |
Current International
Class: |
A61F
2/44 (20060101) |
Field of
Search: |
;623/17.11-17.16 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
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0 505 634 |
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Sep 1992 |
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EP |
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WO 00/64385 |
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Nov 2000 |
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WO |
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WO 02/076336 |
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Oct 2002 |
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WO |
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Other References
Hudgins, Robert Garryl, Development and Characterization of a
Prosthetic Intervertebral Disc, Published Aug. 16, 1999 (on
information and belief); Copyright 1998, ISBN 978-0-599-17460-3.
cited by other .
Hudgins, R. Garryl, and Muzzy, John D., Polymer Composites, vol.
19, No. 6, 1998, pp. 837-845. cited by other.
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Primary Examiner: Stewart; Alvin J
Attorney, Agent or Firm: Carter, DeLuca, Farrell &
Schmidt, LLP
Claims
What is claimed is:
1. A spinal nucleus implant for replacement of at least a portion
of nucleus pulposus tissue removed from a spinal disc of a living
vertebrate to restore function of said spinal disc and related
vertebral joint, and implantable into the cavity created by said
removal of nucleus pulposus tissue, which comprises: A swellable,
biomimetic plastic, having a hydrophobic phase having high
crystallinity and low water content and with hydrophilic phase
having low crystallinity and high water content, said
.[.biomrimetic.]. .Iadd.biomimetic .Iaddend.plastic having an
inherent shape in which it has a relaxed polymer network in a state
of full hydration, having an insertion shape in which it is at
least partially dehydrated to a xerogel state and formable into a
compacted mode for maximum efficiency of surgical insertion, and
capable of anisotropic expansion due to partial rehydration in situ
into an indwelling shape that substantially conforms to the size
and shape of said cavity and is capable of osmotic movement of
liquid therethrough in response to external pressure change to
thereby increase and decrease liquid content in its hydrated state,
said anisotropically swellable biomimetic plastic having preferred
swelling in a vertical plane and suppressed minimal swelling or
swelling in horizontal planes.
2. The spinal nucleus implant of claim 1 wherein said implant is
anisotropically deformable in its said indwelling shape having
preferred deformability in a vertical plane and suppressed
deformability in horizontal planes under compression in the
vertical plane.
3. The spinal nucleus implant of claim 1 wherein said swellable,
biomimetic plastic is at least partially hydrated in its insertion
xerogel state.
4. The spinal nucleus implant of claim 1 wherein said swellable,
biomimetic plastic has been formed in a physiologically safe form
by being plasticized with a non-toxic liquid in its insertion
xerogel state.
5. The spinal nucleus implant of claim 4 wherein said non-toxic
liquid is present at a concentration less than 50% by weight of the
plasicized .[.anisotropicafly.]. .Iadd.anisotropically
.Iaddend.swellable, .[.biomimnetic.]. .Iadd.biomimetic
.Iaddend.plastic.
6. The spinal nucleus implant according to claim 3 wherein said
non-toxic liquid is selected from the group consisting of glycerol,
glycerol monoacetate, glycerol diacetate, glycerylformal, dimethyl
sulfoxide, water and mixtures thereof.
7. The spinal nucleus implant according to claim 1 wherein said
swellable, biomimetic plastic is a dehydrated anisotropically
swellable plastic wherein both said hydrophobic phase and said
hydrophilic phase each have hydrophobic and hydrophilic aspects and
said hydrophobic phase is a less hydrophilic phase having higher
content of hydrophobic groups and said hydrophilic phase is a less
hydrophobic phase having higher content of hydrophilic groups,
relative to one another.
8. The spinal nucleus implant according to claim 7 wherein said
anisotropically swellable, biomimetic plastic comprises
non-degradable polymer with a carbon-carbon backbone.
9. The spinal nucleus implant according to claim 7 wherein said
less hydrophilic phase is a crystalline phase containing nitric
groups.
10. The spinal nucleus implant according to claim 7 wherein said
hydrophilic phase has hydrophilic groups which are selected from a
group consisting of hydroxyl, carboxyl, carboxylate, amide,
N-substituted amide, amidine and N-substituted amidine.
11. The spinal nucleus implant according to claim 1 wherein said
swellable, biomimetic plastic has water content more than 70% by
weight in said state of .[.fully.]. .Iadd.full .Iaddend.hydration
by deionized water.
12. The spinal nucleus implant according to claim 11 wherein said
swellable, .[.biomimnetic.]. .Iadd.biomimetic .Iaddend.plastic has
water content more than 95% by weight in said state of full
hydration.
13. The spinal nucleus implant according to claim 1 wherein said
more hydrophilic phase is substantially discrete hydrophilic
domains dispersed in a substantially continuous less hydrophilic
domain.
14. The spinal nucleus implant according to claim 1 wherein both
the hydrophilic phase and the hydrophobic phase are substantially
continuous hydrophilic domains and hydrophobic domains forming an
interpenetrating network.
15. The spinal nucleus implant according to claim 1 wherein said
hydrophobic phase contains crystalline polymer phase detectable by
x-ray diffraction.
16. The spinal nucleus implant according to claim 7 wherein said
more hydrophobic phase is substantially discrete crystalline
domains dispersed in a substantially continuous more hydrophilic
domain.
17. The spinal nucleus implant according to claim 1 wherein said
swellable, biomimetic plastic has hydrophilic lubricious
surface.
18. The spinal nucleus implant according to claim 17 wherein said
surface is formed in a gradiented manner with increasing carboxylic
groups from the center of said implant towards its outer
surface.
19. The spinal nucleus implant according to claim 1 wherein said
implantable device has at least the two following structural
components: (a) an inner core from said swellable plastic; and, (b)
an outer jacket that is surrounding said core and made from said
swellable plastic which is, in its fully hydrated state, less
swellable than said inner core.
20. The spinal nucleus implant according to claim 1 including at
least one reinforcing element from a substantially non-swellable
material embedded in said swellable, biomimetic plastic.
21. The spinal nucleus implant according to claim 19 and further
including at least one reinforcing element from a substantially
non-swellable material embedded in said swellable,
.[.biomimnetic.]. .Iadd.biomimetic .Iaddend.plastic wherein said at
least one reinforcing element is located between said jacket and
said core.
22. The-spinal nucleus implant according to claim 20 wherein said
at least one reinforcing element is made from an implantable
material selected from the group consisting of metal, metal alloys,
carbon, ceramics, polymer and combinations thereof.
23. The spinal nucleus implant according to claim 22 wherein said
polymer is selected from a group consisting of acrylic polymer,
methacrylic polymer, polyester, polyurethane, polyurea, polyolefin,
halogenated polyolefin, polysaccharide, vinylic polymer,
polyphosphazene and polysiloxane.
24. The spinal nucleus implant according to claim 19 wherein said
inner core is adherent to and connected to said outer jacket.
25. The spinal nucleus implant according to claim 20 wherein said
reinforcing element is more deformable in axial direction than in
lateral direction under axial stress.
26. The spinal nucleus implant according to claim 20 wherein said
reinforcing element has a general shape selected from the group
consisting of helix, ring, elipsoid, cylinder and bellows.
27. A surgical implant procedure for replacing at least a portion
of nucleus pulposus tissue removed from a spinal disc of a living
vertebrae to restore function of said spinal disc and related
vertebral joint, which comprises: a.) creating a spinal nucleus
implant in the form of an anisotropically swellable, biomimetic
xerogel plastic, having a two phase structure with a hydrophobic
phase having high crystallinity and low water content and with
hydrophilic phase having low crystallinity and high water content,
said xerogel plastic being capable of anisotropic expansion by
rehydration into an inherent shape in which it has a relaxed
polymer network in a state of full hydration, and being capable of
osmotic movement of liquid therethrough in response to external
pressure change to thereby increase and decrease liquid content in
its hydrated state said anisotropically swellable biomimetic
plastic having preferred swelling in a vertical plane and minimal
swelling or suppressed swelling in horizontal planes; b.)
surgically removing at least a portion of nucleus pulposus tissue
from a spinal disc of a living vertebrae to create a cavity; and,
c.) implanting said spinal nucleus implant into said nucleus
pulposus cavity in an at least partially hydrated state.
28. The surgical implant procedure according to claim 27 wherein
said spinal nucleus implant, in said fully hydrated state, has
volume substantially larger than volume of said cavity vacated by
the removal of nucleus pulposus tissue.
29. The surgical implant procedure according to claim 27 wherein
said spinal nucleus implant, in said fully hydrated state, has a
cross-section area substantially equivalent to the cross-section
area of said cavity vacated by the removal of nucleus pulposus
tissue, and height substantially larger than the height of said
cavity, the "height" being the dimension substantial parallel with
the spinal axis and "cross-section area" being the area lateral to
the spinal axis.
30. The surgical implant procedure according to claim 27 wherein
said xerogel plastic swells in situ substantially more in the
direction of the spinal axis than in lateral direction.
