U.S. patent application number 11/055406 was filed with the patent office on 2005-12-01 for dual function prosthetic bone implant and method for preparing the same.
This patent application is currently assigned to Calcitec, Inc.. Invention is credited to Ju, Chien-Ping, Lin, Jiin-Huey Chern, Tsai, Chih-Hung.
Application Number | 20050267589 11/055406 |
Document ID | / |
Family ID | 35424292 |
Filed Date | 2005-12-01 |
United States Patent
Application |
20050267589 |
Kind Code |
A1 |
Lin, Jiin-Huey Chern ; et
al. |
December 1, 2005 |
Dual function prosthetic bone implant and method for preparing the
same
Abstract
The present invention discloses a prosthetic bone implant made
of a hardened calcium phosphate cement having an apatitic phase as
a major phase, which includes a dense cortical portion bearing the
majority of load and a porous cancellous portion allowing a rapid
blood/body fluid penetration and tissue ingrowth.
Inventors: |
Lin, Jiin-Huey Chern;
(Winnetka, IL) ; Ju, Chien-Ping; (Carbondale,
IL) ; Tsai, Chih-Hung; (Taichung, TW) |
Correspondence
Address: |
MEYERTONS, HOOD, KIVLIN, KOWERT & GOETZEL, P.C.
P.O. BOX 398
AUSTIN
TX
78767-0398
US
|
Assignee: |
Calcitec, Inc.
|
Family ID: |
35424292 |
Appl. No.: |
11/055406 |
Filed: |
February 10, 2005 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11055406 |
Feb 10, 2005 |
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10852167 |
May 25, 2004 |
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Current U.S.
Class: |
623/23.5 ;
623/23.56 |
Current CPC
Class: |
C04B 28/346 20130101;
C04B 28/346 20130101; A61L 27/56 20130101; C04B 2111/00836
20130101; C04B 22/06 20130101; C04B 38/04 20130101; C04B 40/0028
20130101; C04B 22/082 20130101; C04B 22/16 20130101; C04B 40/0259
20130101; C04B 40/0286 20130101; C04B 40/0286 20130101; C04B 22/10
20130101; C04B 40/0259 20130101; C04B 38/04 20130101; C04B 38/04
20130101; C04B 22/10 20130101; C04B 40/0259 20130101; C04B 40/0028
20130101; C04B 24/04 20130101; C04B 40/0263 20130101; C04B 40/0286
20130101; A61F 2002/30535 20130101; A61F 2250/0058 20130101; C04B
28/346 20130101; C04B 28/346 20130101; A61F 2/28 20130101; A61F
2/4644 20130101; A61L 27/46 20130101 |
Class at
Publication: |
623/023.5 ;
623/023.56 |
International
Class: |
A61F 002/38 |
Claims
1-40. (canceled)
41. A prosthetic bone implant comprising: a load bearing component;
at least one porous component coupled to the load-bearing
component; and at least one transitional component coupling the
load bearing component to the porous component; wherein the load
bearing component and the porous components are at least partially
porous, wherein the porous component is more porous than the load
bearing component, wherein the transitional component comprises a
porosity gradient increasing from the porosity of the porous
component to the porosity of the load bearing component, and
wherein the load bearing component, the porous components and the
transitional components comprise a hardened calcium phosphate
cement.
42. The prosthetic bone implant of claim 41, wherein the porosity
of the porous component is greater than the porosity of the load
bearing component.
43. The prosthetic bone implant of claim 41, wherein the porosity
of the porous component is from about 20% by volume to about 90% by
volume.
44. The prosthetic bone implant of claim 41, wherein the porosity
of the load bearing component is less than about 30% by volume.
45. The prosthetic bone implant of claim 41, wherein the
load-bearing component is adapted to withstand compressive force of
greater than about 35 MPa.
46. The prosthetic bone implant of claim 41, wherein the load
bearing component is adapted to withstand a compressive force of
from about 35 MPa to about 250 MPa.
47. The prosthetic bone implant of claim 41, wherein the load
bearing component is adapted to withstand a compressive force of
from about 110 MPa to about 170 MPa.
48. The prosthetic bone implant of claim 41, wherein the hardened
calcium phosphate cement of the load bearing component and the
hardened calcium phosphate cement of the porous component is made
from at least one calcium phosphate source.
49. The prosthetic bone implant of claim 48, wherein the calcium
phosphate source comprises alpha-tricalcium phosphate
(.alpha.-TCP), beta-tricalcium phosphate (.beta.-TCP), tetracalcium
phosphate (TTCP), monocalcium phosphate monohydrate (MCPN),
monocalcium phosphate anhydrous (MCPA), dicalcium phosphate
dihydrate (DCPD), dicalcium phosphate anhydrous (DCPA), octacalcium
phosphate (OCP), calcium dihydrogen phosphate, calcium dihydrogen
phosphate hydrate, acid calcium pyrophosphate, anhydrous calcium
hydrogen phosphate, calcium hydrogen phosphate hydrate, calcium
pyrophosphate, calcium triphosphate, calcium phosphate tribasic,
calcium polyphosphate, calcium metaphosphate, anhydrous tricalcium
phosphate, tricalcium phosphate hydrate, amorphous calcium
phosphate, or mixtures thereof.
50. The prosthetic bone implant of claim 41, wherein at least a
portion of the hardened calcium phosphate cement of the load
bearing component and at least a portion of the hardened calcium
phosphate cement of the porous component is made from tetracalcium
phosphate.
