CA2027921C - Bone cement composition, cured product thereof, implant material and process for the preparation of the same - Google Patents
Bone cement composition, cured product thereof, implant material and process for the preparation of the sameInfo
- Publication number
- CA2027921C CA2027921C CA002027921A CA2027921A CA2027921C CA 2027921 C CA2027921 C CA 2027921C CA 002027921 A CA002027921 A CA 002027921A CA 2027921 A CA2027921 A CA 2027921A CA 2027921 C CA2027921 C CA 2027921C
- Authority
- CA
- Canada
- Prior art keywords
- methacrylate
- calcium phosphate
- bone
- component
- alkyl
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/0047—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
- A61L24/0073—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material with a macromolecular matrix
- A61L24/0084—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material with a macromolecular matrix containing fillers of phosphorus-containing inorganic compounds, e.g. apatite
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/34—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/02—Materials or treatment for tissue regeneration for reconstruction of bones; weight-bearing implants
Abstract
Disclosed is a bone cement composition comprising polyalkyl methacrylate derived from methacrylate having an alkyl group of 1 - 4 carbon atoms, hydroxyapatite, alkyl methacrylate having an alkyl group of 1 - 4 carbon atoms, 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator. Also disclosed are a cured product of the composition, an implant material using the composition and a process for the preparation of the implant material.
Description
2 ~
~L~
BONE CEME~T COMPOSIr~ION, CURED PRODUCT THEREOF, IMPLANrr MATERIAL AND PROCESS FOR THE PREPARATION OF THE SAME
FIELD OF THE INVENTION
The present invention relates to a bone cement compo-sition particularly suitable for adhesion to a natural bone and an artificial bone, and a reaction cured produc-t of the composition.
The invention also rela-tes to an implan-t material such as an artificial bone, an artificial too-th root ~fung) and a process for the preparation of the implant material.
BACKGROUND OF THE INV~.NTION
After a part of a bone is surgically removed because of disease such as malign tumor or osteomyelitis, a me-thod of transplanting ~grafting) an artificial bone formed from a metal instead of the removed bone has been gene~ally adopted. The transplantation (graft) of the artL:fic:Lal bone is made, for example, by providing a cavity in a natural bone for receiving the artificial bone af-ter removing a part of the natural bone, then filling the cavity with a bonding agent, putting the artificial bone into the bonding agent and curing -the bonding agent to close the gaps between the natural bone and the artificial bone and adhere them to each other. As the bonding agent, there has been conventionally employed a mixture of methyl methacrylate ~referred to hereinaEter as "MM~") an-~ a polymerization ini-tiator such as benzoyl peroxide (referred to hereinafter as "BPO") or a mixture of peroxide and a tertiary amine. For curing the bonding agent, the bonding agent is subjected to polymerization reaction at normal temperatures.
However, the cured product shows poor adhesivity to a natural bone, and moreover the curing reaction of ~MA is an exothermic reaction, so that the organization of the bone may be denatured owing to the generated hea-t during the curing reaction of MMA in the case tha-t the reaction is performed at a high speed.
In more detail, when the polymerization reaction of MMA is performed using such a conventional polymerization initiator as a mixture of BPO and amine, the reaction proceeds rapidly to release a reaction heat in a short pe-riod oE time, so as to temporarily make the temperature of MMA (or cured product of MMA) relativel.y high. I-lence, the organization of the natural bone ln contact wlth the cured product of MMA might be easily denatured.
Further, the cured produc-t of MMA has a low aff:Lnity with an organism (i.e., living body), and any substantial adhesive force is not produced be-tween not only the cured product and the artificial bone but also the cured product and the natural bone, so that looseness is brought about with time on each interface therebe-tween.
~L~
BONE CEME~T COMPOSIr~ION, CURED PRODUCT THEREOF, IMPLANrr MATERIAL AND PROCESS FOR THE PREPARATION OF THE SAME
FIELD OF THE INVENTION
The present invention relates to a bone cement compo-sition particularly suitable for adhesion to a natural bone and an artificial bone, and a reaction cured produc-t of the composition.
The invention also rela-tes to an implan-t material such as an artificial bone, an artificial too-th root ~fung) and a process for the preparation of the implant material.
BACKGROUND OF THE INV~.NTION
After a part of a bone is surgically removed because of disease such as malign tumor or osteomyelitis, a me-thod of transplanting ~grafting) an artificial bone formed from a metal instead of the removed bone has been gene~ally adopted. The transplantation (graft) of the artL:fic:Lal bone is made, for example, by providing a cavity in a natural bone for receiving the artificial bone af-ter removing a part of the natural bone, then filling the cavity with a bonding agent, putting the artificial bone into the bonding agent and curing -the bonding agent to close the gaps between the natural bone and the artificial bone and adhere them to each other. As the bonding agent, there has been conventionally employed a mixture of methyl methacrylate ~referred to hereinaEter as "MM~") an-~ a polymerization ini-tiator such as benzoyl peroxide (referred to hereinafter as "BPO") or a mixture of peroxide and a tertiary amine. For curing the bonding agent, the bonding agent is subjected to polymerization reaction at normal temperatures.
However, the cured product shows poor adhesivity to a natural bone, and moreover the curing reaction of ~MA is an exothermic reaction, so that the organization of the bone may be denatured owing to the generated hea-t during the curing reaction of MMA in the case tha-t the reaction is performed at a high speed.
In more detail, when the polymerization reaction of MMA is performed using such a conventional polymerization initiator as a mixture of BPO and amine, the reaction proceeds rapidly to release a reaction heat in a short pe-riod oE time, so as to temporarily make the temperature of MMA (or cured product of MMA) relativel.y high. I-lence, the organization of the natural bone ln contact wlth the cured product of MMA might be easily denatured.
Further, the cured produc-t of MMA has a low aff:Lnity with an organism (i.e., living body), and any substantial adhesive force is not produced be-tween not only the cured product and the artificial bone but also the cured product and the natural bone, so that looseness is brought about with time on each interface therebe-tween.
3 ~2~
For coping with the above-described drawbacks, there has been proposed a method of making the artiEicial bone itself have ~affinity with a natural bone and bonding the surface of -the artificial bone to the natural bone grown with time to unite them with each other. Tha-t is, the surface of the artificial bone is covered with calcium phosphate such as hydroxyapatite (referred to hereinaf-ter as "HAP") having high affinity with a natural bone to unite the artificial bone to a newborn bone grown with time through calcium phosphate, so as to firmly fix the artificial bone on the natural bone.
However, the method for fixing the artificial bone on the natural bone depending upon a natural healing power of a living body requires a long period of time for growth of a newborn bone, and therefore the affected part must be fixed for that long period of time. The fixing of the af-fected part for a long time brings about adverse side ef-fect such as reduction of muscular strength or kine-tic functions of joints, and in order to recover the reduced functions, rehabil.itation of a long period of time is necessary. Such rehabili.tation makes the burden too heavy for the pa-tient. Especially for aged persons, such burden is a severe problem because the grow-th of a newborn bone is slow and a very long time is required for curing the af-fected part.
Furthermore, since calcium phosphate itself does nothave any adhesive force to the artificial bone, it is very irnportant to allow to firmly adhere calcium phosphate to the artificial bone and to cover the artificial bone with calcium phosphate. In -the prior ~r~ the adhesion between the artificial bone and calcium phosphate is insufficien-t, and various problems still remain accompanied by the insufficient adhesion.
In more detail, for making the artificial bone or ar-tificial tooth root covered with calcium phosphate exhibit the desired functions, it is required that calcium phosphate is firmly adhered to a metal that is a main structural body of the artificial bone or the artificial tooth root. However, most of the artificial bones or artificial tooth roots covered with calcium phosphate are insufficien-t in this viewpoint. Further, in order to give calcium phosphate a sufficient affinity with organism, i-t is also required that calcium phosphate has its crystalline structure almost the same as that of the rigid oxganization of a living body ~i.e., natural bone), and that th~ metal is covered with calcium phosphate of high purity.
For satlsfying those requirernents, a complex process for preparing -the artiEicial bone or the artificial tooth root is needed, and besides, calcium phosphate is necessarily treated at a high temperature in the process for the preparation. However, even in the case of producing an artificial bone or an artificial tooth root in consideration of the above-mentioned viewpoints, there can s ~ J 2 :~.
be hardly obtained those having satis~ac-tory affinity with organism.
As described above, various problems s-till reside in both the conventional artificial bone and the conventional ar-tificial tooth root tdental root).
In dentistry for treating teeth having relatively sim~
ilar organization to that of bones, an adhesive comprising 4-(2-methacryloyloxyethyl)trimellitic anhydride (referred to hereinafter as "4-META") or hydrolyzate thereof (i.e., 4-(2-methacryloyloxyethyl)trimellitic acid, referred to hereinafter as "4-MET") r MMA and tri-n-butylborane (referred to hereinafter as "TBs") has been employed for adhering a metal crown to dentin.
The components of dentin are almost the same as those of a natural bone, so that the present inventors have tried to utilize the adhesion techniques of the dental art in the art of artificial bones. However, even if such techniques are utilized, an adhesive force of the adhesive tends to lower when the adhesive is immersed in water Eor a long pe-riod of time because the affinity of the adhesive with anatural bone i9 insufficient. Eor these reasons, it is difficult to firmly adhere an artificial bone to a natural bone without denaturing organization of the natural bone even by the use of the adhesion techniques of dentistry for burying the artificial bone.
OBJECT OF THE INVENTION
72932~85 The present invention is to solve the above-mentioned problems existing i.n the prior arts, and it is an objec-t o.~ the invention to provide a bone cement composition capable of favorably bonding an artificial bone ~ormed ~rom, ~or example, a metal to a natural bone, and a reaction cured product of the composi-tion.
It is another object o~ the invention to provide an implant material such as an artificial bone and an artificial tooth root having a high adhesivity to natural bones.
It is a further object of the invention to provide a process for the preparation of the above mentioned implant material.
SUMMARY OF THE INVENTION
There is provided by the present invention a bone cement composition comprising: a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by we:Lyht, a componenk (L) containing alkyl met:hacrylate having an alkyl group of 1-4 carbon atoms, and 4-(2-methacryloyloxye-thyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
There is also provided by the invention a reaction cured product of a composition comprising: a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99~9 to 90:10 parts by r~
72932-~
weight, a componen-t (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)-trimellitic acid or anhydride thereof, and a polymeri~akion initiator.
There is further provided by the invention an implant material, such as an artificial bone and an artificial tooth root, comprising a metal and a cured product o-E a bone cement:
composition covering at least a part of a surface of the metal, said composition comprising: a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between -the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof; and a polymerization initiator.
There is furthermore provided by the invention a pro.cess for the preparation of the above-mentioned implant material comprising the steps of covering at least a part of a surface oE a metal with a bone cement composition comprising: a component (:P) contai.ning polyalkyl methacrylate derived from methacryla-te having an al]cyl group of 1~4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxy-ethyl)trimellitic acid or anhydride thereof, and a polymerization initiator; and curing the covered composition.
~' 7a As an example of a suitable calcium phosphate there is mentioned HAP.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. l-a is a schematic sectional view illustrating one embodiment of the arti~icial bones according to the present invention.
~.~
Fig. 1-b is a schematic sectional view illus-trating another embodiment of the artificial bones according to the present invention.
Fig. 2 is a schematic view illustrating a hip joint formed by.burying the artificial bone of the present inven-tion into a femur.
Fig. 3-a is a schematic sectional view illustrating one embodiment of the artificial tooth root according to the present invention.
Fig. 3-b is a schematic sectional view illustrating another embodiment of the artificial tooth roo-t according to the present invention.