31. The surgical implant procedure according to claim 27 wherein
said xerogel plastic is implanted in an anisotropically dehydrated
state in which its volume is less than 50% of the volume of said
cavity vacated by the removal of nucleus pulposus tissue.
32. The surgical implant procedure according to claim 31 wherein
said xerogel plastic in its anisotropically dehydrated state has
the shape optimized for insertion into the cavity through a small
incision in the annulus fibrosus, said shape being an approximate
shape of a cylindrical body.
33. The surgical implant procedure according to claim 31 wherein
said anisotropically dehydrated state is achieved by anisotropical
deformation of said xerogel.
34. The surgical implant procedure according to claim 33 wherein
said anisotropical deformation is achieved by heating the xerogel
above its glass transition temperature, exposing it to deforming
stress in a selected direction, and cooling it down under its glass
transition temperature while still exposed to said deforming
stress.
35. The surgical implant procedure according to claim 33 wherein
said anisotropical deformation is achieved by forming said xerogel
by drying the hydrated swellable plastic under a restraining
stress, preventing shrinking of xerogel in one or more selected
directions.
36. The surgical implant procedure according to claim 35 wherein
said restraining stress is an external stress caused by applying
pressure in axial direction during the dehydration process.
37. The surgical implant procedure according to claim 35 wherein
said restraining stress is created by the presence of internally
embedded structure preventing the shrinking in the direction
lateral to the axis.
38. The surgical implant procedure according to claim 27 wherein
said hydrated implant is under axial stress substantially more
deformable in axial direction than in lateral direction.
.Iadd.39. A spinal disc implant which comprises an implant member
dimensioned for positioning in a cavity defined between adjacent
vertebrae, the cavity having a first height, the implant member
comprising a swellable plastic, whereby upon at least partial
hydration of the implant member, the implant member undergoes
anisotropic expansion and has a capacity to swell to a second
height which is greater than the first height wherein the first
height and the second height are measured along a vertical axis and
the implant member further defines a horizontal axis and a length
extending along the horizontal axis, wherein the capacity to swell
to the second height is greater than a swelling capacity along the
length of the horizontal axis by at least 25%..Iaddend.
.Iadd.40. A spinal disc implant according to claim 39 wherein the
cavity defined between the adjacent vertebrae is the disc
space..Iaddend.
.Iadd.41. A spinal disc implant according to claim 39 wherein the
implant further defines a transverse axis to the vertical axis and
perpendicular to the horizontal axis, the horizontal axis and
transverse axis defining a plane which is transverse to the
vertical axis, the implant having a width which is measured along
the transverse axis, wherein the implant has a capacity to expand
the width along the transverse axis which is at least 25% greater
than the expansion of length measured along the horizontal
axis..Iaddend.
.Iadd.42. A spinal disc implant according to claim 41 wherein the
swelling capacity of the implant member defines a cross-section
area which is substantially equivalent to the cross-section area of
the cavity which has been vacated by removal of nucleus pulposis
tissue of a spinal disc..Iaddend.
.Iadd.43. A spinal disc implant according to claim 42 further
comprising a reinforcing member which assists in limiting the
increase in cross-section area of the implant member..Iaddend.
.Iadd.44. A spinal disc implant according to claim 43 wherein the
reinforcing member is in a form selected from the group consisting
of knitted structure, metal spring and helically wound
fiber..Iaddend.
.Iadd.45. A spinal disc implant according to claim 41 wherein the
length of the implant does not expand along the horizontal
axis..Iaddend.
.Iadd.46. A spinal disc implant according to claim 39 wherein the
swellable plastic is a hydrogel..Iaddend.
.Iadd.47. A spinal disc implant according to claim 39 wherein the
implant member has a water content of more than 70% by
weight..Iaddend.
.Iadd.48. A spinal disc implant according to claim 39 wherein the
implant member is in the form of a xerogel which is dimensioned and
configured for insertion through a small incision in an annulus
fibrosus..Iaddend.
.Iadd.49. A spinal disc implant according to claim 39 wherein the
volume of the implant member fully swelled in body fluid at body
temperature is at least 5% larger than the volume of the cavity
into which the implant is implanted..Iaddend.
.Iadd.50. A spinal disc implant according to claim 39 wherein the
implant is capable of assuming three configurations: (i) an
inherent configuration assumed upon full hydration of the implant,
the inherent configuration having a cross-section area which is
substantially equivalent to the cross-section area of the cavity,
wherein the cavity is formed by removal of nucleus pulposis tissue
of a spinal disc; and the inherent configuration defining the
second height; (ii) an insertion configuration assumed upon at
least partial dehydration of the implant which has a smaller volume
than the inherent configuration, the insertion configuration
dimensioned and configured to facilitate insertion through a small
incision in an annulus fibrosus; and (iii) an indwelling
configuration assumed upon insertion of the implant into the cavity
vacated by removal of nucleus pulposis tissue of a spinal disc, the
indwelling configuration having a cross section area which is
substantially equivalent to the cross-section area of the inherent
configuration, and a height which is less than the height of the
inherent configuration and which is determined by and which
corresponds to the height of said cavity whereby positive swelling
pressure is generated by the implant between the adjacent vertebrae
to increase vertebral separation..Iaddend.
Description
BACKGROUND OF THE INVENTION
1. Field of the Invention
The present invention relates to a spinal nucleus implant to
replace all or a portion of nucleus pulposus which has been removed
form a spinal disc of a living vertebrate, e.g. a human. This
spinal nucleus implant is formed of a xerogel which is capable of
anisotropic swelling.
2. Information Disclosure Statement
Spinal intervertebral disc is a cartilaginous tissue located
between the endplates of adjacent vertebra. The spinal
intervertebral disc acts as a flexible joint between the vertebra,
allowing bending and twisting of the spine column. Damage to the
spinal intervertebral disc can cause spinal dysfunction, crippling
pain and short- or long-term disability. Because of the wide
occurrence of this problem (5% annual incidence of back pain due to
the spinal intervertebral disc is reported), the economic
consequences are enormous. Some disc problems require a surgery.
Typical current procedure is fusion of the adjacent vertebra using
various techniques and devices, such as those described in the U.S.
Pat. No., 4,636,217 (Ogilvie, et al.), U.S. Pat. No. 5,489,308
(Kuslich, et al.) and U.S. Pat. No. 5,716,415 (Steffee). All
currently available surgical procedures, such as removal of the
nucleus or its part (laminectomy), or fusion of adjacent vertebra,
compronise spinal function in one way or another.
For this reason, new remedies are being sought, including the
development of prosthesis of the disc or its part. This is a
difficult undertaking. The spinal column is an extremely intricate
body part, and its proper function is dependent on the seamless
cooperation of all its components, including the vertebral discs. A
vertebral disc has to perform multiple functions. It has to
withstand repeated high stresses in very complex modes of
deformation including combined bending, torque, shear and
compression. In addition, the spinal intervertebral disc acts as an
efficient shock absorber and a pump driving a flow of nutrients
into and metabolites from the disc. Structurally, the disc is a
rather complex composite part involving several types of materials
organized in a complex and intricate fashion. Vertebral endplates
are covered by a layer of hyaline cartilage composed of a collagen
matrix, a glycoprotein component, and water. In addition, about
2-5% of its volume is occupied by living cells producing the
components of the cartilage.
The spinal intervertebral disc itself is composed mainly of
crystalline collagen fibrils and amorphous hydrophilic
proteoglycans. About 3-5% of the volume is occupied by living cells
that produce the its constituents. Structurally, the spinal
intervertebral disc is composed of a hydrogel-like core called the
nucleus pulposus; and an outside ring called the annulus fibrosus.
The structure of the spinal intervertebral disc is schematically
depicted in FIG. 1 and described below.
The spinal intervertebral disc acts primarily as a weight-bearing
and flexible joint. It enables mutual rotation, bending and
translation of the adjacent vertebra, while bearing a considerable
axial load. In addition, the spinal intervertebral disc attenuates
vibrations and mechanical shocks and prevents their propagation
through the skeletal system The load bearing capability and
flexibility in selected directions is achieved by the combination
of the annulus fibrosus and nucleus pulposus. Annulus fibrosus is a
layered structure that is rigid in the radial direction but
deformable in the axial direction and by torque. The axial load is
born by nucleus pulposus that transforms it partly into an axial
component that is contained by the annulus fibrosus. The annulus
fibrosus is formed mainly by collagen fibrils organized in several
layers. Each layer has its collagen fibrils wound at an angle, and
subsequent layers have an alternate orientation. The collagen
organization closely resembles organization of fiber reinforcement
as in composites used for pressure vessels or cords in tires. It
guarantees maximum resistance to radial stress (or internal
pressure) while allowing a deformation in torque and bending.