51. The prosthetic bone implant of claim 41, wherein at least a
portion of the hardened calcium phosphate cement of the load
bearing component and at least a portion of the hardened calcium
phosphate cement of the porous component is made from tetracalcium
phosphate and dicalcium phosphate anhydrous.
52. The prosthetic bone implant of claim 41, wherein at least a
portion of the hardened calcium phosphate cement of the load
bearing component and at least a portion of the hardened calcium
phosphate cement of the porous component is made from apatite.
53. The prosthetic bone implant of claim 52, wherein the molar
ratio of calcium/phosphate of the apatite is about 1.5-2.0.
54. The prosthetic bone implant of claim 41, wherein at least a
portion of the hardened calcium phosphate cement comprising the
load bearing component and the porous component is made from
tetracalcium phosphate, wherein at least a portion of tetracalcium
phosphate particles comprises whiskers on the surface of the
tetracalcium phosphate particles.
55. The prosthetic bone implant of claim 41, wherein the
transitional component comprises a porosity gradient increasing
from the porosity of the porous component to the porosity of the
load bearing component.
56. The prosthetic bone implant of claim 41, wherein the implant is
adapted to allow body fluid and/or tissues to penetrate the implant
when the implant is implanted into a patient.
57. The prosthetic bone implant of claim 41, wherein the porous
components are substantially surrounded by the load bearing
component.
58. The prosthetic bone implant of claim 41, wherein at least a
portion of load bearing component and/or the porous components are
exposed to the surface of the implant.
59. The prosthetic bone implant of claim 41, wherein the
configuration of the porous components relative to the load bearing
component is such that, when the prosthetic bone implant is
implanted into bone, at least a portion of the load bearing
component is coupled to cortical bone, and at least a portion a
porous component is coupled to cancellous bone.
Description
PRIORITY CLAIM
[0001] This application claims priority to Non-Provisional patent
application Ser. No. 10/852,167 entitled "DUAL FUNCTION PROSTHETIC
BONE IMPLANT AND METHOD FOR PREPARING THE SAME" filed on May 25,
2004.
BACKGROUND OF THE INVENTION
[0002] 1. Field of the Invention
[0003] The present invention is related to a prosthetic bone
implant made of a hardened calcium phosphate cement having an
apatitic phase as a major phase, and in particular to a prosthetic
bone implant comprising a dense cortical portion bearing the
majority of load and a porous cancellous portion allowing a rapid
blood/body fluid penetration and tissue ingrowth.
[0004] 2. Description of the Related Art It is advantageous if a
prosthetic bone implant is bioresorbable and is supportive at the
same time. Accordingly, an article made of calcium phosphate will
be preferable than that made of a metal, if the former has strength
which is comparable to a human cortical bone. One way of making
such a bone implant is by sintering a calcium phosphate powder,
particularly a hydroxyapatite (HA) powder, into a block material at
a temperature generally greater than 1000.degree. C. Despite the
fact that the high temperature-sintered HA block material has an
enhanced strength, the bioresorbability of the material is largely
sacrificed, if not totally destroyed, due to the elimination of the
micro- and nano-sized porosity during the sintering process.
[0005] The conventional spinal fusing device is composed of a
metallic cage and a bioresorbable material disposed in the metal
cage, for example the one disclosed in U.S. Pat. No. 5,645,598. An
inevitable disadvantage of this fusion device is the sinking of the
metallic cage sitting between two vertebrae to replace or repair a
defect spinal disk, because the hardness and the relatively small
size of the cage wear out or break the bone tissue, and in
particular the endplate of the vertebra.
SUMMARY OF THE INVENTION
[0006] A primary objective of the invention is to provide a
prosthetic bone implant free of the drawbacks of the prior art.
[0007] The prosthetic bone implant constructed according to the
present invention is made of a hardened calcium phosphate cement
having an apatitic phase as a major phase, which comprises a dense
cortical portion bearing the majority of load and a porous
cancellous portion allowing a rapid blood/body fluid penetration
and tissue ingrowth.
[0008] The prosthetic bone implant of the present invention is made
by a novel technique, which involves immersing an article molded
from two different pastes of calcium phosphate cement (CPC), one of
them having an additional pore-forming powder, in a liquid for a
period of time, so that the compressive strength of the molded CPC
article is significantly improved after removing from the liquid
while the pore-forming powder is dissolved in the liquid, creating
pores in a desired zone or zones of the molded article.
[0009] Features and advantages of the present invention are as
follows:
[0010] 1. Easy process for different shape and size of the
prosthetic bone implant of the present invention, so that the outer
circumferential dense portion thereof can sit over the
circumferential cortical portion of a bone and the porous portion
thereof can contact the cancellous portion of the bone adjacent to
a bone receiving treatment.
[0011] 2. The dense cortical portion of the prosthetic bone implant
made according to the present invention exhibits a high strength
comparable to that of human cortical bone (about 110-170 MPa). The
strength is adjustable by adjusting process parameters.
[0012] 3. The dense cortical portion of the prosthetic bone implant
made according to the present invention contains significant amount
of micro- and nano-sized porosity, that improves bioresorbability
thereof. Conventional high temperature-sintered HA block, on the
other hand, does not possess sufficient micro/nano-sized porosity
and is not bioresorbable.