DETAIL~D DESCRIPTION OF T~IF. INVENTION
A bone cement composition and a reac-tion cured product of the composition according to the invention are described in detail hereinafter.
A polymer employable as a base for the bone cement composition of -the invention (also referrecl to hereinafter as "base poly~er") is polyalkyl rnethacrylate having an alkyl group of 1 - ~ carbon atorns.
As the base polymer, there is generally used polyalkyl methacrylate having a molecular weight of 103 to 10a, preferably 109 to 106, when measured based on GPC in terms of polystyrene. The polyalkyl methacrylate is preferably employed in the form of a powder.
. . . .
Examples of the base polymers include poly-~MA, polyethyl methacrylate, polypropyl me-thacrylate and poly-butyl methacrylate. These base polymers can be employed singly or in combination.
Of these base polymers, most preferred is poly-MMA be-cause possibility of harming human bodies is very low.
The bone cement composition of the invention contains calcium phosphate.
The calcium phosphate has a relatively similar component structure to that of a natural bone, so that the calcium phosphate is finally united with a newborn bone in accordance with growth of the bone to produce a high bond strength (high adhesion s-trength) between the bone cement composition and the bone.
The calcium phosphate used in the present invention include, for example, hydroxyapat.ite, fluoroapatite, tricalcium phospha-te, tetracalcium phospate and a mixture thereof.
The calcium phosphate used in the present :Lnven~ion may be heat treated or not heat treated. Further the calcium phosphate may be porous or not porous.
In the invention, the calcium phosphate of various forms can be employed. Especially when -the calcium phosphate having a mean particle diameter of 1 to 20 ~rn is used, an adhesion strength between a natural bone and a cured product of the bone cement composition and a compression strength can be prominently enhanced. The 7~g32-~5 ca].cium phosphate haviny a mean particle diamet:er o~ 2 to ~5 ym is more preferably employed, and thereby a bone cement compositlon capable of forming a cured product much more enhanced in the adhesion strength and the compression strength can be obtained.
The calci~m phosphate is preferably used in the form of a mixture with a polyalkyl methacrylate powder. In the mixture, the ratio between calcium phosphate and polyalkyl methacrylate is generally within the range of 0.1:99.g to 90:10, preferably 10:90 to 80:20, ~calcium phosphate : polyalkyl methacrylate, by weight~.
In the bone cement composition of the invention, an alkyl methacrylate having an alkyl group of 1-4 carbon atoms is employed as a polymerizable monomer component. Examples of the alkyl methacrylates include alkyl monomethacryla-tes such as MMA, ethyl methacrylate, propyl methacrylate and butyl methacrylate;
and lower alkylene dimethacrylates such as ethylene dimethacrylate and propylene dimethacrylate. They can be employed singly or in combination. Of these, preferably employed as the monomer component is MMA because possibility o~ harming human bodies is very low.
The bone cement composition also contains as a monomer component 4-META or 4-MET having the following formula:
.~
2 ~
CH3 - C = CH2 11 CCOCH2CH2C~ ~IlC~ C
CH3 - C = CH2 11 CCOCH2CH2a:0 ~C
O
The above-described alkyl me-thacrylate and 4-META (or 4-MET~ are usually used in liquid state, so that it is pre-ferred to beforehand dissolve 4-META tor 4-MET) in the liquid methacrylates separately from the aforementioned polyalkyl methacrylate and calcium phosphate to prepare a mixture liquid (i.e., liquid component (L)). In this case, -the liquid component (L) is prepa.red by mixing alkyl methacrylate and 4-META (or ~-MET) in a ral.::Lo o:E generally 99.9 : 0.1 to a5 : 15, preferably 99.5 : 0.5 to 90 : 10 (alkyl methacrylate : ~-META, by weight). By using those liquid components in the above-mentioned ratio, the adhesion strength of the resulting composition and the strength of a cured product of the composition can be prominently enhanced.
The ratio of -the aforementioned solid (powdery) compo-nent (P) to the liquid component (L), that is, component ~2 ~ t~l (P) / component (L), is generally within the range of 0.01 to 10, preferably 0.1 to 5.
Examples of the polymerization initiators employable in the invention includè a rèdox type polymerization ini-tiator, which is a combination oE benzoyl peroxide (BPO)and amine and conventionally used for preparing acrylic polymers at approx. normal temperatures, and alkyl borone.
Particularly preferred are tri-n-butylborane (TBB) and/or partially oxidized TBB. In the case of using TBB and/or partially oxidized TBB, the compound reacts with oxygen and water existing in air to generate a radical, and owing to the radical, the polymerization reaction of alkyl methacrylate and 4-META (or 4-MET) in the composition is performed to cure the bone cement composition of the inven-tion.
The polymerization initia-tor is used in such an amount -that the polymerization reaction is brough-t about. In gen-eral, the polymerization initiator is used in an amount of 0.1 to 1 part by weight per 1 par-t by weight oE the total of 4-META (or 4-MET) and alkyl methacrylate. Especially in the case of using TBB as the polymerization initiator, the amount of TBB is preferably in the range of 0.3 to 0.4 part by weight. The amount of TBB in this case is larger than that of a polymerization initiator used for an adhesive composition in dentistry. ~hen TBB is used in the above-mentioned amount and used in combination with 4-META (or 4-MET) and calcium phosphate, the resulting bone cemen-t ~3 composition can show curing proper-ties, adhesion strength and compression streng-th suitable for ~irmly bonding an artificial bone and a natural bone.
~he bone cement composition can be produced by before-hand preparing each components separately and mixing -them immediately before the use of the composition, but the com-position is advantageously produced by beforehand preparing the solid component, -the liquid component and the polymer-ization initiator as described above and mixing them imme-diately before the use of the composition. In the lattercase, the solid component can be obtained by mixing polyalkyl methacrylate (base polymer) and calcium phosphate. The solid component may contain various additives such as X-ray con-trast medium (e.g., barium sulfate), antibiotics and other fillers. Those various additives are preferably sterilized prior to -the use -thereof. In the case of using a peroxide type polymerization initiator such as benzoyl peroxide as a polymerization initiator, the polymerization -tnitiator can be added to the solid component.
The liquid component can be obtained by mixing alkyl methacrylate and 4-META (or 4 MET) with each other. The liquid component may contain a polymerization inhibitor such as hydroquinone to inhibit the polyrnerization reaction of the above-described monomer component during the stor-age. Further, the liquid component may also contain other additives such as antibiotics and X-ray con-trast medium.
2 ,~
~oreover, the liquid component can contain N,N-di.methyl-p-toluidine Eor the acceleration of curing the resulting bone cement composition within a living body.
The polymerization initiator is stored and transferre~
separately from the above-men-tioned liquid component.
Otherwise, the polymerization initiator is added to the sclid component as described above. Especially in the case oE using a polymerization initiator which forms a radical upon reaction with oxygen or water in air, such as TBB, the polymerization initiator is generally enclosed with an ap-propriate sealed container such as an ampule in the storage or transferrence thereof. For example, the solid compo-nent, the liquid component and the polymerization initiator which are separately prepared (or separately packaged) from each other are mixed with each o-ther immediately before the use thereof to prepare a bone cemen-t composition of the in-vention, whereby a c~1ring reaction is initiated. That is, those components are mixed with each other immedia-tely be-fore the used thereof to prepare an employable borle cement composi-tion.
The artificial bone and the artificial tooth root ac-cordlng to the invention are described in detail below.
Fig. 1-a is a schematic sectional view showing an em-bodiment of the artificial bone of the invention.
The artificial bone 1 of the invention comprises a metal 2 and a layer 3 of a cured product (i.e., cured prod-uc-t layer) of a polyalkyl methacrylate composition which covers at least a part of a surface of the metal 2. The polyalkyl methacrylate composi-tion used herein comprises polyalkyl methacrylate derived from methacrylate having an alkyl group of 1 - 4 carbon atoms, calcium phosphate, alkyl methacrylate having an alkyl group of 1 - 4 carbon atoms, 4-META or ~-MET, and a polymerization ini-tiator.
AS the metal 2 for the ar-tificial bone of the inven-tion, there can be employed a metal which hardly gives an adverse effect to organism even when used for a long period of time and is not varied in i-ts nature for a long period of ti.me. An example of such metal is stainless steel.
The artificial bone of the invention can take various forms depending upon the por-tion of a living body where the artificial bone is applied. Fig. 1-a shows an artificial bone employable for a hip joint, and the artificial bone can be also employed for other artificial joints such as a knee joint and an ankle joint. Otherwise, the ar-tificial bone can be effectively used for portions of a livinc3 body which are connec-ted to other bone organization, such as a tooth root.
On a surface of the metal 2 of the artificial bone 1 according to -the invention is provided a cured product layer 3 containing calcium phosphate.
The cured product layer 3 is generally provided whole surface of the metal 2 facing a natural bone, but the layer 3 may be provided on a part of the metal surface facing the natural bone.
The layer 3 is formed -from a cured product of a methacrylate resin containing calcium phosphate, and the cured product is concretely a cured product of a resin composition containing a base polymer, calcium phosphate, a monomer component and a polymeriza-tion initiator as described above.
The artificial bone of the invention can be prepared by coating the composition containing the above-described calcium phosphate and other components on a surface of a metal 2, or molding the composition in a mold made of ., ~
, Teflon and then curing the composition.
The thickness of the coated layer of the composition can be varied depending on the purpose of the resulting ar-tificial bone. In general, the composition is coated (or covered) in such an amount that the thickness of the cured product layer 3 of the composition would be no-t smaller than 0.1 ~m, preferably in the range of 1 to 500 ~lm.
The coated composition can be cured at normal ternpera-tures or cured under heating.
The shape of the coated layer can be easily varied correspondingly to a shape or a size of a cavity provided in a natural bone for recelving the resulting artificial bone.
The artificial bone prepared as above can be bonded (adhered) to a natural bone using an adhesive (bone cemen-t) having an equivalent composition to that of the bone cement composition used for the cured product layer 3. Otherwise, 17 ~g~
the artificial bone can be transplan-ted in -the same manner as conventionally employed -to be uni-ted with a natural bone with time.
The calclum phosphate contained in the cured product layer 3 has a very similar componen-t structure to that of a natural bone, so that a newborn bone is ~inally united with the calcium phosphate so as to give a prominently high adhesion :Eorce between the artificial bone and the natural bone, whereby any looseness does not occur on the adhered portion even when the artificial bone is used for a long period of time.
The artificial bone of the invention comprises a metal and a cured product of a specific composition covering a surface of the metal as described above. ~lowever, other embodiment shown in Fig. 1-b is also included in -the arti-ficial bone of the invention.
As shown in Flg. 1-b, the artificial bone 21 of the invention comprises a metal 22, a cured product layer 23 of a bone cement composi.t;.on of the invention and a calcium phosphate layer 2~ provided thereon wh:lch faces a natural bone. ~s the metal 22, the same metal as described above (i.e., metal employable for the embodiment described above) can be employed.
The calcium phospate layer 24 can be formed by any conventional methods such as a method of compression molding of calcium phosphate. In detail, the calcium phospha-te is subjected to compression molding in such a 3 ~
manner that a cavity for receiving the metal 22 is formed.
The calcium phospha-te is then subjected to sintering.
The metal 22 and the calc.ium phospha-te layer 24 are combined with each other using a polyalkyl methacrylate composition containing calcium phosphate. The polyalkyl methacrylate composition used herein comprises polyalkyl methacrylate derived from methacrylate having an alkyl group of 1 - 4 carbon atoms, calcium phosphate, alkyl methacrylate having an alkyl group of 1 - 4 carbon atoms, 4-META or 4-MET, and a polymerization initiator. Through the cured product layer 23 of the composition, the metal 22 and the calcium phosphate layer 24 are adhered to each other.