The fibril ends are attached to the adjacent vertebra and to the
cartilaginous surface of the vertebral endplates. Consequently, the
inner space of the annulus fibrosus is virtually sealed. Any liquid
penetrating in or out of the core has to pass through the annulus
fibrosus tissue or through the vertebral endplates. To achieve
sufficient hydraulic permeability, the collagenous structure of the
annulus fibrosus is supplemented by proteoglycans embedded between
the collagen fibrils. The proteoglycans are hydrated so that the
annulus fibrosus forms a sort of a highly organized, anisotropic
hydrogel composite. The collagen domains form a microfibrillar
mesh. The result of this arrangement is a sufficient deformability
in selected directions combined with high mechanical strength, and
particularly high tear strength and resistance to fracture
propagation that are needed for a load-bearing function.
The nucleus pulposus is connected to the annulus fibrosus, but not
to the endplates. It has much a lower concentration of collagen
(which concentration increases with age) and a higher concentration
of hydrophilic proteoglycans. Consequently, it is a natural
composite which is somewhat like a hydrogel and has a very high
equilibrium water content (more than 90% by weight in young
persons). The water content and volume of nucleus pulposus depends
on osmolarity of swelling medium and on the mechanical pressure.
The resistance to the decrease of liquid content due to mechanical
pressure is called the "swelling pressure". Swelling pressure is
the very key to the function of the nucleus pulposus. As the axial
load expels the liquid, the swelling pressure increases until it
reaches equilibrium with the external load. Accordingly, the
nucleus pulposus is capable of counterbalancing and redistributing
the axial stress, converting them to radial components that can be
confined by the annulus fibrosus. In addition, the dehydration and
rehydration of nucleus pulposus under varying load drives the
transport of metabolites and nutrients in and out the spinal
intervertebral disc. Therefore, the nucleus pulposus acts as an
osmotic pump facilitating transport of nutrient and metabolites to
and from the spinal disc and surrounding tissues. This transport
function is essential because the cartilaginous components (annulus
fibrosus, nucleus pulposus and cartilaginous layer of the vertebral
endplates) are neither vascularized nor can be supported with
nutrition by mere diffusion.
Since the nucleus pulposus is substantially a macroscopically
isotropic tissue, it has to be organized on its molecular and
supermolecular levels to perform all these functions.
The nucleus pulposus structure is rather ingenious. The nucleus
pulposus is constructed from a two-phase composite consisting of
crystalline collagen domains forming a scaffold, and amorphous
glycoprotein domains forming hydrophilic filler. The crystalline
collagen domains are responsible for a relatively high strength
even at high hydration. They form a microfibrillar mesh resembling
the fibrous reinforcement in high-performance composites. The
result of this arrangement is a sufficient deformability combined
with sufficient mechanical strength even at full hydration.
The amorphous domains are responsible for water absorption and for
the generation of a swelling pressure. They are formed mainly by
high-molecular, water-soluble glycoproteoglycans.
Glycoproteoglycans are highly hydrophilic and water-soluble
polymers. A small portion of glycoaminoglycans is covalently bound
to the coilagenous scaffold, turning it hydrophilic and highly
wettable with water (this is necessary for the thermodynamic
stability of the two-phase composite). A large portion is
unattached to the scaffold and is retained by an entrapment within
the scaffold due to the large size of glycoproteoglycans
molecules.
To help this physical retention, glycoproteoglycans chains
associate to form larger units. Glycoproteoglycans chains are
equipped with protein terminal sequences adjusted for attachment to
hyaluronic acid. The complexes of the hyaluronic acid and GPG are
too large to escape from the collagenous scaffold. This is a very
different arrangement than in hydrogels where the confinement of
hydrophilic moieties is achieved by crossliking. One can surmise
that the arrangement in the nucleus pulposus provides a higher
osmotic pressure at a given polymer concentration than the network
arrangement usual in hydrogels.
The glycoproteoglycans in the amorphous phase bear a dense negative
charge. The high negative charge density is important because it
generates high values of viral coefficients and, therefore, causes
maximum swelling pressure at a high water content. The high charge
density is facilitated by the composite structure of the nucleus
pulposus. A synthetic crosslinked hydrogel with a similar charge
density would be brittle and mechanically very weak.
A high negative charge is also responsible for a high surface
hydration that is necessary for a low wet friction. This is
important for the low-friction contact between the nucleus pulposus
and the cartilaginous surfaces of vertebral end plates. A high
friction would probably cause an excessive wear of the cartilage
and degenerative changes in vertebra.
This structural complexity of spinal intervertebral disc is the
consequence of complex requirements, not a whimsical excess of
nature. Therefore, the disc replacement's function, properties and
structure has to be a close approximation of the original disc in
order to be able to perform all its functions. In other words, a
successful disc replacement has to be biomimetic to the maximum
degree achievable.
This was not possible for a long time because there were no
synthetic materials that could replicate structure, properties and
functions of natural tissue. Because of that, most of the
prostheses were designed as mechanical joints enabling certain
movement of vertebra but not replicating all SID properties. Such
prostheses are described, for instance, in the following U.S.
patents: U.S. Pat. No. 3,875,595 (Froning); U.S. Pat. No. 4,349,921
(Kuntz); U.S. Pat. No. 4,309,777 (Patil); U.S. Pat. No. 4,714,469
(Kenna); U.S. Pat. No. 4,904,261 (Dove, et al.); U.S. Pat. No.
4,759,769 (Hedman, et al.); U.S. Pat. No. 4,863,476 (Shepperd);
U.S. Pat. No. 5,053,034 (Olerud); U.S. Pat. No. 5,674,296 (Bryan,
et al.); U.S. Pat. No. 5,676,701 (Yuan, et aL); U.S. Pat. No.
5,824,094 (Serhan, et al.); U.S. Pat. No. 5,865,846 (Bryan, et
al).
The main problem of these devices is limited functionality. Even
more importantly, implantation of these devices is a very complex
procedure requiring a major spine surgery with many associated
risks, long-term recovery and high cost.
There is an ongoing effort to develop better prosthesis of the disc
that would more closely replicate its mechanical function. For
instance, Lee et aL in the U.S. Pat. No. 4,911,718 "Functional and
Biocompatible Intervertebral Spacer" (1990) describe a composite
replacement of the disc made from a biocompatible elastomer
reinforced with fibers that mimics the mechanical properties of the
natural disc. It replicates the disc structure having an
elastomeric core with the shape approximating the shape of nucleus
pulposus, wrapped around by a fiber-reinforced elastomeric layers
replicating structure of annulus fibrosus. The reinforcing fibers
have preferred orientation-simulating arrangement of collagen
fibers in annulus fibrosus. The faces of the assembly are equipped
with tough elastomeric layers simulating the mechanical function of
cartilaginous layers of vertebral endplates. This structure
reasonably closely replicates the spinal intervertebral disc
structure and its mechanical function. However, the implantation of
this device is still very complex and costly, requiring a major
spine surgery.
In many cases, the pain relief requires that only nucleus pulposus
(or even only its part) be removed rather than whole spinal
intervertebral disc. In that case, the major part of the axial load
is directly applied to annulus fibrosus. Annulus fibrosus is now
stressed by the axial rather than radial load for which it is
designed. Consequently, annulus fibrosus delaminates, splits,
fractures and brakes down gradually. The situation is somewhat akin
to driving on a deflated tire. In this situation, it is useful to
replace the missing nucleus pulposus (or its part) to reestablish
the radial stress on annulus fibrosus (or to "reinflate" the spinal
intervertebral disc) that is required for its proper function. The
nucleus pulposus replacement can be carried out by an easier, less
traumatic and less expensive surgical procedure.
It is important to recognize that a successful replacement of
nucleus pulposus has to replicate not only the mechanical function,
but also the function of osmotic pump. Without that, the living
tissue of vertebral endplate cartilages and annulus fibrosus cannot
be maintained in healthy condition. For those reasons, the nucleus
pulposus cannot be replaced by a piece of a hydrophobic,
non-hydrogel elastomer, such as silicone rubber or
polyurethane.
This need to maintain the liquid transport function was first
recognized by Bao et al. in the U.S. Pat. No. 5,047,055. Bao
describes a hydrogel prosthesis that has, in its fully hydrated
state, the shape and size generally conforming to a missing natural
nucleus, i.e., to the cavity left after removal of nucleus pulposus
tissue. The hydrogel used in the implant has, in its fully hydrated
state, water content at least 30% and compressive strength at least
4 MN/m.sup.2 (i.e., 40 kg/cm.sup.2 or 556 psi). This high strength
has to be achieved even at full hydration and at a very high water
content, such as in the preferred range 70 to 90% of liquid.
Conceivably, this very high requirement on mechanical strength is
dictated by possible herniation of isotropic material that was
implanted into damaged and weakened annulus fibrosus. This rather
extreme requirement limits selection of materials useful for this
device, Hydrogels are typically weaker than other plastics and
rubbers, particularly at high water content. Therefore, selection
of high-swelling hydrogels with such a high compressive strength is
rather narrow.