[0013] 4. The porous cancellous portion of the prosthetic bone
implant made according to the present invention possesses a
porosity greater than 40% in volume, prepferably 40-90%, allowing
rapid blood/body fluid penetration and tissue ingrowth, thereby
anchoring the prosthetic bone implant.
[0014] 5. A wide range of medical application includes bone dowel,
spacer, cavity filler, artificial disc and fixation devices for
spine and other locations, to name a few.
BRIEF DESCRIPTION OF THE DRAWINGS
[0015] FIGS. 1a to 1d show schematic cross sectional views of four
different designs of prosthetic bone implants constructed according
to the present invention.
[0016] FIGS. 2a to 2f are schematic cross sectional views showing
steps of a method for preparing a prosthetic bone implant according
to one embodiment of the present invention.
[0017] FIGS. 3a and 3b are schematic vertical and horizontal cross
sectional views of a prosthetic bone implant prepared according to
another embodiment of the present invention, respectively.
DETAILED DESCRIPTION OF THE INVENTION
[0018] Preferred embodiments of the present invention includes (but
not limited to) the following:
[0019] 1. A prosthetic bone implant comprising a cortical portion
having two opposite sides, and a cancellous portion integrally
disposed in said cortical portion and being exposed through said
two opposite sides, wherein said cortical portion comprises a
hardened calcium phosphate cement has a porosity of less than 40%
in volume, and said cancellous portion comprises a porous hardened
calcium phosphate cement having a porosity greater than 20% in
volume, and greater than that of said cortical portion.
[0020] 2. The implant according to Item 1, wherein the cortical
portion is in the form of a hollow disk, and the cancellous portion
is in the form of a column surrounded by the hollow disk.
[0021] 3. The implant according to Item 2 further comprising a
transitional portion between said column and said hollow disk
surrounding said central cylinder, which has properties range from
those of said cancellous portion to said cortical portion.
[0022] 4. The implant according to Item 1, wherein the cortical
portion is in the form of a disk having one or more longitudinal
through holes, and the cancellous portion is in the form of one or
more columns surrounded by said one or more longitudinal through
holes.
[0023] 5. The implant according to Item 1, wherein said hardened
calcium phosphate cement of said cortical portion comprises an
apatitic phase as a major phase giving rise to broadened
characteristic X-ray diffraction peaks in comparison with a
high-temperature sintered apatitic phase.
[0024] 6. The implant according to Item 5, wherein said broadened
characteristic the X-ray diffraction peaks are at 2-Theta values of
25-27.degree. and 30-35.degree..
[0025] 7. The implant according to Item 1, wherein said hardened
calcium phosphate cement of said cortical portion is prepared
without a high temperature sintering.
[0026] 8. The implant according to Item 1, wherein said hardened
calcium phosphate cement of said cortical portion comprises an
apatitic phase as a major phase having a Ca/P molar ratio of
1.5-2.0.
[0027] 9. The implant according to Item 1, wherein said hardened
calcium phosphate cement of said cancellous portion comprises an
apatitic phase as a major phase giving rise to broadened
characteristic X-ray diffraction peaks in comparison with a
high-temperature sintered apatitic phase.
[0028] 10. The implant according to Item 9, wherein said broadened
characteristic the X-ray diffraction peaks are at 2-Theta values of
25-27.degree. and 30-35.degree..
[0029] 11. The implant according to Item 1, wherein said hardened
calcium phosphate cement of said cancellous portion is prepared
without a high temperature sintering.
[0030] 12. The implant according to Item 1, wherein said hardened
calcium phosphate cement of said cancellous portion comprises an
apatitic phase as a major phase having a Ca/P molar ratio of
1.5-2.0.
[0031] 13.The implant according to Item 1, wherein said cortical
portion comprises 10-90% in volume of said implant.
[0032] 14. The implant according to Item 1, wherein said cortical
portion has a porosity of less than 30% in volume.
[0033] 15. The implant according to Item 1, wherein said cancellous
portion has a porosity greater than 40-90% in volume.
[0034] 16. A method for preparing a prosthetic bone implant
comprising a cortical portion having two opposite sides, and a
cancellous portion integrally disposed in said cortical portion and
being exposed through said two opposite sides, said method
comprises the following steps:
[0035] a) preparing a first paste comprising a first calcium
phosphate cement and a first setting liquid;
[0036] b) preparing a second paste comprising a second calcium
phosphate cement, a pore-forming powder and a second setting
liquid;
[0037] c) i) preparing a shaped article in a mold having two or
more cells separated by one more partition walls comprising
introducing said first paste and said second paste into said two or
more cells separately, and removing said one or more partition
walls from said mold, so that said second paste in the form of a
single column or two or more isolated columns is integrally
disposed in the first paste in said mold; or ii) preparing a shaped
article comprising introducing one of said first paste and said
second paste into a first mold to form an intermediate in said
first mold, placing said intermediate into a second mold after a
hardening reaction thereof undergoes at least partially, and
introducing another one of said first paste ad said second paste
into said second mold, so that said second paste as a single column
or as two or more isolated columns is integrally disposed in the
first paste in said second mold;
[0038] d) immersing the resulting shaped article from step c) in an
immersing liquid for a first period of time so that said
pore-forming powder is dissolved in the immersing liquid, creating
pores in said single column or said two or more isolated columns;
and
[0039] e) removing the immersed shaped article from said immersing
liquid.
[0040] 17. The method according to Item 16 further comprising
[0041] f) drying the immersed shaped article.