The thickness of the cured product layer 23 is gener-ally not smaller than 1 ~m, preferably in the range of 1 to500 ~m. The thickness of the calcium phosphate layer is generally in the range of 0.1 to 10 mm, p:referabl~l 0.1 to 5 mm An example of the use of the artiE:i.cLal bone according to the invent.ton is d~scri.bed below.
Fig. 2 is a schematic view illustrating an example of an artificial hip joint using the artificial bone of the invention.
A femur 11 is provided a cavity 13 for receiving an artificial join-t 12, then the cavity 13 is charged with a bone cement composition 14. Subsequently, the artificial joint is inserted into the cavity 13 having been charged 19 ~3~
with the bone cement composition. In accordance wlth the curing of the bone cement composition, the artificial joint 12 is adhered to the femur 11 owing -to the chemical adhesive force of the bone cement composition. The -time required for completion o-E -the adhesion be-tween the artificial joint and -the femur is varied depending on the nature of the used bone cement composition. Generally, the time therefor is within the range of approx. 0.5 to 3 hours, and this time is a little longer than the case of using a conventional bone cement composi-tion. Accordingly, a heat-generating temperature of the bone cement composition in the curing stage is low, so -that the organization of the femur contacting the bone cement composition is hardly damaged. For this reason, a growth of a newborn bone can be expected. Further, since calcium phosphate contained in the bone cement composition of the invention has a very similar component structure to that of the newborn bone, the calci.um phosphate and the ~atural bone are finally united. In the case of using the bone cement composition o~ the invention, the eemur and the artificial joint can be bonded to each other not only by a chemical adhesive force of the bone cement composition but also by a joining force given by the unification of newborn bone and calcium phosphate, so that looseness between the artificial bone and the femur hardly occ~rs even in the case of using the arti.ficial bone for a long period of time.
The present invention is described above exemplifying an artificial bone, but -the invention is also applicable to an artificial tooth root.
Fig. 3-a is a schematic sectional view showing an embodiment of the artificial tooth root of the invention.
The artificial tooth root 31 of the invention comprises a metal 32 and a cured product layer 33 of a polyalkyl methacrylate composition (i.e., a bone cement composition of the invention) covers at least a part of a surface of the metal 32.
Fig. 3-b is a shematic sectional view showing another embodiment of the artificial tooth roo-t of the invention.
As shown in Fig. 3-b, the artificial tooth root ~1 of the invention cornprises a metal 42, a cured product layer 43 of a bone cement composition of the inven-tion and a calcium phosphate layer 44 provided thereon which faces a natural bone of jaw. As each of -the metals 32, 42, the same metal as descrlbed above (i.e., metal employable for the embodiment described above) can be employed. Further, each of the cured product layers 33, ~3 and the calcium phosphate layer 4~ can also be formed by the same way as described above.
~he artificial -tooth using the ar-tificial -tooth root of the invention can be implanted as follows.
After baring a bone of jaw out of gingiva on which no tooth exists, -the bone of jaw is provided a cavity for receiving an artificial tooth root, -then the cavity is 21 2 ~ ~ ~ d3~ ~ ~
charged with a bone cement composition. Subsequently, the artificial tooth root is .inserted into the cavi-ty having been charged with the bone cement compositlon to be fixed to the cavity by curing the bone cement composition.
As shown in Fig. 3-a and Fig. 3-b, the me-tal of -the tooth root has a groove opened axially at about the central part on its top.
A protuberance formed at the bottom of an abutment is screwed in the groove, or bonded to -the groove with an adhesive. Then the abutment is covered with an crown to form an artificial tooth.
The bone cement composition of the invention can be employed for adhering an artificial joint as described above, and in addition, it can be also employed as a sub-s-titution bone by charging it in a broken portion of a nat-ural bone.
~FF~CT OE T!1~: INVEMTION
The bone cement composition of the invention contains calcium phosphate such as ~I~P, and the calc:Lum phosphate has a very similar component structure to that of a natural bone, so tha-t the calcium phosphate is united to a newborn bone. Further, the composition contains a specific polyalkyl methacryla-te as a host component and -thereby shows excellen-t adhesion properties to a metal, so that any looseness is not brought about between an artificial bone (e.g., artificial join-t) and a natural bone even ~hen the artifieial bone is used for a long period of -time.
By adhering an artificial bone to a natural bone using the bone cement composition of the invention, ~he growth of a newborn bone is not inhibi-ted, whereby the artificial bone, a natural bone and the cured product of -the bone cement eomposition ean be firmly adhered and united to each o-ther for a short period of time. Accordingly, the affected part is not required to be fi.xed for a long period of time, differently from eonventional cases, so that the decline of functions occuring in the vicinity of the affeeted part is remarkably decreased by using the bone cement composition of the invention.
Moreover, the monomer components such as alkyl methaeryla-te and ~-META in the bone cement composi-tion of the invention are dissolved out in only a small amount, and henee an adverse effeet is hardly c~iven to a human body.
After the bone cemen-t composltion of the :inven~lon :Ls coated over a surface of a natural bone and then the eompo-si~.ion is cured, it has been conf.Lrmed by a scanningelectron microscope -that the bone and the cured product of the bone cement eomposition are firmly adhered to each other.
The implant material such as the artificial bone or the artificial tooth root aecording to the invention has on its surface a layer of a cured product of a specifie methacrylate resin containing calcium phosphate such as 23 ~ 7~
llAP. This calcium phosphate has a very similar component structure to that of a natural bone, so that a newborn bone adsorbs the calcium phosphate to be united in accordance with the grow-th of the bone. Further, the speci-fic polyalkyl methacrylate shows excellent adhesion properties to metals, and therefore looseness is hardly given be-tween an artificial bone ~e.g., artificial joint) and a natural bone even if the artificial bone is used for a long period of time. Furthermore, any complex process is not needed for preparing the implant material of the inven-tion, for example, they can be easily prepared at normal tempera-tures.
The present invention are further described by the following examples, but those examples are given by no means to restrict the invention.
F~.XAMPI,F',S 1 - 9 & COMPARIsoN F,XA~/IPT,F' 1 93 g of polyme-thylmethacrylate (Acrybase, ME-3F, 7L~q 6/em~h/~
tradcrl~.,.c of Fujikura Ka~ei Co., Ltd.) and 7 g of barlurn sulfate were mixed w:ith each other to prepare a powdery polyalkyl methacrylate component.
To 0.8 g of the powdery polyalkyl methacrylate compo-nent was added 0.2 g of porous HAP (Ca/P = 1.7) having a mean particle diameter of 5 ~m (each particle having spherical form), to prepare a solid component (P) containin~ HAP in an amount of 20 ~ by weight.
2~ 7'~
Independently, 19.0 g of MMA and 1.0 g of 4-MET~ were mixed wikh each other to prepare a liquid component ~L).
To 0.~ g of the liquid component (L) was added 3 drops (approx. 0.15 to 0.20 g) of TBB, and they were well mixed.
To the resulting mixture was further added 1 g of the above-obtained solid component (P), and they were rnixed to prepare a bone cement composition of the invention.
Using the bone cement composition prepared as above, two test specimens of cured product of the composition were prepared. One specimen was in the rectangular form having a size of 4.0 mm x 4.0 mm x 3.0 mm, and the other specimen was in the columnar form having a diameter of 6 mm and a length of 8 mm. Of the two, the former was ~L se measured on the compression strength, and latter was measured on the compression strength after immersed in water for 2 months, using an autograph (DSS500, produced by Shimazu Seisakusho Co., Ltd.). The value of the compression strengt~ is a value at which each speclmen is broken.
The same procedures as described above were repeated except for varying the content o~ IIAP in the solicl compo-nent (P) to 40 % by weight (Example 2), 60 ~ by weight ~Example 3) and 80 % by weight (Example 4) to prepare vari-ous bone cement compositions. Using each of the composi-tions, test specimens of cured product of the composition were prepared in the same rnanner as described above. Then, the obtained specimens were measured on the compression streng-th in the same rnanner as described above.
Further, the same procedures as descrlbed above were repeated except for not usin~ H~P to prepare a composition not containing HAP for comparison. Using the composi-tion, test specimens of cured product of the composition were prepared in the same manner as described above, and the ob-tained specimens were measured on the compression s-trength in the same manner as described above.
The results are set forth in Table 1.
EXAMP~ES 5 - 7 The procedures for preparing a bone cement composition in Example 1 were repeated except for using HAP having a mean particle diameter of 15 ~m in the amount of 20 % by weight (Example 5), ~0 % by weight (Example 6) and 60 % by weight (Example 7) instead of HAP having a mean par-ticle diame-ter of 5 ~m, to prepare various bone cemen-t composi-tions. Using each of the obtained bone cement composi tions, test specimens of cured product of the composition were prepared in the same rnanner as described in Example 1.
Then, the obtained specimens were measured on the compres-sion strength in the same manner as descri.bed above.
The results are also set forth in Table 1.
26~ 2 ~
Table 1 HAP in So]id ComponentCo~pression St~enath Particle diameter Amount(kgf/cm2) (~m) (wt ~)Dried After immersing state in water Example 1 5 20 593 5q3 10 Example 2 5 gO 540 604 Example 3 5 60 636 608 Example 4 5 80 969 702 Example 5 15 20 873 524 Example 6 15 40 749 624 15 Example 7 15 60 - 646 Com. Ex. 1 - 0 529 513 As is evident from the results set forth in Table 1, the compresslon strength was increased by addition of HAP, and the strength of the cured product had a tendency of be-ing enhanced in accordance with the increase of -the amount of HAP. This fact indicates tha-t HAP serves to enhance the compression strength of the cured product. Further, when the amount of HAP is increased, the affinity be-tween a cured product of the bone cement composition and a bone, and therefore in the case of adding HAP in an amount wi-thin the range of -the presen-t invention, the adhesive strength between the bone cement composition and the bone can be kept for a long period of time.
FXAMPI.ES 8 - 10 On a section of a human femur was at-tached a masking tape to expose 0.22 cm2 of the femur outside.
Then, on an acrylic rod was placed the bone cement composition p~epared in each of Examples 1 to 3. The acrylic rod was fixed perpendicularly to the exposed portion of the femur through the composition under pressure, and they were allowed to stand for 30 minutes.
Subseque~tly, the femur bonded to the acrylic rod was immersed in water for 1 day, and thereafter the adhesion strength between the femur and -the acrylic rod was mea~sured using an au-tograph at a crosshead speed of 2 mm/minute.
Further, the adhesion stren~th between the acrylic rod and a stainless steel ~SUS-304) which was one material of artificial bones was measured in the same marlner as de scribed above.
The results are set forth in Table 2.
EXAMPLES 11 - 13 & COMPARISON FXAMPTF 2 On a section of a human femur was attached a masking tape to expose 0.22 cm2 of the femur outside.
Then, on an acrylic rod was placed the bone cement composition prepared in each of Examples 5 to 7, and the 2 ~ r~ ~ 2 'L
acrylic rod wlth the composition was bonded to the exposed portion of the Eernur through -the composition by means of pressure weldl.ng, and they were allowed to stand for 30 minu-tes.
Subsequently, the femur bonded to -the acrylic rod was immersed in water for 1 day, and thereafter the adhesion strength between the femur and the acrylic rod was measured using an autograph.
Further, the adhesion strength between the acrylic rod and a s-tainless steel (SUS-304) which was one material of artificial bones was measured in the same manner as de-scribed above.
Furthermore, the adhesion strength between the femur and the acrylic rod and between the stainless steel and the acrylic rod in the case of using a composition no-t contain-ing HAP was also measured for comparison in the same manner as described above.