The hydrogel prostheses according to Bao is implanted in partly or
fully dehydrated shape when it is undersized, i.e. its volume is
10-70% of the volume of fully hydrated hydrogel implant.
Consequently, the hydrogel implant can be inserted through a small
incision and then grow into its full size by absorbing aqueous body
fluids. The hydrogel used for the implant has in its fully hydrated
state water content higher than 30%, and preferably between 70 and
90% of liquid. The materials used by Bao are isotropic so that the
implant's expansion due to hydration is equal in all directions.
The implant can be composed from 2 or more pieces of combined size
and shape, if fully hydrated, of the cavity vacated by the nucleus
pulposus removal.
There are several shortcomings of this concept. Hydrogel expansion
is limited to the size of the cavity vacated by the nucleus
pulposus, so that its swelling pressure at the fully hydrated and
expanded state will be very low, or even zero. Therefore, the
implant will not generate sufficient axial force for the vertebral
separation that can be found in the healthy spinal intervertebral
disc. This is different from natural nucleus pulposus that is
underswelled inside the spinal intervertebral disc and generates
positive swelling pressure even at maximum vertebral separation.
Bao could not use such an "oversized design" because the spinal
nucleus implant is implanted into a damaged annulus fibrosus
(either due to surgical incision or due to the original injury) and
expansion of the spinal nucleus implant beyond the cavity size
would cause its extrusion similar to herniation of natural nucleus
pulposus. As Bao notes, bulging of the implant under stress is
prevented by resistance of annulus fibrosus to deformation. Because
the integrity of annulus fibrosus is compromised, hydrogel used in
prosthesis has to be much stronger than natural nucleus pulposus to
resist herniation or extrusion (namely, more than 4 MN/sq.m at full
hydration).
This limitation is caused by the fact that the swelling of the
Bao's the spinal nucleus implant is isotropic, namely, it is the
same in radial and axial directions. Consequently, extensive
expansion in axial direction would cause comparable expansion in
radial direction that would generate pressure against the damaged
annulus fibrosus and cause it rupture, bulging or herniation. In
addition, the hydrogels of the kind described by Bao are isotropic
elastomers, with the same deformability in any direction. In the
described design, the axial load will cause radial deformation,
that will be the largest in the direction of the least resistance,
i.e. in locations where annulus fibrosus has been weakened by the
surgery or by previous injury to the disc. This may result in
bulging, herniation or extrusion of the implant--problems similar
to the disc damage that was the reason for the surgery in the first
place.
Some of these shortcomings were addressed in subsequent invention
by Bao et al. described in the U.S. Pat. No. 5,192,326. The
prosthetic nucleus is formed by a multiplicity of hydrogel beads
having water content at least 30%, said beads being surrounded by a
flexible semipermeable cover. The porous cover has, if fully
extended, the size and shape of the cavity vacated by the nucleus
pulposus removal. The size of the beads is at least three times
larger than size of the pores in said cover so that the hydrogel is
safely confined within the cover. The hydrogel beads can contain as
much as 99% of liquid if fully hydrated. The overall volume of the
fully hydrated hydrogel beads may be greater that the volume of the
cavity vacated by the nucleus pulposus removal, because casing
restricts the swelling and prevents the hydrogel expansion beyond
the internal volume and dimensions of the cover. The cover can be
made of knitted fibers. Preferably, the casing is coated by a
highly biocompatible polymer to prevent adverse reactions to the
implant. However, even with a coating the microporous casing may
induce a foreign body reaction, initiate protein deposition, become
loci of bacterial colonization or cause other problems. The use of
the cover sacrifices some advantages of hydrogels, such as high
biocompatibility and surface lubricity. In addition, the beads have
relatively low packing density and relatively large interstitial
space fraction.
Ray et al. invented somewhat similar designs to '326. In the U.S.
Pat. No. 4,772,287 Ray describes a implant into the nucleus
pulposus composed of two flexible cylindrical bladders filled with
a liquid, preferably a thixotropic liquid. The bladders are
surrounded by strong fibrous casing, preferably combined with a
biodegradable polymer that promotes tissue in growth. Optionally,
the bladders are equipped by tubing for adding or withdrawing
fluid. This device obviously does not replicate the shape and
properties of nucleus pulposus, only attempts to simulate some of
its functions. The fibrous casing is designed to facilitate
integration of the implant into the residual spinal intervertebral
disc tissue, causing thus partial fusion of the vertebral
joint.
In the U.S. Pat. No. 4,904,260 Ray describes an improvement of his
basic design in which the capsule is made of a semipermeable
material and filled with an aqueous liquid containing a therapeutic
material capable of a slow diffusion from the implant into the
tissue.
In the U.S. Pat. No. 5,674,295 Ray describes another improvement of
his basic design in which a hydrogel cylindrical body is used
instead of the liquid-filled bladder. The strong fibrous casing is
designed to allow more swelling in axial direction than in radial
direction, allowing thus sufficient axial expansion while
protecting annulus fibrosus against excessive pressure from the
expanding and/or deformed hydrogel
This design is further modified in the U.S. Pat. No. 5,824,093
(continuation-in-part to the '295) where the hydrogel bodies have
oval crossections and the constraining jacket designed to maintain
the general shape of the hydrogel under full hydration and
load.
In all Ray's designs the device is not mimicking the nucleus
pulposus shape, size, properties or full function. The volume of
the hydrated hydrogel is substantially smaller that the natural
nucleus pulposus volume. The shape of Ray's implant differs
substantially from the nucleus pulposus shape and one could
anticipate certain problems with position stability of such
implants. To improve the stability, porous or fibrous constraining
jacket is incorporated into the residual spinal intervertebral disc
tissue. However, this causes a partial fusion, and thus a partial
immobilization, of the vertebral joint. The Ray's device does not
fill the space designed for nucleus pulposus, which may cause a
tendency to distort and to extrude the device under some
conditions.
As seen from the description, no prior art invention provides a
satisfactory solution to the problem of nucleus pulposus
replacement, and neither teaches the present invention nor renders
the present invention obvious.
Notwithstanding the prior art, the present invention is neither
taught nor rendered obvious thereby.
SUMMARY OF THE INVENTION
This invention relates to a biomimetic spinal nucleus implant
designed to restore the function of spinal disc and vertebral joint
after a part or all of the nucleus pulposus tissue was removed from
the disc of a living vertebrate, e.g. a human. The spinal nucleus
implant according to this invention is a swellable plastic device
capable of anisotropic swelling into a form of hydrogel implant
with anisotropic deformability. The spinal nucleus implant
according to the invention is implantable into spinal disc through
a small incision facilitating thus the surgery, minimizing the
trauma of the surgery and improving the safety of the device.
The invention also relates to the surgical implant procedure
relating thereto.
BRIEF DESCRIPTION OF THE DRAWINGS
The present invention should be more fully understood when the
specification herein is taken in conjunction with the drawings
appended hereto wherein:
FIG. 1 shows an oblique front view of a cross section of a spinal
intervertebral disc and FIG. 2 shows a front expanded cut section
of annular fibers of an annulus laminate of a spinal intervertebral
disc. FIGS. 3, 4, 5 and 6 show oblique front views of various steps
of a present invention surgical implant procedure, showing cavity
creation (nucleus pulposus removal), spinal nucleus implant
insertion, unfolded and fully hydrated;
FIGS. 7, 8, 9 and 10 show oblique front views of spherical,
cylindrical, helixical and ovate spinal nucleus implant; and,
FIGS. 11, 12 and 13 show front cut views of present invention
spinal nucleus implant structures.
FIGS. 14-18 show alternative embodiments of the present
invention.
DETAILED DESCRIPTION OF THE PRESENT INVENTION
The device according to this invention is designed to replicate the
structure and material properties of natural nucleus pulposus to
the extent needed to replicate all its essential functions, to
achieve position stability of spinal nucleus implant implanted in a
weakened annulus fibrosus, and to make spinal nucleus implant
implantable through a small incision.
The preferred spinal nucleus implant according to the present
invention has properties closely mimicking the essential properties
of natural nucleus pulposus, such as: Hydrophilic material with
equilibrium water content around 90% or higher at full hydration;
Two-phase structure comprising domains with high crystallinity and
lower water content {"hydrophobic domains") and domains with low
crystallinity and high water content ("hydrophilic domains"). High
content of carboxylate groups, particularly in hydrophilic domains
with high water content and on the surface of the device.
Associative water-soluble polymers concentrated in hydrophilic
domains with higher water content. Water content strongly dependent
on osmolarity of swelling medium. Highly hydrated negatively
charged lubricious surface.