[0042] 18. The method according to Item 16, wherein said
pore-forming powder is selected from the group consisting of LiCl,
KCl, NaCl, MgCl.sub.2, CaCl.sub.2, NaIO.sub.3, KI,
Na.sub.3PO.sub.4, K.sub.3PO.sub.4, Na.sub.2CO.sub.3, amino
acid-sodium salt, amino acid-potassium salt, glucose,
polysaccharide, fatty acid-sodium salt, fatty acid-potassium salt,
potassium bitartrate (KHC.sub.4H.sub.4O.sub.6)- , potassium
carbonate, potassium gluconate (KC.sub.6H.sub.11O.sub.7),
potassium-sodium tartrate (KNaC.sub.4H.sub.4O.sub.6.4H.sub.2O),
potassium sulfate (K.sub.2SO.sub.4), sodium sulfate, and sodium
lactate.
[0043] 19. The method according to Item 16, wherein said first
calcium phosphate cement comprises at least one Ca source and at
least one P source, or at least one calcium phosphate source; and
said second calcium phosphate cement comprises at least one Ca
source and at least one P source, or at least one calcium phosphate
source.
[0044] 20. The method according to Item 19, wherein said first
calcium phosphate cement comprises at least one calcium phosphate
source, and said second calcium phosphate cement comprises at least
one calcium phosphate source.
[0045] 21.The method according to Item 20, wherein said calcium
phosphate source is selected from the group consisting of
alpha-tricalcium phosphate (.alpha.-TCP), beta-tricalcium phosphate
(.beta.-TCP), tetracalcium phosphate (TTCP), monocalcium phosphate
monohydrate (MCPM), monocalcium phosphate anhydrous (MCPA),
dicalcium phosphate dihydrate (DCPD), dicalcium phosphate anhydrous
(DCPA), octacalcium phosphate (OCP), calcium dihydrogen phosphate,
calcium dihydrogen phosphate hydrate, acid calcium pyrophosphate,
anhydrous calcium hydrogen phosphate, calcium hydrogen phosphate
hydrate, calcium pyrophosphate, calcium triphosphate, calcium
phosphate tribasic, calcium polyphosphate, calcium metaphosphate,
anhydrous tricalcium phosphate, tricalcium phosphate hydrate, and
amorphous calcium phosphate.
[0046] 22. The method according to Item 21, wherein said first
calcium phosphate cement and said second calcium phosphate cement
are identical.
[0047] 23. The method according to Item 22, wherein said first
calcium phosphate cement and said second calcium phosphate cement
are tetracalcium phosphate.
[0048] 24. The method according to Item 16, wherein the first
setting liquid and the second setting liquid independently are an
acidic solution, a basic solution, or a substantially pure
water.
[0049] 25. The method according to Item 24, wherein said acidic
solution is selected from the group consisting of nitric acid
(HNO.sub.3), hydrochloric acid (HCl), phosphoric acid
(H.sub.3PO.sub.4), carbonic acid (H.sub.2CO.sub.3), sodium
dihydrogen phosphate (NaH.sub.2PO.sub.4), sodium dihydrogen
phosphate monohydrate (NaH.sub.2PO.sub.4.H.sub.2O), sodium
dihydrogen phosphate dihydrate, sodium dihydrogen phosphate
dehydrate, potassium dihydrogen phosphate (KH.sub.2PO.sub.4),
ammonium dihydrogen.phosphate (NH.sub.4H.sub.2PO.sub.4), malic
acid, acetic acid, lactic acid, citric acid, malonic acid, succinic
acid, glutaric acid, tartaric acid, oxalic acid and their
mixture.
[0050] 26. The method according to Item 22, wherein said basic
solution is selected from the group consisting of ammonia, ammonium
hydroxide, alkali metal hydroxide, alkali earth hydroxide, disodium
hydrogen phosphate (Na.sub.2HPO.sub.4), disodium hydrogen phosphate
dodecahydrate, disodium hydrogen phosphate heptahydrate, sodium
phosphate dodecahydrate (Na.sub.3PO.sub.4.12H.sub.2O), dipotassium
hydrogen phosphate (K.sub.2HPO.sub.4), potassium hydrogen phosphate
trihydrate (K.sub.2HPO.sub.4.3H.sub.2O), potassium phosphate
tribasic (K.sub.3PO.sub.4), diammonium hydrogen phosphate
((NH.sub.4).sub.2HPO.sub- .4), ammonium phosphate trihydrate
((NH.sub.4).sub.3PO.sub.4.3H.sub.2O), sodium hydrogen carbonate
(NaHCO.sub.3), sodium carbonate Na.sub.2CO.sub.3, and their
mixture.
[0051] 27. The method according to Item 16, wherein step c-i)
further comprises allowing said first paste and said second paste
undergoing a hardening reaction in said mold.
[0052] 28. The method according to Item 16, wherein step c-i)
further comprises pressurizing said first paste and said second
paste in said mold after removing said one or more partition walls
from said mold to remove a portion of liquid from said first paste
and said second paste, so that a liquid/powder ratio of said first
paste and of said second paste decreases; and allowing said first
paste and second paste undergoing a hardening reaction in said
mold.
[0053] 29. The method according to Item 16, wherein step c-ii)
further comprises allowing said intermediate undergoing a hardening
reaction in said first mold, and allowing said another one of said
first paste and said second paste undergoing a hardening reaction
in said second mold.