The results are also set forth in Table 2.
2g 6~ d ~ ~,? ~
Table 2 HAP in Solid Co~ponent A~hesion Strength (MPa) Particle diameter Amount Human Stainless steel (~m) (wt.%)femur (SUS-304) Example 8 5 20 4.1 7.1 Example 9 5 40 11.1 12.0 Example 10 5 60 9.6 10.3 10 Example 11 15 20 5.5 7.3 Example 12 15 40 10.3 12.2 Example 13 15 60 9.9 11.6 Com. Ex. 2 - 0 8.5 7.8 FXAMPT.F,S 19 & 15 & COMPARISON EXA~PT,F, 3 The procedures of Example 2 were repeated except for varying the 4-META concentration in the liquid component to 3 % by weight (Example 1~), 10 % by weight (Example 15) and 0 % by weight (Comparison Example 3) to prepare various compositions. In the case of using each of -the obtai.ned compositions, the adhesion strength be-tween the human femur and the stainless steel (S~S-304) was measured in the same manner as described above.
The results are set forth in Table 3.
Table 3 4-MF.TA Concentration A~hesion Stren~th ~Pa) Amoun-t Human Stainless s-teel (wt.%) femur(SUS-304) Example 14 3 10.8 Example 9 5 11.1 12.0 Example 1510 7.6 10 Com. Ex. 3 0 S.7 0 As is evident from the results set forth in Table 3, 4-META was very effective for adhesion to the human ~emur and the stainless steel, and showed a high effectiveness when the 4-META concentration was within the range of 3 to 5 % by weight.
EXA~PT,FS 16 ~- 18 & CO~PARI~oN EXAMPT,E 9 Each of the bone cement composltions prepared in Examples 1 to 3 was cured into a columnar form (d:Lameter: 6 mm, length: 8 mm).
The columnar cured product was immersed in methanol for 1 week, and then the amount of the monomers (MMA and 4-META) dissolved in -the methanol was measured by the use of a liquid chromatograph (WATERS Micro Bordapa ~ 8, MeOH :
H2O = 7 : 3, 1 ml/minute).
Further, the amount of the monomers dissolved in the me-thanol in the case of using a composition not contalning HAP was also measured for cornparison in the same manner as described above.
The results are set ~orth in Table 4.
Each of the bone cement compositions prepared in Examples 5 to 7 was cured into a columnar form (diameter: 6 mm, length: 8 mm).
The columnar cured product was immersed in methanol for 1 week, and then the amount of the monomers (MMA and 4-META) dissolved in -the methanol was measured in the same manner as described in Example 16.
Further, the amount of the monomers in the case of us-i.ng a composition not containlng H~P was also measured for comparison in the same manner as described above.
The resu].ts are also set Eorth .in rrable 9.
3~
Table 4 ~.
M~P .in Solid Com~onent ~m~unt o-f Monorner Particle diameter Amount (wt.%) (~m) (wt.%) MM~4-META
Example 16 5 20 0.321.09 Example 17 5 40 0.210.70 Example 18 5 60 0.170.54 10 Example 19 15 20 0.320.82 Example 20 15 40 0.320.69 Example 21 15 60 0.240.42 Com. Ex. 4 - 0 0.480.84 F.XAMP~.~.S 22 ~ 24 The procedures of Example 1 were repeated except that each of the Eollowi.ng porous calc~um phosphates was used instead of HAP to obtain a bone cernent composit:i.on o~ the invention:
a) trica.lclum phosphate (Ca/P = 1.50) heat-treated at 950 ~C for 4 hrs (Example 22);
b) the mixture of HAP and tricalci.um phosphate (Ca/P =
1.60) heat-treated at 950 ~C for 4 hrs (Example 23); and c) the mixture of HAP and calcium oxide (Ca/P = 1.67) heat-trea-ted at 950 ~C for 'i hrs (Example 24).
All o~ the obtained compositions show as yood ef~ects as the composition of Example 1.
For coping with the above-described drawbacks, there has been proposed a method of making the artiEicial bone itself have ~affinity with a natural bone and bonding the surface of -the artificial bone to the natural bone grown with time to unite them with each other. Tha-t is, the surface of the artificial bone is covered with calcium phosphate such as hydroxyapatite (referred to hereinaf-ter as "HAP") having high affinity with a natural bone to unite the artificial bone to a newborn bone grown with time through calcium phosphate, so as to firmly fix the artificial bone on the natural bone.
However, the method for fixing the artificial bone on the natural bone depending upon a natural healing power of a living body requires a long period of time for growth of a newborn bone, and therefore the affected part must be fixed for that long period of time. The fixing of the af-fected part for a long time brings about adverse side ef-fect such as reduction of muscular strength or kine-tic functions of joints, and in order to recover the reduced functions, rehabil.itation of a long period of time is necessary. Such rehabili.tation makes the burden too heavy for the pa-tient. Especially for aged persons, such burden is a severe problem because the grow-th of a newborn bone is slow and a very long time is required for curing the af-fected part.
Furthermore, since calcium phosphate itself does nothave any adhesive force to the artificial bone, it is very irnportant to allow to firmly adhere calcium phosphate to the artificial bone and to cover the artificial bone with calcium phosphate. In -the prior ~r~ the adhesion between the artificial bone and calcium phosphate is insufficien-t, and various problems still remain accompanied by the insufficient adhesion.
In more detail, for making the artificial bone or ar-tificial tooth root covered with calcium phosphate exhibit the desired functions, it is required that calcium phosphate is firmly adhered to a metal that is a main structural body of the artificial bone or the artificial tooth root. However, most of the artificial bones or artificial tooth roots covered with calcium phosphate are insufficien-t in this viewpoint. Further, in order to give calcium phosphate a sufficient affinity with organism, i-t is also required that calcium phosphate has its crystalline structure almost the same as that of the rigid oxganization of a living body ~i.e., natural bone), and that th~ metal is covered with calcium phosphate of high purity.
For satlsfying those requirernents, a complex process for preparing -the artiEicial bone or the artificial tooth root is needed, and besides, calcium phosphate is necessarily treated at a high temperature in the process for the preparation. However, even in the case of producing an artificial bone or an artificial tooth root in consideration of the above-mentioned viewpoints, there can s ~ J 2 :~.
be hardly obtained those having satis~ac-tory affinity with organism.
As described above, various problems s-till reside in both the conventional artificial bone and the conventional ar-tificial tooth root tdental root).
In dentistry for treating teeth having relatively sim~
ilar organization to that of bones, an adhesive comprising 4-(2-methacryloyloxyethyl)trimellitic anhydride (referred to hereinafter as "4-META") or hydrolyzate thereof (i.e., 4-(2-methacryloyloxyethyl)trimellitic acid, referred to hereinafter as "4-MET") r MMA and tri-n-butylborane (referred to hereinafter as "TBs") has been employed for adhering a metal crown to dentin.
The components of dentin are almost the same as those of a natural bone, so that the present inventors have tried to utilize the adhesion techniques of the dental art in the art of artificial bones. However, even if such techniques are utilized, an adhesive force of the adhesive tends to lower when the adhesive is immersed in water Eor a long pe-riod of time because the affinity of the adhesive with anatural bone i9 insufficient. Eor these reasons, it is difficult to firmly adhere an artificial bone to a natural bone without denaturing organization of the natural bone even by the use of the adhesion techniques of dentistry for burying the artificial bone.
OBJECT OF THE INVENTION
72932~85 The present invention is to solve the above-mentioned problems existing i.n the prior arts, and it is an objec-t o.~ the invention to provide a bone cement composition capable of favorably bonding an artificial bone ~ormed ~rom, ~or example, a metal to a natural bone, and a reaction cured product of the composi-tion.
It is another object o~ the invention to provide an implant material such as an artificial bone and an artificial tooth root having a high adhesivity to natural bones.
It is a further object of the invention to provide a process for the preparation of the above mentioned implant material.
SUMMARY OF THE INVENTION
There is provided by the present invention a bone cement composition comprising: a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by we:Lyht, a componenk (L) containing alkyl met:hacrylate having an alkyl group of 1-4 carbon atoms, and 4-(2-methacryloyloxye-thyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
There is also provided by the invention a reaction cured product of a composition comprising: a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99~9 to 90:10 parts by r~
72932-~
weight, a componen-t (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)-trimellitic acid or anhydride thereof, and a polymeri~akion initiator.
There is further provided by the invention an implant material, such as an artificial bone and an artificial tooth root, comprising a metal and a cured product o-E a bone cement:
composition covering at least a part of a surface of the metal, said composition comprising: a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between -the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof; and a polymerization initiator.
There is furthermore provided by the invention a pro.cess for the preparation of the above-mentioned implant material comprising the steps of covering at least a part of a surface oE a metal with a bone cement composition comprising: a component (:P) contai.ning polyalkyl methacrylate derived from methacryla-te having an al]cyl group of 1~4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxy-ethyl)trimellitic acid or anhydride thereof, and a polymerization initiator; and curing the covered composition.
~' 7a As an example of a suitable calcium phosphate there is mentioned HAP.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. l-a is a schematic sectional view illustrating one embodiment of the arti~icial bones according to the present invention.
~.~
Fig. 1-b is a schematic sectional view illus-trating another embodiment of the artificial bones according to the present invention.
Fig. 2 is a schematic view illustrating a hip joint formed by.burying the artificial bone of the present inven-tion into a femur.
Fig. 3-a is a schematic sectional view illustrating one embodiment of the artificial tooth root according to the present invention.
Fig. 3-b is a schematic sectional view illustrating another embodiment of the artificial tooth roo-t according to the present invention.
DETAIL~D DESCRIPTION OF T~IF. INVENTION
A bone cement composition and a reac-tion cured product of the composition according to the invention are described in detail hereinafter.
A polymer employable as a base for the bone cement composition of -the invention (also referrecl to hereinafter as "base poly~er") is polyalkyl rnethacrylate having an alkyl group of 1 - ~ carbon atorns.
As the base polymer, there is generally used polyalkyl methacrylate having a molecular weight of 103 to 10a, preferably 109 to 106, when measured based on GPC in terms of polystyrene. The polyalkyl methacrylate is preferably employed in the form of a powder.
. . . .
Examples of the base polymers include poly-~MA, polyethyl methacrylate, polypropyl me-thacrylate and poly-butyl methacrylate. These base polymers can be employed singly or in combination.
Of these base polymers, most preferred is poly-MMA be-cause possibility of harming human bodies is very low.
The bone cement composition of the invention contains calcium phosphate.
The calcium phosphate has a relatively similar component structure to that of a natural bone, so that the calcium phosphate is finally united with a newborn bone in accordance with growth of the bone to produce a high bond strength (high adhesion s-trength) between the bone cement composition and the bone.
The calcium phosphate used in the present invention include, for example, hydroxyapat.ite, fluoroapatite, tricalcium phospha-te, tetracalcium phospate and a mixture thereof.
The calcium phosphate used in the present :Lnven~ion may be heat treated or not heat treated. Further the calcium phosphate may be porous or not porous.
In the invention, the calcium phosphate of various forms can be employed. Especially when -the calcium phosphate having a mean particle diameter of 1 to 20 ~rn is used, an adhesion strength between a natural bone and a cured product of the bone cement composition and a compression strength can be prominently enhanced. The 7~g32-~5 ca].cium phosphate haviny a mean particle diamet:er o~ 2 to ~5 ym is more preferably employed, and thereby a bone cement compositlon capable of forming a cured product much more enhanced in the adhesion strength and the compression strength can be obtained.
The calci~m phosphate is preferably used in the form of a mixture with a polyalkyl methacrylate powder. In the mixture, the ratio between calcium phosphate and polyalkyl methacrylate is generally within the range of 0.1:99.g to 90:10, preferably 10:90 to 80:20, ~calcium phosphate : polyalkyl methacrylate, by weight~.