The spinal nucleus implant according to the present invention also
has the following differences from natural nucleus pulposus: The
implant size, in its fully hydrated state, does not conform to the
natural nucleus pulposus; The implant shape, in its fully hydrated
state, does not conform to the natural nucleus pulposus; Dehydrated
implant has anisotropical swelling with preferred swelling in axial
direction of spine (vertical plane), and suppressed in the radial
direction (horizontal planes); The implant has anisotropical
deformability (it is more deformable axially and more rigid
radially).
These features are explained in more detail below.
In order to replicate or replace the nucleus pulposus functions,
the present invention spinal nucleus implant comprises a material
capable of swelling in the presence of water and is capable of
changing water content in response to external conditions, such as
pressure, temperature, osmolarity or pH. They are two types of
swellable materials suitable for this invention: More organized
hydrophilic composites having some hydrophobicity resembling
structure of cartilaginous tissues, and more homogeneous
hydrogels.
The present invention hydrophilic composites can be of "cellular"
(or "domain") type with continuous hydrophobic domains and discrete
hydrophilic domains, and interpenetrating networks where both types
of domains are continuous.
The preferred material for the spinal nucleus implant is a
synthetic composite of the cellular type with the structure similar
to the nucleus pulposus. The structure comprises strong fibrillar
crystalline phase, and an amorphous phase comprising charged
associative polymers. Polymers involved in the composite are
non-biodegradable, preferably with carbon-carbon backbone. The
preferred types of polymers are multiblock acrylic polymers.
Composites may be of "domain type", in which associative polymers
are located in discrete hydrophilic domains; or of a
"interpenetrating network" type.
The requirements for the spinal nucleus implant according to the
present invention can be also met by certain type of hydrogels.
Contrary to composites, hydrogels are formed by a single type of
network (covalent, physical or combined). Only hydrogels having
certain combination of properties are suitable for the present
invention, as described in more detail below.
According to the present invention, height (ie., the axial
dimension) of the fully hydrated the spinal nucleus implant is
greater than maximum separation between the vertebra in prone
position. The fully hydrated diameter of the spinal nucleus
implant, however, is substantially the same as the diameter of the
cavity vacated by the nucleus pulposus removal.
In the following description, the term "swellable plastic" is used
to include both composites and hydrogels.
Swellable plastics contain one or more polymeric components.
Preferably, swellable plastics suitable for the spinal nucleus
implant comprise polymeric components having C--C backbone. Such
polymers, such as polyvinylalcohol, polyvinyl pyrrolidone or
derivatives of polyacrylic or polymethacrylic acid, are more
resistant to biodegradation than polymers with heteroatoms in their
backbones, such as polyurethanes or polyesters.
Preferably, at least on of the polymeric components contains both
hydrophilic hydrophobic groups.
The preferred swellable plastic comprises two polymer phases of
different hydrophilicity, the less hydrophilic phase having higher
content of hydrophobic groups and more hydrophilic phase having
higher content of hydrophilic groups. The less hydrophilic phase is
preferably crystalline and more hydrophilic phase is preferably
amorphous, as can be established from X-ray diffraction.
The preferred hydrophobic groups are pendant nitrile substituents
in 1,3 positions on polymethylene backbone, such as in
poly(acrylonitrile) or poly(methacrylonitrile). The hydrophilic
phase preferably contains a high concentration of ionic groups.
Preferred hydrophilic groups are derivatives of acrylic acid and/or
methacrylic acids including salts, acrylamidine, N-substituted
acrylamidine, acrylamide and N-substituted acryl amide, as well as
various combinations thereof. The particularly preferred
combination contains approximately two thirds of acrylic acid and
its salts (on molar basis), the rest being a combination of plain
and N-substituted acrylamides and acrylamidines.
At least one polymeric component is preferably a multiblock
copolymer with alternating sequences of hydrophilic and hydrophobic
groups. Such sequences are usually capable of separating into two
polymer phases and form strong physically crosslinked hydrogels.
Such multiblock copolymers can be, for instance, products of
hydrolysis or aminolysis of polyacrylonitrile or
polymethacrylonitrile and copolymers thereof For the sake of
brevity, we will call "PAN" all polymers and copolymers having at
least 80 molar % of acrylonitrile and/or methacrylonitrile units in
their composition. Hydrolysis and aminolysis of PAN and products
thereof are described, for instance, in the U.S. Pat. Nos.
4,107,121; 4,331,783; 4,337,327; 4,369,294; 4,370,451; 4,379,874;
4,420,589; 4,943,618, and 5,252,692 that are incorporated by this
reference.
The swellable plastic can comprise of at least two polymeric
components arranged as interpenetrating network. In that case, one
component is essentially a hydrophobic polymer capable of forming a
reticulated crystalline fibrillar mesh or scaffold. Examples of
such polymers are polyurethane, polyurea, PAN, expanded
polytetrafluoroethylene, cellulose triacetate and polyvinylalcohol.
The spaces between the fibrils are filed by a continuous phase of
hydrophilic polymer with 3-dimensional physical or covalent network
(i.e., a hydrogel such as crosslinked polyvinylalcohol or
polyvinylpyrrolidone). The most suitable hydrogels for this role
are those based on hydrophilic derivatives of polyacrylic and
polymethacrylic acid.
The preferred material for the spinal nucleus implant is a
synthetic composite of a cellular (or domain) type with continuous
phase formed by a hydrophobic polymer or a hydrophilic polymer with
low to medium water content forming a "closed cells" spongy
structure that provides composite with a strength and shape
stability. Examples of suitable polymers are polyurethanes,
polyureas, PAN, polydimethylsiloxanes (silicone rubber), and highly
crystalline multiblock acrylic and methacrylic copolymers. The
polymer has to be sufficiently permeable for water. It is known
that even distinctly hydrophobic polymers, such as silicone rubber,
can form swellable composites. More preferably, the continuous
phase is formed by a strong hydrophilic polymer with sufficient
permeability for water but impermeable for high-molecular solutes.
Examples of such polymers are highly crystalline hydrogels based on
segmented polyurethanes, polyvinylalcohol or multiblock
acrylonitrile copolymers with derivatives of acrylic acid.
Typically, suitable polymers for the continuous phase in cellular
composites have water content in fully hydrated state between about
60% by weight and 90% by weight, preferably between 70 and 85% by
weight.
The second component is a highly hydrophilic polymer of high enough
molecular weight that cannot permeate through the continuous phase.
This component is confined inside the matrix of the continuous
phase. The entrapped hydrophilic polymers may be high-molecular
weight water-soluble polymers, associative water-soluble polymers
or highly swellable hydrogels containing, in fully hydrated state,
at least 95% of water and up to 99.8% of water. Such hydrogels are
very weak mechanically. However, it does not matter in composites
where such polymers' role is generation of osmotic pressure rather
than load-bearing, with compression strength in full hydration in
the range of 0.01 MN/m.sup.2 or lower.
Such system with closed cells (or domains) containing highly
swellable or water-soluble polymers can form composites with very
high swelling pressure as needed for the spinal nucleus implant
function. Examples of suitable hydrophilic polymers are
high-molecular weight polyacrylamide, polyacrylic acid,
polyvinylpyrrolidone, polyethyleneoxide, copolymers of
ethyleneoxide and propyleneoxide or hyaluronic acid; covalently
crosslinked hydrogels such as hydrophilic esters or amides of
polyacrylic or polymethacrylic acids; and physically crosslinked
hydrogels, such as hydrolyzates or aminolyzates of PAN.
Particularly suitable are associative water-soluble polymers
capable of forming very highly viscous solutions or even soft
physical gels. Preferred are associative polymers containing
negatively charged groups, such as carboxylates, sulpho-groups,
phosphate groups or sulfate groups. Particularly preferred are
associative polymers formed by hydrolysis and/or aminolysis of PAN
to high but finite conversions that leave a certain number of
nitrile groups (typically, between 5 and 25 molar %) unreacted.
Preferred composites have both continuous phase and dispersed phase
formed by different products of hydrolysis or aminolysis of PAN. In
this case both components are compatible and their hydrophobic
blocks can participate in the same crystalline domains. This
improves anchorage of the more hydrophilic component and prevents
its extraction. Size of more hydrophilic domains may vary widely,
from nanometers to millimeters, preferably from tens of nanometers
to microns.
The ratio between the continuous a discrete phase (i.e., between
more hydrophobic and more hydrophilic components may vary from
about 1:2 to 1:100 on the dry weight basis, but preferred ratio
ranges from about 1:5 to 1:20.
Any swellable plastic (e.g. a hydrogel) can be characterized in
various ways. The most important characteristic is the liquid
content in the state of full hydration. We use the term "Mill
hydration" in the usual sense, i.e. meaning equilibrium hydration
in full and unrestricted contact with an excess of a liquid of
defined composition at a defined temperature, for a time sufficient
to achieve equilibrium, without any restriction of sample expansion
due to a limited space, availability of swelling liquid or due to
an external load or pressure applied against the hydrogel. Unless
specifically stated otherwise, the liquid medium is an isotonic
unbuffered 0.9% by weight NaCl solution in water, and temperature
is the body temperature of 36.5.degree. C.+/-0.5.degree. C.