[0054] 30. The method according to Item 16, wherein step c-ii)
further comprises pressurizing said one of said first paste and
said second paste in said first mold to remove a portion of liquid
therefrom before the hardening reaction of said intermediate is
completed; allowing said intermediate undergoing a hardening
reaction in said first mold; pressuring said another one of said
first paste and said second paste in said second mold, so that a
liquid/powder ratio of said another one of said first paste and of
said second paste decreases; and allowing said another one of said
first paste and second paste undergoing a hardening reaction in
said second mold.
[0055] 31. The method according to Item 28, wherein said pressuring
is about 1 to 500 MPa.
[0056] 32. The method according to Item 30, wherein said pressuring
is about 1 to 500 MPa.
[0057] 33.The method according to Item 16, wherein the immersing
liquid is an acidic aqueous solution, a basic aqueous solution, a
physiological solution, an organic solvent, or a substantially pure
water.
[0058] 34. The method according to Item 33, wherein the immersing
liquid comprises at least one of Ca and P sources.
[0059] 35. The method according to Item 33, wherein the immersing
liquid is a Hanks' solution, a HCl aqueous solution or an aqueous
solution of (NH.sub.4).sub.2HPO.sub.4.
[0060] 36. The method according to Item 16, wherein the immersing
in step d) is carried out for a period longer than 10 minutes.
[0061] 37. The method according to Item 16, wherein the immersing
in step d) is carried out for a period longer than 1 day.
[0062] 38. The method according to Item 16, wherein the immersing
in step d) is carried out at a temperature of about 10 and
90.degree. C.
[0063] 39. The method according to Item 38, wherein the immersing
in step d) is carried out at room temperature.
[0064] 40. The method according Item 17 further comprising cleaning
said immersed shaped article before said drying; and heating the
resulting dried shaped article at a temperature between 50 and
500.degree. C.
[0065] Four different designs of prosthetic bone implants
constructed according to the present invention are shown in FIGS.
1a to 1d. In FIG. 1a, the prosthetic bone implant of the present
invention has a dense cortical portion D1 in the tubular form and a
porous cancellous portion P1 formed in the central through hole of
the tubular cortical portion D1. Both the dense cortical portion D1
and the porous cancellous portion P1 are made of a hardened calcium
phosphate cement having an apatitic phase as a major phase. In FIG.
1b, the prosthetic bone implant of the present invention has a
dense cortical portion D1 in the tubular form; a cylindrical porous
cancellous portion P1 in the center of the tubular cortical portion
D1; and an annular transitional portion P2 connecting the tubular
cortical portion D1 and the cylindrical cancellous portion P1. The
transitional portion P2 is made of a hardened calcium phosphate
cement having an apatitic phase as a major phase, and a porosity
gradient increasing from the lower porosity of the cylindrical
cancellous portion P1 to the higher porosity of the tubular
cortical portion D1, which may be formed in-situ during molding of
two different two different CPC pastes, one of them having an
additional pore-forming powder for forming the cylindrical
cancellous portion P1, and another one being a regular CPC powder
for forming the dense cortical portion D1. The porous cancellous
portion P1 may be in the forms of isolated columns surrounded by
the dense cortical portion D1 as shown in FIGS. 1c and 1d. Other
designs are also possible in addition to those shown in FIGS. 1a to
1d.
[0066] A suitable method for preparing the prosthetic bone implant
of the present invention includes placing a tubular partition wall
10 in a hollow cylindrical mold 20, as shown in FIG. 2a; pouring a
first paste comprising a calcium phosphate cement and a setting
liquid in the annular cell and a second paste comprising the
calcium phosphate cement, a pore-forming powder and the setting
liquid in the central cell, as shown in FIG. 2b; removing the
partition wall and pressing the CPC pastes before hardening, as
shown in FIG. 2c, wherein a portion of the setting liquid is
removed from the gap between the mold 20 and the press 30 and/or
holes (not shown in the drawing) provided on the press 30. The CPC
paste will undergo a hardening reaction to convert into apatitic
phase. The hardened disk is removed from the mold and is subjected
to surface finishing to expose the central portion hardened from
the second paste, as shown in FIG. 2d, followed by immersing in a
bath of an immersing liquid as shown in FIG. 2e, where the
pore-forming powder is dissolved in the immersing liquid while the
hardened CPC thereof gaining compressive strength. The immersing
may last from 10 minutes to several days. The composite disk so
formed is washed with water after being removed from the bath, and
dried and heated in an oven to obtain the prosthetic bone implant
as shown in FIG. 2f. The heating is conducted at a temperature
between 50 and 500.degree. C. for a period of several hours to
several days, which enhance the compressive strength of the
cortical portion of the prosthetic bone implant.