In the bone cement composition of the invention, an alkyl methacrylate having an alkyl group of 1-4 carbon atoms is employed as a polymerizable monomer component. Examples of the alkyl methacrylates include alkyl monomethacryla-tes such as MMA, ethyl methacrylate, propyl methacrylate and butyl methacrylate;
and lower alkylene dimethacrylates such as ethylene dimethacrylate and propylene dimethacrylate. They can be employed singly or in combination. Of these, preferably employed as the monomer component is MMA because possibility o~ harming human bodies is very low.
The bone cement composition also contains as a monomer component 4-META or 4-MET having the following formula:
.~
2 ~
CH3 - C = CH2 11 CCOCH2CH2C~ ~IlC~ C
CH3 - C = CH2 11 CCOCH2CH2a:0 ~C
O
The above-described alkyl me-thacrylate and 4-META (or 4-MET~ are usually used in liquid state, so that it is pre-ferred to beforehand dissolve 4-META tor 4-MET) in the liquid methacrylates separately from the aforementioned polyalkyl methacrylate and calcium phosphate to prepare a mixture liquid (i.e., liquid component (L)). In this case, -the liquid component (L) is prepa.red by mixing alkyl methacrylate and 4-META (or ~-MET) in a ral.::Lo o:E generally 99.9 : 0.1 to a5 : 15, preferably 99.5 : 0.5 to 90 : 10 (alkyl methacrylate : ~-META, by weight). By using those liquid components in the above-mentioned ratio, the adhesion strength of the resulting composition and the strength of a cured product of the composition can be prominently enhanced.
The ratio of -the aforementioned solid (powdery) compo-nent (P) to the liquid component (L), that is, component ~2 ~ t~l (P) / component (L), is generally within the range of 0.01 to 10, preferably 0.1 to 5.
Examples of the polymerization initiators employable in the invention includè a rèdox type polymerization ini-tiator, which is a combination oE benzoyl peroxide (BPO)and amine and conventionally used for preparing acrylic polymers at approx. normal temperatures, and alkyl borone.
Particularly preferred are tri-n-butylborane (TBB) and/or partially oxidized TBB. In the case of using TBB and/or partially oxidized TBB, the compound reacts with oxygen and water existing in air to generate a radical, and owing to the radical, the polymerization reaction of alkyl methacrylate and 4-META (or 4-MET) in the composition is performed to cure the bone cement composition of the inven-tion.
The polymerization initia-tor is used in such an amount -that the polymerization reaction is brough-t about. In gen-eral, the polymerization initiator is used in an amount of 0.1 to 1 part by weight per 1 par-t by weight oE the total of 4-META (or 4-MET) and alkyl methacrylate. Especially in the case of using TBB as the polymerization initiator, the amount of TBB is preferably in the range of 0.3 to 0.4 part by weight. The amount of TBB in this case is larger than that of a polymerization initiator used for an adhesive composition in dentistry. ~hen TBB is used in the above-mentioned amount and used in combination with 4-META (or 4-MET) and calcium phosphate, the resulting bone cemen-t ~3 composition can show curing proper-ties, adhesion strength and compression streng-th suitable for ~irmly bonding an artificial bone and a natural bone.
~he bone cement composition can be produced by before-hand preparing each components separately and mixing -them immediately before the use of the composition, but the com-position is advantageously produced by beforehand preparing the solid component, -the liquid component and the polymer-ization initiator as described above and mixing them imme-diately before the use of the composition. In the lattercase, the solid component can be obtained by mixing polyalkyl methacrylate (base polymer) and calcium phosphate. The solid component may contain various additives such as X-ray con-trast medium (e.g., barium sulfate), antibiotics and other fillers. Those various additives are preferably sterilized prior to -the use -thereof. In the case of using a peroxide type polymerization initiator such as benzoyl peroxide as a polymerization initiator, the polymerization -tnitiator can be added to the solid component.
The liquid component can be obtained by mixing alkyl methacrylate and 4-META (or 4 MET) with each other. The liquid component may contain a polymerization inhibitor such as hydroquinone to inhibit the polyrnerization reaction of the above-described monomer component during the stor-age. Further, the liquid component may also contain other additives such as antibiotics and X-ray con-trast medium.
2 ,~
~oreover, the liquid component can contain N,N-di.methyl-p-toluidine Eor the acceleration of curing the resulting bone cement composition within a living body.
The polymerization initiator is stored and transferre~
separately from the above-men-tioned liquid component.
Otherwise, the polymerization initiator is added to the sclid component as described above. Especially in the case oE using a polymerization initiator which forms a radical upon reaction with oxygen or water in air, such as TBB, the polymerization initiator is generally enclosed with an ap-propriate sealed container such as an ampule in the storage or transferrence thereof. For example, the solid compo-nent, the liquid component and the polymerization initiator which are separately prepared (or separately packaged) from each other are mixed with each o-ther immediately before the use thereof to prepare a bone cemen-t composition of the in-vention, whereby a c~1ring reaction is initiated. That is, those components are mixed with each other immedia-tely be-fore the used thereof to prepare an employable borle cement composi-tion.
The artificial bone and the artificial tooth root ac-cordlng to the invention are described in detail below.
Fig. 1-a is a schematic sectional view showing an em-bodiment of the artificial bone of the invention.
The artificial bone 1 of the invention comprises a metal 2 and a layer 3 of a cured product (i.e., cured prod-uc-t layer) of a polyalkyl methacrylate composition which covers at least a part of a surface of the metal 2. The polyalkyl methacrylate composi-tion used herein comprises polyalkyl methacrylate derived from methacrylate having an alkyl group of 1 - 4 carbon atoms, calcium phosphate, alkyl methacrylate having an alkyl group of 1 - 4 carbon atoms, 4-META or ~-MET, and a polymerization ini-tiator.
AS the metal 2 for the ar-tificial bone of the inven-tion, there can be employed a metal which hardly gives an adverse effect to organism even when used for a long period of time and is not varied in i-ts nature for a long period of ti.me. An example of such metal is stainless steel.
The artificial bone of the invention can take various forms depending upon the por-tion of a living body where the artificial bone is applied. Fig. 1-a shows an artificial bone employable for a hip joint, and the artificial bone can be also employed for other artificial joints such as a knee joint and an ankle joint. Otherwise, the ar-tificial bone can be effectively used for portions of a livinc3 body which are connec-ted to other bone organization, such as a tooth root.
On a surface of the metal 2 of the artificial bone 1 according to -the invention is provided a cured product layer 3 containing calcium phosphate.
The cured product layer 3 is generally provided whole surface of the metal 2 facing a natural bone, but the layer 3 may be provided on a part of the metal surface facing the natural bone.
The layer 3 is formed -from a cured product of a methacrylate resin containing calcium phosphate, and the cured product is concretely a cured product of a resin composition containing a base polymer, calcium phosphate, a monomer component and a polymeriza-tion initiator as described above.
The artificial bone of the invention can be prepared by coating the composition containing the above-described calcium phosphate and other components on a surface of a metal 2, or molding the composition in a mold made of ., ~
, Teflon and then curing the composition.
The thickness of the coated layer of the composition can be varied depending on the purpose of the resulting ar-tificial bone. In general, the composition is coated (or covered) in such an amount that the thickness of the cured product layer 3 of the composition would be no-t smaller than 0.1 ~m, preferably in the range of 1 to 500 ~lm.
The coated composition can be cured at normal ternpera-tures or cured under heating.
The shape of the coated layer can be easily varied correspondingly to a shape or a size of a cavity provided in a natural bone for recelving the resulting artificial bone.
The artificial bone prepared as above can be bonded (adhered) to a natural bone using an adhesive (bone cemen-t) having an equivalent composition to that of the bone cement composition used for the cured product layer 3. Otherwise, 17 ~g~
the artificial bone can be transplan-ted in -the same manner as conventionally employed -to be uni-ted with a natural bone with time.
The calclum phosphate contained in the cured product layer 3 has a very similar componen-t structure to that of a natural bone, so that a newborn bone is ~inally united with the calcium phosphate so as to give a prominently high adhesion :Eorce between the artificial bone and the natural bone, whereby any looseness does not occur on the adhered portion even when the artificial bone is used for a long period of time.
The artificial bone of the invention comprises a metal and a cured product of a specific composition covering a surface of the metal as described above. ~lowever, other embodiment shown in Fig. 1-b is also included in -the arti-ficial bone of the invention.
As shown in Flg. 1-b, the artificial bone 21 of the invention comprises a metal 22, a cured product layer 23 of a bone cement composi.t;.on of the invention and a calcium phosphate layer 2~ provided thereon wh:lch faces a natural bone. ~s the metal 22, the same metal as described above (i.e., metal employable for the embodiment described above) can be employed.
The calcium phospate layer 24 can be formed by any conventional methods such as a method of compression molding of calcium phosphate. In detail, the calcium phospha-te is subjected to compression molding in such a 3 ~
manner that a cavity for receiving the metal 22 is formed.
The calcium phospha-te is then subjected to sintering.
The metal 22 and the calc.ium phospha-te layer 24 are combined with each other using a polyalkyl methacrylate composition containing calcium phosphate. The polyalkyl methacrylate composition used herein comprises polyalkyl methacrylate derived from methacrylate having an alkyl group of 1 - 4 carbon atoms, calcium phosphate, alkyl methacrylate having an alkyl group of 1 - 4 carbon atoms, 4-META or 4-MET, and a polymerization initiator. Through the cured product layer 23 of the composition, the metal 22 and the calcium phosphate layer 24 are adhered to each other.
The thickness of the cured product layer 23 is gener-ally not smaller than 1 ~m, preferably in the range of 1 to500 ~m. The thickness of the calcium phosphate layer is generally in the range of 0.1 to 10 mm, p:referabl~l 0.1 to 5 mm An example of the use of the artiE:i.cLal bone according to the invent.ton is d~scri.bed below.
Fig. 2 is a schematic view illustrating an example of an artificial hip joint using the artificial bone of the invention.
A femur 11 is provided a cavity 13 for receiving an artificial join-t 12, then the cavity 13 is charged with a bone cement composition 14. Subsequently, the artificial joint is inserted into the cavity 13 having been charged 19 ~3~
with the bone cement composition. In accordance wlth the curing of the bone cement composition, the artificial joint 12 is adhered to the femur 11 owing -to the chemical adhesive force of the bone cement composition. The -time required for completion o-E -the adhesion be-tween the artificial joint and -the femur is varied depending on the nature of the used bone cement composition. Generally, the time therefor is within the range of approx. 0.5 to 3 hours, and this time is a little longer than the case of using a conventional bone cement composi-tion. Accordingly, a heat-generating temperature of the bone cement composition in the curing stage is low, so -that the organization of the femur contacting the bone cement composition is hardly damaged. For this reason, a growth of a newborn bone can be expected. Further, since calcium phosphate contained in the bone cement composition of the invention has a very similar component structure to that of the newborn bone, the calci.um phosphate and the ~atural bone are finally united. In the case of using the bone cement composition o~ the invention, the eemur and the artificial joint can be bonded to each other not only by a chemical adhesive force of the bone cement composition but also by a joining force given by the unification of newborn bone and calcium phosphate, so that looseness between the artificial bone and the femur hardly occ~rs even in the case of using the arti.ficial bone for a long period of time.
The present invention is described above exemplifying an artificial bone, but -the invention is also applicable to an artificial tooth root.
Fig. 3-a is a schematic sectional view showing an embodiment of the artificial tooth root of the invention.