Dehydrated swellable plastic is often called "xerogel". Another
characteristic is compression strength. It can be measured
according to ASTM method D695, performed in aqueous immersion.
Unless stated otherwise, compressive strength is meant at full
hydration and ambient temperature.
Swellable plastics used in the present invention has to have the
following basic characteristics: Liquid content in the state of
full hydration with deionized water at ambient temperature higher
than 70% of water and preferably higher than 95% of water. Liquid
content in the state of full hydration with 0.9% aqueous solution
of NaCl at body temperature higher than 65% and preferably higher
than 85% of liquid. Capability of anisotropical swelling, i.e.
capability of a xerogel to expand due to its hydration, even in
absence of an external load or any external restriction, in a
selected direction or directions more than in other directions. For
instance, an anisotropic xerogel rod can increase its diameter
while decreasing its length due to its hydration. Swellable
plastics particularly useful for this invention have modulus of
elasticity increasing with deformation. This is important for
confinement of radial deformation, i.e. prevention of bulging and
herniation under high axial loads. Swellable plastics exhibiting
this type of behavior are typically those containing a crystalline
phase in their structure. Swellable plastics suitable for this
invention are those capable of holding "frozen deformation" and to
release such deformation in fully hydrated state. Such materials
are often called "memory hydrogels" or "memory hydrogel
composites". Particularly useful are those materials that are able
to hold the "frozen deformation" even in plasticized state at
temperatures lower than body temperature. The frozen deformation is
released due to hydration, heating to body temperature or a
combination of both. Swellable plastics particularly useful for
invention are those with high hydraulic permeability. All
hydrophilic plastics, including hydrogels, have relatively high
diffusive permeability for water and aqueous solutes. However, the
spinal nucleus implant application requires different type of
permeability, so called hydraulic permeability, in which the
transport is facilitated by pressure gradient rather than
concentration gradient. Hydraulic permeability can be characterized
by "filtration coefficient" K.sub.f. Swellable plastic suitable for
the present invention have K.sub.f>5.10.sup.-14
[cc.cm-of-thickness/sec.cm.sup.2.(dyn/cm.sup.2)] and preferably
K.sub.f>1.10.sup.-12 [cc.cm-of-thickness/sec.cm.sup.2.
(dyn/cm.sup.2)].
The spinal nucleus implant according to the invention have the
following characteristics:
The spinal nucleus implant has the fully hydrated volume larger
than volume cavity created by a partial or complete removal of
nucleus pulposus. The volume of the spinal nucleus implant fully
swelled in body fluid at body temperature is preferably by at least
5% larger, and more preferably by at least 10% larger than the
volume of the cavity into which the spinal nucleus implant is
implanted. The cavity volume is determined at maximum natural
separation of vertebra, i.e. with the body in horizontal
position.
The spinal nucleus implant according to the invention has three
basic shapes: inherent shape A insertion shape B indwelling shape C
Inherent shape A is corresponding to the most relaxed polymer
network in the state of full hydration of the swellable plastic
(ie., in -the state with minimum free enthalpy). The spinal nucleus
implant in the inherent shape A has cross-section area
substantially equivalent to the cross-section area of the cavity
vacated by the removal of nucleus pulposus tissue, and height
substantial larger than height of such said cavity. (By "height" is
meant the dimension substantially parallel with the spinal axis
while the "cross-section area" is the area lateral to the spinal
axis.) Insertion shape B is the shape of xerogel deformed in such a
way that it facilitates insertion and anisotropic swelling in the
preferred direction of spinal axis. The xerogel in the shape B and
anisotropically dehydrated state has the shape optimized for
insertion into the cavity through a small incision in the annulus
fibrosus. The preferred shape is an approximate shape of a
cylindrical body which length is approximately the length of the
longer axis of the nucleus pulposus cross-section. In presence of
body fluids and absence of an external load or other spatial
restriction. The spinal nucleus implant would spontaneously change
from shape B to shape A. In dwelling shape C is substantially the
shape of the cavity created by the partial or complete removal of
nucleus pulposus tissue. The spinal nucleus implant is implanted in
a partly dehydrated state and in the insertion state A. Once
inserted, it imbibes additional water from body fluids and
increases its volume until it reaches shape C. The volume in the
state C is smaller than in state A and its main dimensions are
different. The spinal nucleus implant is partially dehydrated in
the shape B because the restriction of space and pressure of
surrounding structures does not allow xerogel to reach full
hydration. In the shape C, the xerogel has reached substantially
the fully hydrated cross-section of the state B. Because of that,
it does generate radial swelling pressure that could overly strain
the weakened annulus fibrosus and to cause extrusion or herniation.
However, the height in the shape C is smaller that the fully
hydrated shape A so that the spinal nucleus implant generates
swelling pressure preferentially in axial direction.
Once implanted into the cavity in the disc, the spinal nucleus
implant according to the present invention swells anisotropically
from shape B to shape C, i.e. differently in various directions.
For isotropic swelling, which is typical for hydrogels hitherto
used in the spinal nucleus implant, relative increase of all linear
dimension is the same, and relative increase of any dimension is
cubic root of relative volume expansion. For instance, if volume of
an isotropic hydrogel increases eight times due to the hydration,
any of its linear dimensions (such as thickness, diameter, radius
of curvature etc) is doubled.
In the case of anisotropic swelling, the volume change is achieved
by preferential expansion in selected directions. More
specifically, the spinal nucleus implant according to the present
invention swells after implantation more in axial direction than in
radial direction (with respect to the spine). It can even swell in
the axial direction only, or swell in axial directions while
sharing in radial direction. This anisotropic swelling in preferred
direction allows generation of swelling pressure in axial direction
(that is necessary for vertebral separation) without generating an
excessive radial swelling pressure against annulus fibrosus. This
feature allows the use of the spinal nucleus implant with fully
hydrated volume larger than the cavity volume created by removal of
nucleus pulposus tissue. The relative change in the axial direction
is higher than the relative change in lateral direction by at least
25% and preferably by at least 100% (i.e., is preferably is twice
as large).
Deformed shape B is the shape different from the inherent shape,
with its cross-section minimized in order to facilitate its
insertion through a small incision. The deformed state is stable as
long as the spinal nucleus implant hydrogel is partly or fully
dehydrated and as long as temperature is below glass transition
temperature and/or melting temperature of at least one polymer
phase in the hydrogel The preferred deformed shape B may be that of
a flat disc that can be folded for insertion in a taco-style or
rolled for insertion into an approximately cylindrical shape
("burrito style"). It can be also folded into a shape of letter M
or into other convenient shapes.
The spinal nucleus implant according to the present invention can
be made from one or more parts, each of the parts having
anisotropic swelling of the spinal nucleus implant described above.
Such parts can be individually smaller than the single-piece the
spinal nucleus implant, but can be combined into a part that meets
the essential the spinal nucleus implant requirements described
above. Individual parts can be inserted through-a smaller incision
and combined inside the spinal intervertebral disc cavity to
perform the spinal nucleus implant function.
For instance, the spinal nucleus implant can be formed by a
multitude of individual thin discs, each individually
anisotropically swellable (i.e., increasing thickness rather than
footprint). These discs are stacked inside the spinal
intervertebral disc cavity. Compression during their swelling and
the fact that they cannot become fully hydrated will secure
sufficient adhesion between layers. The mutual position between
layers can be also secured by various means such as sutures, pins,
spikes, adhesive layers and so forth
The spinal nucleus implant in the shape B can be also formed by a
single piece of longitudinal shape (such as a tape) that pushed
inside the cavity through a small incision and "assembled" by
folding or otherwise stacking to form the desired indwelling
shape.
Additional advantage of compound the spinal nucleus implant shapes
is improved liquid transport in and out of the device. Insertion
through a small incision is facilitated by using a swellable
plastic that is sufficiently deformable in the Insertion State.
Because many swellable plastics are rigid or even brittle in
completely dehydrated state, such plastics can be plastizied by a
suitable non-toxic water-miscible liquid such as a salt solution,
glycerol, polyethylene glycol, glyceroldiacetate, glycerolformal,
dimethylsulfoxide and the like, alone or in combination with water.
Another possibility is plastification with a limited about of
water, although long-term control of appropriate water
concentration can be difficult.
The spinal nucleus implant is implanted into a more o less damaged
annulus fibrosus The anisotropic swelling protects the annulus
fibrosus against excessive radial swelling pressure that could lead
to herniation or extrusion of the spinal nucleus implant material.
Additional protection can be provided by an anisotropic
deformability of the spinal nucleus implant. Namely, it is
desirable that the spinal nucleus implant is more deformable in
axial that radial direction. This can be achieved by a multitude of
ways. One way is to use a swellable plastic that increases its
modulus of elasticity with deformation. This type of behavior is
shown by many materials with crystalline component, such as natural
rubber, tendon, cartilage, certain type of composites and
interpenetrating networks.