[0067] An alternative method for preparing the prosthetic bone
implant of the present invention from the same raw materials
includes pouring the second paste in a first mold, pressing the
second paste to remove a portion of the setting liquid from the
second paste before the hardening reaction is completed, so that
the liquid/powder ratio in the second paste decreases, and allowing
the hardening reaction undergo in the mold for a period of time,
e.g. 15 minutes starting from the mixing of the CPC powder, the
pore-forming powder and the setting liquid, to obtain a cylindrical
block having a diameter of 7 mm. Then, the cylindrical block is
removed from the first mold, and placed in the center of a second
mold having a diameter of 10 mm. The first paste is poured into the
annular space in the second mold, and a press having a dimension
corresponding to the annular shape is used to pressure the first
paste to remove a portion of the setting liquid from the first
paste before the hardening reaction is completed, so that the
liquid/powder ratio in the first paste decreases. Again, the first
paste will undergo a hardening reaction to convert into apatitic
phase. The hardened cylinder having a diameter of 10 mm is removed
from the second mold, followed by immersing in an immersing liquid,
where the pore-forming powder contained in the second paste is
dissolved in the immersing liquid while the hardened CPC thereof
gaining compressive strength, to obtain the prosthetic bone implant
of the present invention, as shown in FIGS. 3a and 3b. It is
apparently to people skilled in the art that the prosthetic bone
implant shown in FIGS. 3a and 3b can also be prepared by changing
the sequence of the molding of the first paste and the second paste
with modifications to the second mold used in this alternative
method.
[0068] The following examples are intended to demonstrate the
invention more fully without acting as a limitation upon its scope,
since numerous modifications and variations will be apparent to
those skilled in this art.
PREPARATIVE EXAMPLE 1
Preparation of TTCP Powder
[0069] A Ca.sub.4(PO.sub.4).sub.2O (TTCP) powder was prepared by
mixing Ca.sub.2P.sub.2O.sub.7 powder with CaCO.sub.3 powder
uniformly in ethanol for 24 hours followed by heating to dry. The
mixing ratio of Ca.sub.2P.sub.2O.sub.7 powder to CaCO.sub.3 powder
was 1:1.27 (weight ratio) and the powder mixture was heated to
1400.degree. C. to allow two powders to react to form TTCP.
PREPARATIVE EXAMPLE 2
Preparation of Conventional TTCP/DCPA-Based CPC Powder (Abbreviated
as C-CPC)
[0070] The resulting TTCP powder from PREPARATIVE EXAMPLE 1 was
sieved and blended with dried CaHPO.sub.4 (DCPA) powder in a ball
mill for 12 hours. The blending ratio of the TTCP powder to the
DCPA powder was 1:1 (molar ratio) to obtain the conventional CPC
powder. Particles of this C-CPC powder have no whisker on the
surfaces thereof.
PREPARATIVE EXAMPLE 3
Preparation of Non-Dispersive TTCP/DCPA-Based CPC Powder
(Abbreviated as ND-CPC)
[0071] The TTCP powder prepared according to the method of
PREPARATIVE EXAMPLE 1 was sieved and blended with dried CaHPO.sub.4
(DCPA) powder in a ball mill for 12 hours. The blending ratio of
the TTCP powder to the DCPA powder was 1:1 (molar ratio). The
resultant powder mixture was added to a 25 mM diluted solution of
phosphate to obtain a powder/solution mixture having a
concentration of 3 g powder mixture per 1 ml solution while
stirring. The resulting powder/solution mixture was formed into
pellets, and the pellets were heated in an oven at 50.degree. C.
for 10 minutes. The pellets were then uniformly ground in a
mechanical mill for 20 minutes to obtain the non-dispersive
TTCP/DCPA-based CPC powder (ND-CPC). The particles of this ND-CPC
powder have whisker on the surfaces thereof.
[0072] Dense Blocks
EXAMPLE 1
Effect of Immersion Time on Compressive Strength of CPC Block
[0073] To a setting solution of 1 M phosphoric acid solution
(pH=5.89) the ND-CPC powder from PREPARATIVE EXAMPLE 3 was added in
a liquid/powder ratio (L/P ratio) of 0.4, i.e. 4 ml liquid/10 g
powder, while stirring. The resulting paste was filled into a
cylindrical steel mold having a length of 12 mm and a diameter of 6
mm, and was compressed with a gradually increased pressure until a
maximum pressure was reached. The maximum pressure was maintained
for one minute, and then the compressed CPC block was removed from
the mold. At the 15.sup.th minute following the mixing of the
liquid and powder, the compressed CPC block was immersed in a
Hanks' solution for 1 day, 4 days, and 16 days. Each test group of
the three different periods of immersion time has five specimens,
the compressive strength of which was measured by using a AGS-500D
mechanical tester (Shimadzu Co., Ltd., Kyoto, Japan) immediately
following the removal thereof from the Hanks' solution without
drying. The CPC paste in the mold was compressed with a maximum
pressure of 166.6 MPa, and in the course of the compression the
compression speeds were about 5 mm/min during 0.about.104.1 MPa; 3
mm/min during 104.1.about.138.8 MPa; 1 mm/min during
138.8.about.159.6 MPa: and 0.5 mm/min during 159.6.about.166.6 MPa.
The measured wet specimen compressive strength is listed Table
1.
1TABLE 1 Compressive Immersion time (Day) strength (MPa) Standard
deviation (MPa) No immersion 37.3* 0.6 1 day 149.2 12.9 4 days
122.7 6.7 16 days 116.4 7.7 *This value was measured before the
compressed CPC blocks were immersed in the Hanks' solution, and it
was substantially the same for the compressed CPC blocks not
immersed in the Hanks' solution measured a few days after the
preparation.
[0074] It can seen from Table 1 that the compressive strength of
the compressed CPC blocks is increased remarkably after one-day
immersion in comparison with the non-immersed block, and declines a
little for a longer immersion time.