The artificial tooth root 31 of the invention comprises a metal 32 and a cured product layer 33 of a polyalkyl methacrylate composition (i.e., a bone cement composition of the invention) covers at least a part of a surface of the metal 32.
Fig. 3-b is a shematic sectional view showing another embodiment of the artificial tooth roo-t of the invention.
As shown in Fig. 3-b, the artificial tooth root ~1 of the invention cornprises a metal 42, a cured product layer 43 of a bone cement composition of the inven-tion and a calcium phosphate layer 44 provided thereon which faces a natural bone of jaw. As each of -the metals 32, 42, the same metal as descrlbed above (i.e., metal employable for the embodiment described above) can be employed. Further, each of the cured product layers 33, ~3 and the calcium phosphate layer 4~ can also be formed by the same way as described above.
~he artificial -tooth using the ar-tificial -tooth root of the invention can be implanted as follows.
After baring a bone of jaw out of gingiva on which no tooth exists, -the bone of jaw is provided a cavity for receiving an artificial tooth root, -then the cavity is 21 2 ~ ~ ~ d3~ ~ ~
charged with a bone cement composition. Subsequently, the artificial tooth root is .inserted into the cavi-ty having been charged with the bone cement compositlon to be fixed to the cavity by curing the bone cement composition.
As shown in Fig. 3-a and Fig. 3-b, the me-tal of -the tooth root has a groove opened axially at about the central part on its top.
A protuberance formed at the bottom of an abutment is screwed in the groove, or bonded to -the groove with an adhesive. Then the abutment is covered with an crown to form an artificial tooth.
The bone cement composition of the invention can be employed for adhering an artificial joint as described above, and in addition, it can be also employed as a sub-s-titution bone by charging it in a broken portion of a nat-ural bone.
~FF~CT OE T!1~: INVEMTION
The bone cement composition of the invention contains calcium phosphate such as ~I~P, and the calc:Lum phosphate has a very similar component structure to that of a natural bone, so tha-t the calcium phosphate is united to a newborn bone. Further, the composition contains a specific polyalkyl methacryla-te as a host component and -thereby shows excellen-t adhesion properties to a metal, so that any looseness is not brought about between an artificial bone (e.g., artificial join-t) and a natural bone even ~hen the artifieial bone is used for a long period of -time.
By adhering an artificial bone to a natural bone using the bone cement composition of the invention, ~he growth of a newborn bone is not inhibi-ted, whereby the artificial bone, a natural bone and the cured product of -the bone cement eomposition ean be firmly adhered and united to each o-ther for a short period of time. Accordingly, the affected part is not required to be fi.xed for a long period of time, differently from eonventional cases, so that the decline of functions occuring in the vicinity of the affeeted part is remarkably decreased by using the bone cement composition of the invention.
Moreover, the monomer components such as alkyl methaeryla-te and ~-META in the bone cement composi-tion of the invention are dissolved out in only a small amount, and henee an adverse effeet is hardly c~iven to a human body.
After the bone cemen-t composltion of the :inven~lon :Ls coated over a surface of a natural bone and then the eompo-si~.ion is cured, it has been conf.Lrmed by a scanningelectron microscope -that the bone and the cured product of the bone cement eomposition are firmly adhered to each other.
The implant material such as the artificial bone or the artificial tooth root aecording to the invention has on its surface a layer of a cured product of a specifie methacrylate resin containing calcium phosphate such as 23 ~ 7~
llAP. This calcium phosphate has a very similar component structure to that of a natural bone, so that a newborn bone adsorbs the calcium phosphate to be united in accordance with the grow-th of the bone. Further, the speci-fic polyalkyl methacrylate shows excellent adhesion properties to metals, and therefore looseness is hardly given be-tween an artificial bone ~e.g., artificial joint) and a natural bone even if the artificial bone is used for a long period of time. Furthermore, any complex process is not needed for preparing the implant material of the inven-tion, for example, they can be easily prepared at normal tempera-tures.
The present invention are further described by the following examples, but those examples are given by no means to restrict the invention.
F~.XAMPI,F',S 1 - 9 & COMPARIsoN F,XA~/IPT,F' 1 93 g of polyme-thylmethacrylate (Acrybase, ME-3F, 7L~q 6/em~h/~
tradcrl~.,.c of Fujikura Ka~ei Co., Ltd.) and 7 g of barlurn sulfate were mixed w:ith each other to prepare a powdery polyalkyl methacrylate component.
To 0.8 g of the powdery polyalkyl methacrylate compo-nent was added 0.2 g of porous HAP (Ca/P = 1.7) having a mean particle diameter of 5 ~m (each particle having spherical form), to prepare a solid component (P) containin~ HAP in an amount of 20 ~ by weight.
2~ 7'~
Independently, 19.0 g of MMA and 1.0 g of 4-MET~ were mixed wikh each other to prepare a liquid component ~L).
To 0.~ g of the liquid component (L) was added 3 drops (approx. 0.15 to 0.20 g) of TBB, and they were well mixed.
To the resulting mixture was further added 1 g of the above-obtained solid component (P), and they were rnixed to prepare a bone cement composition of the invention.
Using the bone cement composition prepared as above, two test specimens of cured product of the composition were prepared. One specimen was in the rectangular form having a size of 4.0 mm x 4.0 mm x 3.0 mm, and the other specimen was in the columnar form having a diameter of 6 mm and a length of 8 mm. Of the two, the former was ~L se measured on the compression strength, and latter was measured on the compression strength after immersed in water for 2 months, using an autograph (DSS500, produced by Shimazu Seisakusho Co., Ltd.). The value of the compression strengt~ is a value at which each speclmen is broken.
The same procedures as described above were repeated except for varying the content o~ IIAP in the solicl compo-nent (P) to 40 % by weight (Example 2), 60 ~ by weight ~Example 3) and 80 % by weight (Example 4) to prepare vari-ous bone cement compositions. Using each of the composi-tions, test specimens of cured product of the composition were prepared in the same rnanner as described above. Then, the obtained specimens were measured on the compression streng-th in the same rnanner as described above.
Further, the same procedures as descrlbed above were repeated except for not usin~ H~P to prepare a composition not containing HAP for comparison. Using the composi-tion, test specimens of cured product of the composition were prepared in the same manner as described above, and the ob-tained specimens were measured on the compression s-trength in the same manner as described above.
The results are set forth in Table 1.
EXAMP~ES 5 - 7 The procedures for preparing a bone cement composition in Example 1 were repeated except for using HAP having a mean particle diameter of 15 ~m in the amount of 20 % by weight (Example 5), ~0 % by weight (Example 6) and 60 % by weight (Example 7) instead of HAP having a mean par-ticle diame-ter of 5 ~m, to prepare various bone cemen-t composi-tions. Using each of the obtained bone cement composi tions, test specimens of cured product of the composition were prepared in the same rnanner as described in Example 1.
Then, the obtained specimens were measured on the compres-sion strength in the same manner as descri.bed above.
The results are also set forth in Table 1.
26~ 2 ~
Table 1 HAP in So]id ComponentCo~pression St~enath Particle diameter Amount(kgf/cm2) (~m) (wt ~)Dried After immersing state in water Example 1 5 20 593 5q3 10 Example 2 5 gO 540 604 Example 3 5 60 636 608 Example 4 5 80 969 702 Example 5 15 20 873 524 Example 6 15 40 749 624 15 Example 7 15 60 - 646 Com. Ex. 1 - 0 529 513 As is evident from the results set forth in Table 1, the compresslon strength was increased by addition of HAP, and the strength of the cured product had a tendency of be-ing enhanced in accordance with the increase of -the amount of HAP. This fact indicates tha-t HAP serves to enhance the compression strength of the cured product. Further, when the amount of HAP is increased, the affinity be-tween a cured product of the bone cement composition and a bone, and therefore in the case of adding HAP in an amount wi-thin the range of -the presen-t invention, the adhesive strength between the bone cement composition and the bone can be kept for a long period of time.
FXAMPI.ES 8 - 10 On a section of a human femur was at-tached a masking tape to expose 0.22 cm2 of the femur outside.
Then, on an acrylic rod was placed the bone cement composition p~epared in each of Examples 1 to 3. The acrylic rod was fixed perpendicularly to the exposed portion of the femur through the composition under pressure, and they were allowed to stand for 30 minutes.
Subseque~tly, the femur bonded to the acrylic rod was immersed in water for 1 day, and thereafter the adhesion strength between the femur and -the acrylic rod was mea~sured using an au-tograph at a crosshead speed of 2 mm/minute.
Further, the adhesion stren~th between the acrylic rod and a stainless steel ~SUS-304) which was one material of artificial bones was measured in the same marlner as de scribed above.
The results are set forth in Table 2.
EXAMPLES 11 - 13 & COMPARISON FXAMPTF 2 On a section of a human femur was attached a masking tape to expose 0.22 cm2 of the femur outside.
Then, on an acrylic rod was placed the bone cement composition prepared in each of Examples 5 to 7, and the 2 ~ r~ ~ 2 'L
acrylic rod wlth the composition was bonded to the exposed portion of the Eernur through -the composition by means of pressure weldl.ng, and they were allowed to stand for 30 minu-tes.
Subsequently, the femur bonded to -the acrylic rod was immersed in water for 1 day, and thereafter the adhesion strength between the femur and the acrylic rod was measured using an autograph.
Further, the adhesion strength between the acrylic rod and a s-tainless steel (SUS-304) which was one material of artificial bones was measured in the same manner as de-scribed above.
Furthermore, the adhesion strength between the femur and the acrylic rod and between the stainless steel and the acrylic rod in the case of using a composition no-t contain-ing HAP was also measured for comparison in the same manner as described above.
The results are also set forth in Table 2.
2g 6~ d ~ ~,? ~
Table 2 HAP in Solid Co~ponent A~hesion Strength (MPa) Particle diameter Amount Human Stainless steel (~m) (wt.%)femur (SUS-304) Example 8 5 20 4.1 7.1 Example 9 5 40 11.1 12.0 Example 10 5 60 9.6 10.3 10 Example 11 15 20 5.5 7.3 Example 12 15 40 10.3 12.2 Example 13 15 60 9.9 11.6 Com. Ex. 2 - 0 8.5 7.8 FXAMPT.F,S 19 & 15 & COMPARISON EXA~PT,F, 3 The procedures of Example 2 were repeated except for varying the 4-META concentration in the liquid component to 3 % by weight (Example 1~), 10 % by weight (Example 15) and 0 % by weight (Comparison Example 3) to prepare various compositions. In the case of using each of -the obtai.ned compositions, the adhesion strength be-tween the human femur and the stainless steel (S~S-304) was measured in the same manner as described above.
The results are set forth in Table 3.
Table 3 4-MF.TA Concentration A~hesion Stren~th ~Pa) Amoun-t Human Stainless s-teel (wt.%) femur(SUS-304) Example 14 3 10.8 Example 9 5 11.1 12.0 Example 1510 7.6 10 Com. Ex. 3 0 S.7 0 As is evident from the results set forth in Table 3, 4-META was very effective for adhesion to the human ~emur and the stainless steel, and showed a high effectiveness when the 4-META concentration was within the range of 3 to 5 % by weight.
EXA~PT,FS 16 ~- 18 & CO~PARI~oN EXAMPT,E 9 Each of the bone cement composltions prepared in Examples 1 to 3 was cured into a columnar form (d:Lameter: 6 mm, length: 8 mm).
The columnar cured product was immersed in methanol for 1 week, and then the amount of the monomers (MMA and 4-META) dissolved in -the methanol was measured by the use of a liquid chromatograph (WATERS Micro Bordapa ~ 8, MeOH :
H2O = 7 : 3, 1 ml/minute).
Further, the amount of the monomers dissolved in the me-thanol in the case of using a composition not contalning HAP was also measured for cornparison in the same manner as described above.