This type of behavior can be readily detected from mechanical
testing. The benefit can be further improved by radial orientation
of the crystalline network in the spinal nucleus implant device
made from such swellable plastics.
Another method for limiting radial deformation is in using embedded
reinforcement from rigid materials, such as metals, plastics,
polymeric fibers etc. Important is proper construction of the
reinforcement so that it does not restrict axial deformation.
Preferred is helical arrangement, such as embedded metal spring or
helically wound fibers. Another possible arrangement is embedded
stacked concentric rings. One of suitable reinforcement is knitted
structures, e.g. vascular grafts that have similar requirements on
anisotropic deformation. Such grafts are made from medically tested
materials, which is another advantage. Polymeric reinforcement can
be made from medical-grade polyurethanes, polyesters, polyamides
and other polymers of sufficient rigidity.
The reinforcement can be advantageously made of permeable hollow
fibers, preferably medical-grade hollow fibers used for
extracorporeal oxygenators, kidney dialysis or hybrid organs. Such
hollow fibers can improve hydraulic liquid transport that is
critical for the proper the spinal nucleus implant function.
Metallic reinforcement elements, such as rings or helical springs,
can be advantageously used as X-ray markers allowing monitoring of
position and deformation status of the implant. They can be used
either alone or in a combination with another reinforcement or
another X-ray markets.
The spinal nucleus implant is intended as a life-long implant and
its high biocompatibility is highly desirable. This can be achieved
best by designing the spinal nucleus implant with a continuous
highly hydrated surface, preferably with a high content of
negatively charged groups, such as carboxylate groups. Particularly
preferred is a gradiented surface with carboxylate concentration
and hydration increasing from the bulk to the surface. Such
surfaces are not only highly biocompatible, but also have very low
wet friction as to not erode adjacent tissues, such as the hyaline
cartilage of vertebral endplates. Moreover, they will prevent
adhesions that could restrict the implant's movement, impede with
the liquid transport and complicate the implant removal or
replacement if that would become necessary. The preferred method is
described in the copending U.S. Pat. No. 5,939,208 (P. Stoy: Method
for Creation of Biomimetic Surfaces, issued Aug. 17, 1999).
Preferred manufacturing method comprises the following steps: (1)
Fabrication of the device from suitable swellable plastic. This
includes operations such as casting, incorporation of
reinforcement, creation of biomimetic surface layer and other
operations that may be necessary for fabrication of the selected
the spinal nucleus implant design (2) Extraction of impurities in
the state of full hydration of the spinal nucleus implant by a
suitable aqueous liquid, such as distilled water or an isotonic
salt solution. This step may consist of multiple operations,
including swelling with an aqueous solution of a plasticizer, such
as glycerol. (3) Dehydration by evaporation of water to a preset
degree in a deformed state. Essentially an axial pressure is
applied to during the dehydration to impose the deformation. The
pressure can be applied throughout the process, or only at the very
end of the dehydration process. In that case the essentially
dehydrated device is heated, deformed by a pressure using a
suitable instrument, and cooled down. This final step is preferably
carried out under clean room or even sterile conditions. (4)
Sterilization is carried out after or during the dehydration or
deformation process.
The invention and some of the preferred embodiments is further
illustrated by the following non-limiting examples.
EXAMPLES:
Example 1
AQUACRYL 90MD hydrogel was purchased from GelMed International
s.r.o., V Cibulkach 51, Prague 5, Czech Republic. It is described
as acrylic multiblock copolymer with alternating hydrophilic and
hydrophobic blocks, hydrophobic block being composed of
acrylonitrile units, the hydrophilic blocks from a combination of
acrylic acid, acrylamidine and acrylamide units. The molar
composition polymer is reported as follows:
TABLE-US-00001 Acrylonitrile units 55% Acrylic acid units 30%
Acrylamide units 9% Acrylamidine units 6%
The hydrogel contains 98.6% by weight of liquid at fill hydration
by pure water and 90.6% by weight in hydrated in an isotonic NaCl
solution (0.9% by weight of NaCl in water).
Tensile strength at ambient temperature and full hydration by
isotonic solution is 6 kg per square cm. If fully hydrated by
water, the hydrogel is too brittle to measure its tensile or
compressive strength (estimated below 1 kg/sq.cm in both
cases).
AQUACRYL was supplied as 10% by weight polymer solution in sodium
thiocyanate solvent (55% by weight aqueous solution).
AQUACRYL was molded in a semi-open porous mold into approximate
shape (though not all its dimensions) of nucleus pulposus 71, which
is shown in FIG. 14. The footprint or cross-section of nucleus
pulposus is kidney-shaped with the largest dimension approximately
40 mm. If we orient this longest dimension in the direction of
X-axis in orthogonal coordinates, than the largest dimension in the
direction of Y-axis is approximately 20 mm. The height of the space
between two vertebra occupied by nucleus pulposus (in the direction
of spinal axis and Z-axis of the orthogonal system) is
approximately 15 mm. These values are approximate and average. It
has to be understood that dimensions of nucleus pulposus differ
from disc to disc and from person to person. The height also
differs appreciably with time and load applied on the disc.
The porous mold has the cross-section calculated to approximate
dimensions of nucleus pulposus cross-section. Calculation was made
from known volume fractions of polymer component in the starting
solution and the final, fully hydrated hydrogel. The ratio of
volumes of the solution to the gel is reciprocal ratio of volume
fractions of the polymer in the two systems. Then the ratio of any
mold dimension to the corresponding hydrogel dimension is third
cube of the ratio of the corresponding volumes. The height of the
mold is substantially larger than height of nucleus pulposus.
The AQUACRYL solution was fed into the mold and solidified by
coagulation with excess of isotonic saline. Solidified hydrogel was
demolded and thoroughly washed with isotonic solution until all
sodium thiocyanate is removed.
After the washing the main fully hydrated dimensions in isotonic
solution are as follows:
TABLE-US-00002 Length 31 mm Width 18 mm Height 86 mm
The specimen is cut to 25 mm sections and the dried under axial
compression by an increasing load sufficient to maintain the
original cross-sectional dimensions. The drying starts at ambient
temperature. The drying temperature is gradually increased until
reaches 100.degree. C. and xerogel is kept at this temperature for
24 hours. Then it is cooled to ambient temperature. The pressure is
maintained until the cooling is completed. Result of this process
is a xerogel article of crossection approximately 32.times.19 mm
and thickness approximately 2.5 mm. The device in xerogel state is
shown in FIG. 15a as 81 while the same device after reswelling into
its inherent, fully hydrated state is shown in FIG. 15b as 81b.
If this xerogel article is immersed into isotonic saline at body
temperature, it fully hydrates and swells into original dimensions
31.times.18.times.25 mm. The swelling factors in individual axes
are as follows: X=0.97; Y=0.95; Z=10.
Part of nucleus pulposus can be surgically removed to create cavity
of crossection approximating the implant crossection. This device
in its xerogel insertion state is a rigid wafer that can be
inserted into the disc via a horizontal slit incision in annulus
pulposus. The incision can be secured by suture. Once the implant
swells for several hours, in increases it height until it runs
against the upper endplate. The continuing swelling increases
vertebral separation and stretches annulus pulposus into the shape
and tension required for its long-term function. The implant
becomes party hydrated and substantially conforms the shape of the
cavity created by removal of the tissue. The device in its partly
hydrated indwelling state (B) has approximate dimensions of
31.times.18.times.15 mm. The swelling factors in individual axes
are as follows: X=0.97; Y=0.95; Z=6.
Example 2
AQUACRYL 80MD was acquired from the same source as the hydrogel
from Example 1. This grade of AQUACRYL has the same structure and
some functional groups, albeit in different proportion:
TABLE-US-00003 Acrylonitrile units 79.7% Acrylic acid units 13.5%
Acrylamide units 4.1% Acrylamidine units 2.7%
The hydrogel contains 90.3% by weight of liquid at full hydration
by pure water and 79.8% by weight in hydrated in an isotonic NaCl
solution (0.9% by weight of NaCl in water). Tensile strength at
ambient temperature and full hydration by isotonic solution is 17.3
kg per square cm AQUACRYL 80MD was supplied as 10% by weight
polymer solution in sodium thiocyanate solvent (55% by weight
aqueous solution).
VISACRYL T2 associative polymer was purchased from GelMed
International s.r.o., V Cibulkach 51, Prague 5, Czech Republic. It
is described as acrylic multiblock copolymer with alternating
hydrophilic and hydrophobic blocks, hydrophobic block being
composed of acrylonitrile units, the hydrophilic blocks form a
combination of acrylic acid, acrylamidine and acrylamide units.