EXAMPLE 2
Effect of Whiskers on Compressive Strength of TTCP/DCPA-Based CPC
Block
[0075] The procedures of EXAMPLE 1 were repeated by using the C-CPC
powder prepared in PREPARATIVE EXAMPLE 2 and the ND-CPC powder
prepared in PREPARATIVE EXAMPLE 3. The maximum pressure used to
compress the CPC paste in the mold in this example was 156.2 MPa.
The results for one-day immersion time are listed in Table 2.
2 TABLE 2 Compressive Standard CPC powder strength (MPa) deviation
(MPa) C-CPC (no whisker) 62.3 5.0 ND-CPC (with whisker) 138.0
8.2
[0076] It can be seen from Table 2 that the compressive strength,
62.3 MPa, of the immersed compressed CPC block prepared from the
conventional CPC powder (no whisker) is about 1.7 times of that
(37.3 MPa) of the non-immersed compressed CPC block in Table 1, and
the compressive strength, 138.0 MPa, of the immersed compressed CPC
block prepared from the non-dispersive CPC powder (with whisker) is
about 3.7 times of that of the non-immersed compressed CPC block in
Table 1
EXAMPLE 3
Effect of Whiskers on Compressive Strength of TTCP-Based CPC
Block
[0077] Ca.sub.4(PO.sub.4).sub.2O (TTCP) powder as synthesized in
PREPARATIVE EXAMPLE 1 was sieved with a #325 mesh. The sieved
powder has an average particle size of about 10 .mu.m. To the TTCP
powder HCl aqueous solution (pH=0.8) was added according to the
ratio of 1 g TTCP/13 ml solution. The TTCP powder was immersed in
the HCl aqueous solution for 12 hours, filtered rapidly and washed
with deionized water, and filtered rapidly with a vacuum pump
again. The resulting powder cake was dried in an oven at 50.degree.
C. The dried powder was divided into halves, ground for 20 minutes
and 120 minutes separately, and combined to obtain the
non-dispersive TTCP-based CPC powder, the particles of which have
whisker on the surfaces thereof. A setting solution of diammonium
hydrogen phosphate was prepared by dissolving 20 g of diammonium
hydrogen phosphate, (NH.sub.4).sub.2HPO.sub.4, in 40 ml deionized
water. The procedures in EXAMPLE 1 were used to obtain the wet
specimen compressive strength for one-day immersion time, wherein
the maximum pressure to compress the CPC paste in the mold was
156.2 MPa. The results are shown in Table 3.
3 TABLE 3 Compressive Standard CPC powder strength (MPa) deviation
(MPa) TTCP (no whisker) 79.6 8.8 TTCP (with whisker) 100 4.2
[0078] The trend same as the TTCP/DCPA-based CPC powder in Table 2
of EXAMPLE 2 can be observed in Table 3.
EXAMPLE 4
Effect of Molding Pressure on Compressive Strength of ND-CPC Block
(in Low Pressure Regime: 0.09.about.3.5 MPa)
[0079] The procedures of EXAMPLE 1 were repeated except that the
maximum pressure used to compress the CPC paste in the mold was
changed from 166.6 MPa to the values listed in Table 4. The period
of immersion was one day. The results are listed in Table 4.
4TABLE 4 Pressure for compressing the CPC paste in mold Compressive
Standard (MPa) strength (MPa) deviation (MPa) 0.09 12.3 2.0 0.35
16.0 2.3 0.7 20.7 2.5 1.4 26.4 1.4 3.5 35.2 3.7
[0080] The data in Table 4 indicate that the compressive strength
of the CPC block increases as the pressure used to compress the CPC
paste in the mold increases.
EXAMPLE 5
Effect of Reducing Liquid/Powder Ratio During Compression of the
CPC Paste in the Mold on Compressive Strength of ND-CPC Block
[0081] The procedures of EXAMPLE 1 were repeated except that the
maximum pressure used to compress the CPC paste in the mold was
changed from 166.6 MPa to the values listed in Table 5. The liquid
leaked from the mold during compression was measured, and the
liquid/powder ratio was re-calculated as shown in Table 5. The
period of immersion was one day. The results are listed in Table
5.
5TABLE 5 Pressure for compressing the L/P ratio (after Compressive
Standard CPC paste in a portion of strength deviation mold (MPa)
liquid removed) (MPa) (MPa) 1.4 0.25 26.4 1.4 34.7 0.185 75.3 3.9
69.4 0.172 100.4 6.8 156.2 0.161 138.0 8.2 166.6 0.141 149.2
12.9
[0082] The data in Table 5 show that the compressive strength of
the CPC block increases as the liquid/powder ratio decreases during
molding.
EXAMPLE 6
Effect of Post-Heat Treatment on Compressive Strength of CPC
Block
[0083] The procedures of EXAMPLE 1 were repeated. The period of
immersion was one day. The CPC blocks after removing from the
Hanks' solution were subjected to post-heat treatments: 1)
50.degree. C. for one day; and 2) 400.degree. C. for two hours with
a heating rate of 10.degree. C. per minute. The results are listed
in Table 6.
6 TABLE 6 Compressive Standard strength (MPa) deviation (Mpa) No
post-heat treatment 149.2 12.9 50.degree. C., one day 219.4 16.0
400.degree. C., two hours 256.7 16.2
[0084] It can be seen from Table 6 that the post-heat treatment
enhances the compressive strength of the CPC block.