The results are set ~orth in Table 4.
Each of the bone cement compositions prepared in Examples 5 to 7 was cured into a columnar form (diameter: 6 mm, length: 8 mm).
The columnar cured product was immersed in methanol for 1 week, and then the amount of the monomers (MMA and 4-META) dissolved in -the methanol was measured in the same manner as described in Example 16.
Further, the amount of the monomers in the case of us-i.ng a composition not containlng H~P was also measured for comparison in the same manner as described above.
The resu].ts are also set Eorth .in rrable 9.
3~
Table 4 ~.
M~P .in Solid Com~onent ~m~unt o-f Monorner Particle diameter Amount (wt.%) (~m) (wt.%) MM~4-META
Example 16 5 20 0.321.09 Example 17 5 40 0.210.70 Example 18 5 60 0.170.54 10 Example 19 15 20 0.320.82 Example 20 15 40 0.320.69 Example 21 15 60 0.240.42 Com. Ex. 4 - 0 0.480.84 F.XAMP~.~.S 22 ~ 24 The procedures of Example 1 were repeated except that each of the Eollowi.ng porous calc~um phosphates was used instead of HAP to obtain a bone cernent composit:i.on o~ the invention:
a) trica.lclum phosphate (Ca/P = 1.50) heat-treated at 950 ~C for 4 hrs (Example 22);
b) the mixture of HAP and tricalci.um phosphate (Ca/P =
1.60) heat-treated at 950 ~C for 4 hrs (Example 23); and c) the mixture of HAP and calcium oxide (Ca/P = 1.67) heat-trea-ted at 950 ~C for 'i hrs (Example 24).
All o~ the obtained compositions show as yood ef~ects as the composition of Example 1.
Claims (27)
1. A bone cement composition comprising:
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms, and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms, and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
2. The bone cement composition as claimed in claim 1, wherein said component (L) contains the alkyl methacrylate and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof in an amount such that the ratio between the alkyl methacrylate and the 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof is within the range of 99.9:0.1 to 85:15 parts by weight, the ratio of the component (P) to the component (L) is within the range of 0.01 to 10, and the amount of the polymerization initiator contained in the composition is within the range of 0.1 to 1 part by weight per 1 part by weight of the component (L).
3. The bone cement composition as claimed in claim 1, wherein the polyalkyl methacrylate is a homopolymer or a copolymer of methacrylate selected from the group consisting of methyl methacrylate, ethyl methacrylate, propyl methacrylate and butyl methacrylate, and the alkyl methacrylate is methyl methacrylate.
4. The bone cement composition as claimed in claim l or 2, wherein the calcium phosphate is hydroxyapatite.
5. The bone cement composition as claimed in claim 1, wherein the calcium phosphate is in the form of particles having a mean particle diameter within the range of l to 20 µm.
6. The bone cement composition as claimed in claim 1, wherein the polymerization initiator is tri-n-butylborane and/or a partially oxidized product thereof.
7. A reaction cured product of a composition comprising:
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
8. The reaction cured product as claimed in claim 7, wherein said component (L) contains the alkyl methacrylate and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof in an amount such that the ratio between the alkyl methacrylate and the 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof is within the range of 99.9:0.1 to 85:15 parts by weight, the ratio of the component (P) to the component (L) is within the range of 0.01 to 10, and the amount of the polymerization initiator contained in the composition is within the range of 0.1 to l part by weight per l part by weight of the component (L).
9. The reaction cured product as claimed in claim 7 or 8, wherein the polyalkyl methacrylate is a homopolymer of methyl methacrylate or ethyl methacrylate or a copolymer of methyl methacrylate and ethyl methacrylate and the alkyl methacrylate is methyl methacrylate.
10. The reaction cured product as claimed in claim 7 or 8, wherein the calcium phosphate is hydroxyapatite.
11. The reaction cured product as claimed in claim 7 or 8, wherein the calcium phosphate has a mean particle diameter within the range of 1 to 20 µm.
12. The reaction cured product as claimed in claim 7 or 8, wherein the polymerization initiator is tri-n-butylborane and/or a partially oxidized product thereof.
13. An implant material comprising a metal and a cured product of a bone cement composition covering at least a part of a surface of the metal, said composition comprising:
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
14. The implant material as claimed in claim 13, wherein said component (L) contains the alkyl methacrylate and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof in an amount such that the ratio between the alkyl methacrylate and the 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof is within the range of 99.9:0.1 to 85:15 parts by weight, the ratio of the component (P) to the component (L) is within the range of 0.01 to 10, and the amount of the polymerization initiator contained in the composition is within the range of 0.1 to 1 part by weight per l part by weight of the component (L).
15. The implant material as claimed in claim 13 or 14, wherein the polyalkyl methacrylate is a homopolymer or a copolymer of methacrylate selected from the group consisting of methyl methacrylate, ethyl methacrylate, propyl methacrylate and butyl methacrylate, and the alkyl methacrylate is methyl methacrylate.
16. The implant material as claimed in claim 13 or 14, wherein the calcium phosphate is hydroxyapatite.
17. The implant material as claimed in claim 13 or 14, wherein the calcium phosphate is a sintered calcium phosphate.
18. The implant material as claimed in claim 13 or 14, wherein the calcium phosphate is in the form of a particle having a mean particle diameter within the range of 1 to 20 µm.
19. The implant material as claimed in claim 13 or 14, wherein the polymerization initiator is tri-n-butylborane.
20. The implant material as claimed in claim 13 or 14, wherein the implant material is an artificial bone or an artificial tooth root.
21. An implant material comprising a metal and a calcium phosphate layer provided thereon which faces a natural bone, said metal and said calcium phosphate layer being adhered to each other with a cured product of a bone cement composition comprising:
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator.
22. A process for the preparation of an implant material comprising the steps of covering at least a part of a surface of a metal with a bone cement composition comprising:
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator; and curing the covered composition.
a component (P) containing polyalkyl methacrylate derived from methacrylate having an alkyl group of 1-4 carbon atoms and calcium phosphate in an amount such that the ratio between the calcium phosphate and the polyalkyl methacrylate is within the range of 0.1:99.9 to 90:10 parts by weight, a component (L) containing alkyl methacrylate having an alkyl group of 1-4 carbon atoms and 4-(2-methacryloyloxyethyl)trimellitic acid or anhydride thereof, and a polymerization initiator; and curing the covered composition.
23. A bone cement composition for bonding an artificial bone made of a metal to a natural bone, which comprises:
i) a powdery polyalkyl methacrylate derived from an alkyl methacrylate having 1 to 4 carbon atoms in the alkyl moiety, the polyalkyl methacrylate having a molecular weight of 104 to 10 6;
ii) calcium phosphate selected from the group consisting of hydroxyapatite, fluoroapatite, tricalcium phosphate, tetracalcium phosphate and a mixture thereof, the calcium phosphate having a mean particle size of 1 to 20 µm;
iii) a first polymerizable monomer selected from the group consisting of an alkyl monomethacrylate having 1 to 4 carbon atoms in the alkyl moiety and a lower alkylene dimethacrylate;
iv) a second polymerizable monomer selected from the group consisting of 4-(2-methacryloyloxyethyl)trimellitic acid and its anhydride; and v) a polymerization initiator selected from the group consisting of [a] a redox combination of a peroxide and an amine and [b] a trialkyl borane or a partially oxidized product thereof, wherein the polyalkyl methacrylate and the calcium phosphate are solid and are contained at a calcium phosphate:
polyalkyl methacrylate weight ratio of from 10:90 to 90:20;
the first and second polymerizable monomers are liquid and are contained at a first polymerizable monomer : second polymerizable monomer weight ratio of from 99.5:0.5 to 85:15;
the solid components and the liquid components are contained at a solid/liquid weight ratio of 0.1 to 5; and the polymerization initiator (v) is kept separate from the first (iii) and second (iv) polymerizable monomers until immediately before the use of the composition.
i) a powdery polyalkyl methacrylate derived from an alkyl methacrylate having 1 to 4 carbon atoms in the alkyl moiety, the polyalkyl methacrylate having a molecular weight of 104 to 10 6;
ii) calcium phosphate selected from the group consisting of hydroxyapatite, fluoroapatite, tricalcium phosphate, tetracalcium phosphate and a mixture thereof, the calcium phosphate having a mean particle size of 1 to 20 µm;
iii) a first polymerizable monomer selected from the group consisting of an alkyl monomethacrylate having 1 to 4 carbon atoms in the alkyl moiety and a lower alkylene dimethacrylate;
iv) a second polymerizable monomer selected from the group consisting of 4-(2-methacryloyloxyethyl)trimellitic acid and its anhydride; and v) a polymerization initiator selected from the group consisting of [a] a redox combination of a peroxide and an amine and [b] a trialkyl borane or a partially oxidized product thereof, wherein the polyalkyl methacrylate and the calcium phosphate are solid and are contained at a calcium phosphate:
polyalkyl methacrylate weight ratio of from 10:90 to 90:20;
the first and second polymerizable monomers are liquid and are contained at a first polymerizable monomer : second polymerizable monomer weight ratio of from 99.5:0.5 to 85:15;
the solid components and the liquid components are contained at a solid/liquid weight ratio of 0.1 to 5; and the polymerization initiator (v) is kept separate from the first (iii) and second (iv) polymerizable monomers until immediately before the use of the composition.
24. The composition according to claim 23, wherein:
the polyalkyl methacrylate (i) is polymethyl methacrylate;
the calcium phosphate (ii) is hydroxyapatite having a mean particle diameter of 2 to 15 µm;
the first polymerizable monomer (iii) is methyl methacrylate;
the second polymerizable monomer (iv) is 4-(2-methacryloyloxyethyl)trimellitic anhydride; and the polymerization initiator (v) comprises tri-n-butylborane or partially oxidized product thereof.
the polyalkyl methacrylate (i) is polymethyl methacrylate;
the calcium phosphate (ii) is hydroxyapatite having a mean particle diameter of 2 to 15 µm;
the first polymerizable monomer (iii) is methyl methacrylate;
the second polymerizable monomer (iv) is 4-(2-methacryloyloxyethyl)trimellitic anhydride; and the polymerization initiator (v) comprises tri-n-butylborane or partially oxidized product thereof.
25. An implant material comprising a metal body and a cured product of a bone cement composition covering at least a part of a surface of the metal body, wherein the bone cement composition is defined in claim 23 or 24.