Part of the amide and amidine units is substituted with
sulfoethylene groups. The molar composition polymer is reported as
follows:
TABLE-US-00004 Acrylonitrile units 22.2% Acrylic acid wiits 51.9%
Acrylamide units 8.5% N-sulfoethylacrylamide units 6.6 Acrylamidine
units 6.1% N-sulfoethylacrylamidine units 4.7%
The polymer is soluble in pure water at an elevated temperature to
form shear-thinning, thixotropic solutions at ambient temperature.
At ambient temperature polymer does not dissolve but forms soft
gels with water concentration 99.5% by weight in pure water and
97.6% by weight in isotonic saline. Polymer was supplied as a
granular gel with 5% by weight of solids.
20 weight parts of VISACRYL T2 concentrate was mixed into 80 weight
parts of AQUACRYL 80MD solution and mixed in a high-speed blender
to form a viscous paste. The mixture was then heated to 60.degree.
C. in a closed vessel for 12 hours to remove entrapped air. The
paste was filled into the mold from Example 1 and coagulated and
washed as described in Example 1. The resulting hydrophilic
composite has liquid content over 90% by weight and improved
modulus of elasticity and swelling pressure as compared to hydrogel
from Example 1. The molded article was soaked for 24 hours in a
mixture of 12.5 weight parts of glycerol, 0.9 weight parts of NaCl
and 86.6 weight parts of deionized water. It was then cut and dried
under stress as described above. After drying, the article was
conditioned for 24 hours in air of 60% relative humidity at ambient
temperature. The resulting spinal nucleus implants are plasticized
and deformable for easier insertion through a small incision. The
xerogel implant can be rolled into the insertion shape shown into a
cylindrical insertion shape shown as 91a in FIG. 16a. Once inserted
into the surgically created cavity, it unfolds and starts its
anisotropic expansion into a partially hydrated insertion shape. If
it is fully hydrated without mechanical restrictions, it swells
into its inherent shape shown as 16b. The implants have similar
anisotropic, but faster swelling and higher swelling pressure than
product described in Example 1.
Example 3
Hydrogel from the Example 1 was processed in the following way:
The polymer solution was diluted to 7.5% to decrease its viscosity
and increase liquid content in the resulting content to 92.3% by
weight of isotonic saline.
A strand of twisted polyester fibers was impregnated with the
solution, wrapped helically around a lattice made from grass fibers
(250 micron diameter) and inserted into the porous mold from
Example 1 that was shortened to 25 mm. The mold was then filled
with the diluted polymer solution and coagulated with tap
water.
After demolding, glass fibers were removed from the gel. The
polyester fiber reinforcement was completely embedded in the
hydrogel, forming helix coaxial with the device. The reinforcement
limited radial deformation of the molding. The channels facilitated
drainage of liquid exuded from the hydrogel under axial
pressure.
The molding was then washed with isotonic saline and soaked in
mixture containing 12.5% of glycerol 0.9% of NaCl and 86.6% of pure
water (all % by weight).
Plasticized hydrogel was then dried under pressure as described in
Example 1. The result was a flexible wafer of elliptic crossection
and thickness 3.5 mm. The wafer can be readily folded or rolled to
facilitate implantation as described in Example 2. After
implantation, the device swells only axially to achieve vertebral
separation by swelling pressure.
It resists radial expansion under pressure, preventing thus
extrusion or herniation in the case that annulus fibrosus is
damaged. FIG. 17a shows the implant 101a in its fully hydrated
inherent shape, where 103a is the embedded helical fibrous
reinforcement in its expanded shape. FIG. 17b shows the implant in
its xerogel insertion shape 101b with the fibrous reinforcement
103b in its compressed state.
Example 4
Cylindrical rod of expanded PTFE (GORTEX, Gore Associates), having
diameter of 25.2 mm and porosity 45%, was used to swellable form
interpenetrating network. The PTFE is axially stretched (up to 3
times) and soaked with a liquid containing 25% glycerol diacetate
and 75% of monomer mixture comprising, HEMA (93.4%), EGDMA (0.5%)
and methacrylic acid (6%), and dibenzoylperoxide (0.1%). Then
axially compressed to 50% of its original length, and the monomers
are polymerized under nitrogen at 65.degree. C. The IPN composite
can be reshaped for a convenient insertion when heated above
80.degree. C., compressed and cooled under compression.
Swelling of the hydrogel component, outside of the PTFE matrix, in
isotonic saline and at body temperature, is 73% by weight. Its
compression strength in fully swollen state and outside of PTFE
matrix is approximately 0.05 MN/m.sup.2. If swollen in isotonic
saline, composite expands primarily in axial direction. The swollen
IPN composite is more deformable in axial direction than in radial
direction. The composite is very strong, resist radial expansion
under axial pressure while generating sufficiently high axial
swelling pressure. Its components are highly biocompatible and
biostable with excellent history in long-term implants. Shape
memory allows maintenance of the deformed insertion shape under
ambient storage conditions. This combination of properties makes
this composite article suitable for use as spinal nucleus
implant.
Example 5
Polymer solution from Example 1 is cast as membrane approximately 2
mm thick. The membrane is soaked in a sodium thiocyanate solution
to equilibrium and then partly dried to a pre-calculated weight.
The conditions were calculated so that the final concentration of
sodium thiocyanate in the swelling liquid is 45% by weight.
Furthermore, rings of 15 mm diameter are made from nickel-titanium
alloy wires with a diameter of 0.75 mm. Foils are now stacked with
wire ring placed between each two layers of foil. The stacked
assembly is then compressed at 95.degree. C. to cause polymer
melting and fusing. After cooling and washing, a block of
hydrophilic polymer with embedded ring-shaped reinforcement is
formed, as shown in its fully hydrated insertion shape in its fully
hydrated insertion shape in FIG. 18 where portion 111a is the
hydrated polymer and 113a is the metal reinforcement. The polymer
is thoroughly washed in isotonic saline and soaked in diluted
glycerol and dried under pressure as described in Example 2.
Referring now to FIG. 1, there is shown a spinal intervertebral
disc 1 of a living vertebrate such as a human or ape. It includes a
nucleus pulposus center 11 and annulus laminates 3, 5, 7 and 9.
FIG. 2 shows a flattened partial section of one annulus laminate 5
indicating fibers at a 60.degree. angle to vertical axis 2.
FIGS. 3, 4, 5 and 6 show oblique front views of the spinal
intervertebral disc of FIG. 1, in various stages of a surgical
procedure of the present invention. Identical parts shown in FIG. 1
are identically numbered in these Figures.
In FIG. 3, an incision 15 has been made and damaged nucleus
pulposus has been removed. Remaining nucleus pulposus is shown as
area 13, adjacent to cavity 17, the space created from the removal
of the damaged nucleus pulposus.
In FIG. 4, present invention spinal nucleus implant 21A is shown in
its partially hydrated folded form and is inserted through incision
15 and into cavity 17. FIG. 5 shows spinal nucleus implant 21B
(unfolded), located within cavity 17, and FIG. 6 shows spinal
nucleus implant 21C and its fully hydrated, enlarged state, subject
to volumetric and liquid content changes resulting from osmotic
pressure changes, stresses, and movements described above. This
spinal nucleus implant is initially formed in accordance with any
of the examples set forth above.
FIGS. 7a, 7b, 8a, 8b, 9a, 9b, 10a and 10b show spinal nucleus
implants of the present invention in various forms. The spinal
nucleus implants of the present invention in their fully hydrated
inherent shapes are shown in the form of sphere 31a, cylinder 33a,
helix 35a, and ovoid 37a, respectively. The same implants in their
xerogel insertion shapes are shown as biconvex lenticular disc 31b,
rolled disc 33b, flattened helix 35b and folded elliptic disc 37b.
All forms may include optional embedded reinforcing structures that
are not shown in the drawings. FIG. 11 shows a top view of a
present invention spinal nucleus implant 39, with a soft, high
water content core 41 and an outer jacket with high crystalline
polymer content 43. At their interface 45, an optional structural
support or transition layer may be included.
FIG. 12 has a present invention spinal nucleus implant 51 with a
core 53 and a jacket 55 and further includes structural support
elements 57a in the core and 57b in the jacket.
FIG. 13 shows a partially cut present invention spinal nucleus
implant sphere 61, cut along line AB. It has a center 63 with a low
polymer content and a high water content with a gradient increasing
in polymer content and decreasing in water content toward outer
layer 69. For example, center 63 may contain ten percent polymer
and ninety percent water and layer 65 may contain eighty percent of
polymer and twenty percent water and layer 67 may contain thirty
percent polymer and seventy percent water and outer surface 69 may
contain even more water with a lubricious, negatively charged
surface.
Obviously, numerous modifications and variations of the present
invention are possible in light of the above teachings. It is
therefore understood that within the scope of the appended claims,
the invention may be practiced otherwise than as specifically
described herein.
* * * * *