[0085] Porous Blocks
EXAMPLE 7
Effect of KCl Content and Immersion Time on Compressive Strength of
Porous CPC Block
[0086] To a setting solution of 1 M phosphoric acid solution
(pH=5.89) the ND-CPC powder from PREPARATIVE EXAMPLE 3 was added in
a liquid/powder ratio (L/P ratio) of 0.4, i.e. 4 ml liquid/10 g
powder, while stirring. KCl powder in a predetermined amount was
mixed to the resulting mixture by stirring intensively. The
resulting paste was filled into a cylindrical steel mold having a
length of 12 mm and a diameter of 6 mm, and was compressed with a
gradually increased pressure until a maximum pressure of 3.5 MPa
was reached. The maximum pressure was maintained for one minute,
and then the compressed CPC block was removed from the mold. At the
15.sup.th minute following the mixing of the liquid and powders,
the compressed CPC block was immersed in a deionized water at
37.degree. C. for 4 days, 8 days, and 16 days. The compressive
strength of the specimens of the three different periods of
immersion time was measured by using a AGS-500D mechanical tester
(Shimadzu Co., Ltd., Kyoto, Japan) after the specimens were dry.
The measured dry specimen compressive strength is listed Table
7.
7 TABLE 7 Dry compressive strength (MPa) Immersion time (Day)
KCl/CPC ratio by weight 4 days 8 days 16 days 1 7.0 5.4 6.6 1.5 3.9
2.7 4.3 2 1.3 2.3 2.6
[0087] It can seen from Table 7 that the dry compressive strength
of the porous CPC blocks decreases as the KCl/CPC ratio by weight
increases.
EXAMPLE 8
Porosity and Compressive Strength of Porous CPC Blocks Prepared
from Different Pore-Forming Powders
[0088] The procedures of EXAMPLE 7 were repeated by using sugar,
KI, C.sub.17H.sub.33COONa and C.sub.13H.sub.27COOH instead of KCl.
The immersion time was 14 days in deionized water. In the cases
where the C.sub.17H.sub.33COONa and C.sub.13H.sub.27COOH were used,
the CPC blocks were further immersed in ethanol for additional four
days. The conditions and the results are listed in Table 8.
8TABLE 8 Pore-forming powder S.sup.a) C.S. (MPa).sup.b) Porosity
(vol %).sup.c) Sugar 1 4.1 58.4 KI 2 4.3 62.2 KI 3 1.7 75.5
C17H33COONa 1 8.0 56.0 C13H27COOH 2 5.9 60.1 .sup.a)S =
Pore-forming powder/CPC by volume. .sup.b)C.S. = dry compressive
strength (hereinafter abbreviated as C.S.). .sup.c)Porosity:
Porosity (vol %) was measured by Archimedes' method, and calculated
as in ASTM C830.
[0089] It can be seen from Table 8 that various powders which are
soluble in water can be used in the preparation of a porous CPC
block according to the method of the present invention.
[0090] Dual-Functional Block
EXAMPLE 9
[0091] To a setting solution of 1 M phosphoric acid solution
(pH=5.89) the ND-CPC powder from PREPARATIVE EXAMPLE 3 was added in
a liquid/powder ratio (L/P ratio) of 0.4, i.e. 4 ml liquid/10 g
powder, while stirring. KCl powder in a ratio of KCl powder/CPC by
volume of 2 was mixed to the resulting mixture by stirring
intensively. The resulting paste was filled into a cylindrical
steel mold having a length of 12 mm and a diameter of 7 mm, and was
compressed with a gradually increased pressure until a maximum
pressure of 3.5 MPa was reached. The maximum pressure was
maintained for one minute, and then the compressed CPC block was
removed from the mold at the 15.sup.th minute following the mixing
of the liquid and powders.
[0092] The resulting cylinder having a diameter of 7 mm was placed
in another cylindrical steel mold having a diameter of 10 mm. To a
setting solution of 1 M phosphoric acid solution (pH=5.89) the
ND-CPC powder from PREPARATIVE EXAMPLE 3 was added in a
liquid/powder ratio (L/P ratio) of 0.4, i.e. 4 ml liquid/10 g
powder, while stirring. The resulting paste was filled into the gap
between said cylinder and said another mold, and was compressed
with a gradually increased pressure until a maximum pressure of 50
MPa was reached. The maximum pressure was maintained for one
minute. At the 15.sup.th minute following the mixing of the liquid
and ND-CPC powder, the CPC/KCl composite block was immersed in a
deionized water at 37.degree. C. for 4 days. KCl powder was
dissolved in the deionized water, and a dual-functional CPC block
having a porous CPC cylinder surround by a dense CPC annular block
was obtained.
[0093] The compressive strength of the specimen was measured by
using a AGS-500D mechanical tester (Shimadzu Co., Ltd., Kyoto,
Japan) after the specimens were dry. The measured dry specimen
compressive strength is 68.8 MPa.
[0094] The porosities of the porous CPC cylinder and the dense CPC
annular block were measured by Archimedes' method, and calculated
as in ASTM C830, after the dual-functional CPC block was broken
intentionally, and the results are 74% and 30%, respectively.
[0095] X-ray diffraction pattern of the powder obtained by grinding
the dual-functional CPC block shows broadened characteristic X-ray
diffraction peaks of apatite at 2.theta.=25-27.degree. and
2.theta.=20-35.degree. with a scanning range of 2.theta. of
20-40.degree. and a scanning rate of 1.degree./m results indicate
that the powder is a mixture of apatite and TTCP with apatite as a
major portion.
* * * * *