26. The implant material according to claim 25, which is an artificial bone or an artificial tooth root.
27. The implant material according to claim 26, wherein the bone cement material also includes an X-ray contrast medium.
Applications Claiming Priority (4)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP27264589 | 1989-10-19 | ||
| JP272644/1989 | 1989-10-19 | ||
| JP272645/1989 | 1989-10-19 | ||
| JP27264489 | 1989-10-19 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2027921A1 CA2027921A1 (en) | 1991-04-20 |
| CA2027921C true CA2027921C (en) | 1997-12-09 |
Family
ID=26550304
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002027921A Expired - Fee Related CA2027921C (en) | 1989-10-19 | 1990-10-18 | Bone cement composition, cured product thereof, implant material and process for the preparation of the same |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US5264215A (en) |
| EP (1) | EP0425200B1 (en) |
| AT (1) | ATE110283T1 (en) |
| CA (1) | CA2027921C (en) |
| DE (1) | DE69011807T2 (en) |
Families Citing this family (48)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5962028A (en) | 1988-04-20 | 1999-10-05 | Norian Corporation | Carbonated hydroxyapatite compositions and uses |
| JPH05220218A (en) * | 1992-02-13 | 1993-08-31 | Norio Nakabayashi | Anti-thrombogenic regeneration cellulose film and manufacture thereof |
| US5459177A (en) * | 1993-03-09 | 1995-10-17 | Sun Medical Co., Ltd. | Adhesive for soft tissue and kit thereof |
| US6075067A (en) * | 1994-08-15 | 2000-06-13 | Corpipharm Gmbh & Co | Cement for medical use, method for producing the cement, and use of the cement |
| US5965635A (en) * | 1995-06-07 | 1999-10-12 | Illinois Tool Works Inc. | Alkylacrylate ester composition for anchoring materials in or to concrete or masonry |
| US5643994A (en) * | 1994-09-21 | 1997-07-01 | Illinois Tool Works Inc. | Anchoring systems and methods utilizing acrylate compositions |
| US5550172A (en) * | 1995-02-07 | 1996-08-27 | Ethicon, Inc. | Utilization of biocompatible adhesive/sealant materials for securing surgical devices |
| US6287341B1 (en) | 1995-05-19 | 2001-09-11 | Etex Corporation | Orthopedic and dental ceramic implants |
| US6953594B2 (en) | 1996-10-10 | 2005-10-11 | Etex Corporation | Method of preparing a poorly crystalline calcium phosphate and methods of its use |
| US7517539B1 (en) | 1996-10-16 | 2009-04-14 | Etex Corporation | Method of preparing a poorly crystalline calcium phosphate and methods of its use |
| IT1297509B1 (en) * | 1997-12-23 | 1999-12-17 | Aloja Ernesto D | USE OF BONE CEMENTS FOR FIXING AND STABILIZATION OF NATURAL TEETH AND / OR DENTAL IMPLANTS |
| US6020396A (en) * | 1998-03-13 | 2000-02-01 | The Penn State Research Foundation | Bone cement compositions |
| US6383519B1 (en) * | 1999-01-26 | 2002-05-07 | Vita Special Purpose Corporation | Inorganic shaped bodies and methods for their production and use |
| US6799966B1 (en) | 1999-03-04 | 2004-10-05 | 3M Innovative Properties Company | Fluoropolymeric orthodontic article |
| US6458162B1 (en) * | 1999-08-13 | 2002-10-01 | Vita Special Purpose Corporation | Composite shaped bodies and methods for their production and use |
| US7008433B2 (en) | 2001-02-15 | 2006-03-07 | Depuy Acromed, Inc. | Vertebroplasty injection device |
| AU2002361860A1 (en) * | 2001-12-21 | 2003-07-15 | Richard J. Lagow | Calcium phosphate bone replacement materials and methods of use thereof |
| US20040127563A1 (en) * | 2002-03-22 | 2004-07-01 | Deslauriers Richard J. | Methods of performing medical procedures which promote bone growth, compositions which promote bone growth, and methods of making such compositions |
| JP2004236729A (en) * | 2003-02-04 | 2004-08-26 | Kobayashi Pharmaceut Co Ltd | Bone cement composition |
| EP2918296A1 (en) | 2003-02-28 | 2015-09-16 | Biointeractions Ltd. | Polymeric network system for medical devices and methods of use |
| US20060264967A1 (en) | 2003-03-14 | 2006-11-23 | Ferreyro Roque H | Hydraulic device for the injection of bone cement in percutaneous vertebroplasty |
| US8066713B2 (en) | 2003-03-31 | 2011-11-29 | Depuy Spine, Inc. | Remotely-activated vertebroplasty injection device |
| US8415407B2 (en) | 2004-03-21 | 2013-04-09 | Depuy Spine, Inc. | Methods, materials, and apparatus for treating bone and other tissue |
| WO2006011152A2 (en) | 2004-06-17 | 2006-02-02 | Disc-O-Tech Medical Technologies, Ltd. | Methods for treating bone and other tissue |
| US8579908B2 (en) | 2003-09-26 | 2013-11-12 | DePuy Synthes Products, LLC. | Device for delivering viscous material |
| US7189263B2 (en) * | 2004-02-03 | 2007-03-13 | Vita Special Purpose Corporation | Biocompatible bone graft material |
| US9220595B2 (en) | 2004-06-23 | 2015-12-29 | Orthovita, Inc. | Shapeable bone graft substitute and instruments for delivery thereof |
| DE102005023094A1 (en) * | 2005-05-13 | 2006-11-16 | Nies, Berthold, Dr. | Bioactive bone cement e.g. for implantation into bones, made by adding small amounts of polymerizable monomers containing anionic groups which cause cement surface to mineralize after being incubated in simulated body fluid |
| US9381024B2 (en) | 2005-07-31 | 2016-07-05 | DePuy Synthes Products, Inc. | Marked tools |
| US9918767B2 (en) | 2005-08-01 | 2018-03-20 | DePuy Synthes Products, Inc. | Temperature control system |
| US8360629B2 (en) | 2005-11-22 | 2013-01-29 | Depuy Spine, Inc. | Mixing apparatus having central and planetary mixing elements |
| EP2422822A1 (en) | 2006-06-29 | 2012-02-29 | Orthovita, Inc. | Bioactive bone graft substitute |
| US9642932B2 (en) | 2006-09-14 | 2017-05-09 | DePuy Synthes Products, Inc. | Bone cement and methods of use thereof |
| US8602780B2 (en) * | 2006-10-16 | 2013-12-10 | Natural Dental Implants, Ag | Customized dental prosthesis for periodontal or osseointegration and related systems and methods |
| US9539062B2 (en) | 2006-10-16 | 2017-01-10 | Natural Dental Implants, Ag | Methods of designing and manufacturing customized dental prosthesis for periodontal or osseointegration and related systems |
| US10426578B2 (en) * | 2006-10-16 | 2019-10-01 | Natural Dental Implants, Ag | Customized dental prosthesis for periodontal or osseointegration and related systems |
| US8454362B2 (en) * | 2006-10-16 | 2013-06-04 | Natural Dental Implants Ag | Customized dental prosthesis for periodontal- or osseointegration, and related systems and methods |
| US9801697B2 (en) * | 2011-03-18 | 2017-10-31 | Natural Dental Implants Ag | Integrated support device for providing temporary primary stability to dental implants and prosthesis, and related methods |
| WO2008047371A2 (en) | 2006-10-19 | 2008-04-24 | Depuy Spine, Inc. | Fluid delivery system |
| CN102131529A (en) * | 2008-06-30 | 2011-07-20 | 国立大学法人东京大学 | Bone defect filler not adsorbing bone growth factor and not inhibiting the activity of the same |
| DE102010003547A1 (en) | 2009-04-02 | 2010-10-14 | Innotere Gmbh | Bioactive bone cement and process for its preparation |
| EP2502637B1 (en) | 2009-11-20 | 2018-04-04 | Mitsui Chemicals, Inc. | Adhesive composition for soft tissue, adhesive composition for covering wounds, or wound covering agent composition |
| NO2502638T3 (en) * | 2009-11-20 | 2018-07-21 | ||
| DE102012014702A1 (en) * | 2012-07-25 | 2014-01-30 | Heraeus Medical Gmbh | Pasty bone cement |
| CN107648663A (en) | 2016-07-25 | 2018-02-02 | 薪创生命科技有限公司 | New bone material substitutes synthesizing formula, preparation method and application method |
| EP4021521A1 (en) | 2019-08-26 | 2022-07-06 | Setbone Medical Ltd. | Implant comprising a plurality of hardening states |
| CN112316200A (en) * | 2020-07-20 | 2021-02-05 | 北京奥凯伟迪生物科技有限公司 | Dual-curing adhesive for bone bonding and preparation method thereof |
| CN114404658B (en) * | 2022-02-18 | 2023-01-31 | 中国科学技术大学先进技术研究院 | Bone cement, preparation method thereof and orthopedic implant material |
Family Cites Families (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE2905878A1 (en) * | 1979-02-16 | 1980-08-28 | Merck Patent Gmbh | IMPLANTATION MATERIALS AND METHOD FOR THEIR PRODUCTION |
| DK154260C (en) * | 1981-02-20 | 1989-05-22 | Mundipharma Gmbh | PROCEDURE FOR THE MANUFACTURING OF A BONE IMPLANT OF FURNISHED TRICAL CUMPHOSPHATE, SPECIFICALLY FOR FILLING OF SPACES OR FOR COMPOSITION OF BONE PARTS AFTER FRACTURE. |
| US4514527A (en) * | 1983-01-10 | 1985-04-30 | American Dental Association Health Foundation | Method for obtaining strong adhesive bonding of composites to dentin enamel and other substrates |
| US4636526A (en) * | 1985-02-19 | 1987-01-13 | The Dow Chemical Company | Composites of unsintered calcium phosphates and synthetic biodegradable polymers useful as hard tissue prosthetics |
| JPS63268780A (en) * | 1987-04-28 | 1988-11-07 | G C Dental Ind Corp | Dentin bonding compound |
| US4782826A (en) * | 1987-05-21 | 1988-11-08 | Mentor Corporation | Penile prosthesis |
-
1990
- 1990-10-18 CA CA002027921A patent/CA2027921C/en not_active Expired - Fee Related
- 1990-10-19 US US07/599,827 patent/US5264215A/en not_active Expired - Lifetime
- 1990-10-19 EP EP90311483A patent/EP0425200B1/en not_active Expired - Lifetime
- 1990-10-19 AT AT90311483T patent/ATE110283T1/en not_active IP Right Cessation
- 1990-10-19 DE DE69011807T patent/DE69011807T2/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| EP0425200B1 (en) | 1994-08-24 |
| DE69011807T2 (en) | 1995-02-16 |
| US5264215A (en) | 1993-11-23 |
| EP0425200A1 (en) | 1991-05-02 |
| DE69011807D1 (en) | 1994-09-29 |
| CA2027921A1 (en) | 1991-04-20 |
| ATE110283T1 (en) | 1994-09-15 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2027921C (en) | Bone cement composition, cured product thereof, implant material and process for the preparation of the same | |
| US4202055A (en) | Anchorage for highly stressed endoprostheses | |
| US4259117A (en) | Dental filling material | |
| US3829973A (en) | Dental and surgical bonding-filling material | |
| US4728570A (en) | Calcium-hydroxide-treated polymeric implant matrial | |
| JPS6241662A (en) | Biologically active composite material for artificial prosthetic purpose | |
| Morita et al. | Performance of adhesive bone cement containing hydroxyapatite particles | |
| CA2126452A1 (en) | Adhesive composition and method | |
| EP0089782A1 (en) | Polymeric acrylic prosthesis | |
| US3882600A (en) | Composition in method for treating teeth | |
| EP0758544B1 (en) | Dental or surgical adhesive and polymerization initiator composition for the same | |
| JP2001505196A (en) | Bioabsorbable polymerization products from radiation-curable binder systems | |
| AU6100498A (en) | Bone substitute material with a surface coating of peptides having an rgd amino acid sequence | |
| EP0835646A2 (en) | Adhesive composition for dental or surgical treatment | |
| KR101177997B1 (en) | Preparation method of microsphere carrier of calcium phosphate cement with collagen | |
| NZ199182A (en) | Porous prostheses from sintered polymetric particles | |
| JP2751938B2 (en) | Bone cement composition and hardened body | |
| JPS63183069A (en) | Implant material and its production | |
| US5718924A (en) | Fluoride releasing biomaterials | |
| JP2751939B2 (en) | Implant material and method for producing the same | |
| Okazaki et al. | Mechanical and biological properties of apatite composite resins | |
| JP2000245821A (en) | Bloactive cement composition | |
| JP2004201869A (en) | Bioactive bone cement | |
| JP3471866B2 (en) | Manufacturing method of artificial root | |
| JP3871298B2 (en) | Medical implant material |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKLA | Lapsed |