Patent Application
20080058442
As compared to the survey article on medical and scientific products by L. H. Hench “Engineered Materials Handbook” Vol 4, ASM International 1991, pp1007-1013, (especially Figures 1 and 2, p. 1008), the present invention deals with bioactive materials of an additional type, the type of which could be defined as type 5, i.e. with even faster dissolution and precipitation of phases than in the traditional bioactive glasses and/or resorbable materials. This is accomplished by the use of soluble glasses and the inorganic cement.
One route according to the present invention that yields surprisingly good initial results and improved final properties is to make a hybrid material of a glass ionomer cement and minerals of calcium aluminate and/or calcium silicate, maintaining a bioactive feature of the system. Glass ionomer cements consist of glass and poly acrylic acid. The acid dissolves the glass, and the ions from the glass cross-link the acid, and the material hardens. The reaction is rather rapid and nearly final strength is reached after about one hour. By exchanging fractions of the glass for calcium aluminate or silicate and a corresponding fraction of the PAA for water (with accelerator) a hybrid material can be formed. The liquid contents are controlled via
with a 0.2<wc/c<0.45 (refers to the inorganic cement system), 0<PAA/(reactive glass)<0.21 and 0.2<wGIC/(reactive glass)<0.45 (refers to the glass ionomer system). All ratios refer ratios by weight.
In the formula c=inorganic cement;
wc=water to react with inorganic cement;
wGIC=water to react with reactive glass, and
w (i.e. total water)=wc+wGIC.
The PAA can be applied as a solution and/ or as solid acid component.
Since the initial pH is acidic, the PAA reaction occurs first and as the acid is cross-linked the pH increases and the hydration of the Ca-aluminates continues. The material has a much higher initial strength than that of the pure ceramic system. The final strength is higher than that of the GIC. The microstructural variables are controlled by the reactive glass, the poly acrylic acid including the pH, the Ca-aluminate or Ca-silicate and inert fillers, e.g. dental glass particles or glass fibers.
The initial solution should have a pH<7, preferably 1-4, enhancing the cross-linking of the polycarboxylic. The pH increases when the polycarboxylic system meets the CA-system, resulting in a basic overall system at pH>7. The amounts of the polyacrylic acids are controlled to maintain pH<7 up to 30 minutes. After final hydration the pH approaches neutrality from the basic side. One problem with pure Glass Ionomer systems, which are based on polycarboxylic is the corrosion resistance sensitivity. The basic CAH system neutralises the initial acidity in the polyacrylic systems. The present invention could be looked upon as a two-phase biomaterial composed of two different biomaterials where the first is activated to take care of necessary early-age phenomena and the second biomaterial to establish the property profile of the end-product, included being a bioactive material.
The control of pH, especially the effect of obtaining a pH>7 early in the process—after initial acidic condition—is essential in transforming the initial acid system into a bioactive system, i.e. conditions for apatite formation, the requirements of which is high pH and a chemical surrounding of ions including calcium, phosphate and hydroxyl ions—the phosphate ions originating from phosphate glass, body liquid or from P-containing bonding materials, the hydroxyl ions from the dissolution of the Ca-aluminate system or added bases, preferably Li-hydroxide and/or Ca-hydroxide. The high pH contributes to formation of aluminate ions (Al(OH)4-) instead of aluminium ions (Al3+).
Reactive filler particles in the present invention are composed of reactive glass, a phosphorous-containing glass and chemically bonded ceramics, preferably Ca-aluminates, preferably CA=(CaO)(Al2O3), C12A7=(CaO)12(Al2O3)7) and C3A=(CaO)3(Al2O3) and/or CS=(CaO SiO2), C2S=(2CaO SiO2), and C3S=(3CaO SiO2), the latter preferably for orthopaedic applications. The composition of the reactive glass, especially the dissolution rate, is crucial. The glass grain size is also important and should be below 40 micron. The pure PAA gives an earlier general cross-linking reaction. Addition of a salt of the PAA is important in achieving improved viscosity at a low w/c. The inert filler is essential for the general end-product microstructure. Its effect concerns a lowered expansion, increased radio-opacity and favoured mechanical properties, especially hardness and fracture toughness.
Concerning calcium aluminate phases it is preferable to use CA, C12A7 and C3A, which yield good initial strength. The addition of accelerator is dependant upon the selection of the Ca-aluminate phase. Low concentrations of lithium ions increase the reaction rate for CA. For C12A7 and C3A the effect of accelerator is more complex.
According to another aspect of the invention addition of a base is included to achieve a change of pH to a high pH>7, more preferably pH>10 after an initial “acidic” time period of approximately 5 minutes. This is to assure an optimised hydration speed.
According to another aspect of the invention addition of a further acid is included to keep the pH<7 during a prolonged time of up to 30 minutes. This is to assure an optimised time for complete cross-linking of the acid.
Ways to induce such additional (delayed and then rapid) pH changes include release of acids/bases from a porous material (preferably nano/meso-pore structure or zeolite type structures). An additional way is coating of the particle surfaces to control the release/dissolution of pH changing species, especially the CBCs material, e.g. Ca-aluminate phases by coating with for instance Na-glyconate.
The active acids can be introduced either as dried substance together with the inorganic cement or as liquid in the hydration liquid or as a combination of both dry an active acid raw material and a liquid solution of the active acid.
Suitably, said polycarboxylic has a molecular weight of 100-250,000, preferably 1000-100,000 and it is present in an amount of up to 30%, preferably 1-20% and most preferred 3-15% by weight, calculated on the powdered material including any dry additives for dental applications.
It is preferred that the system comprises inert dental glass, as an additive in the powdered material, preferably at a content of 3-30 weight-% more preferred 5-20%. The particle size is critical in establishing high homogeneity. It is preferred that the particle size is 0.1-5 μm, more preferable 0.2-2 μm, and most preferable 0.3-0.7 μm. The dental glass may contain low additional amounts of less stable glass or reactive glass, preferable below 10% of the glass content. These glasses can preferably contain fluorine and phosphorus to yield fluoride ions, which contribute to F-apatite formation. According to the present invention the translucency is achieved earlier than in a pure an inorganic cement based system due to early pore closure.
Said polyacrylic acid or salt thereof is an acid in the group that consists of PAA, Me(I)-PAA, PAMA and Me(I)-PAMA, wherein
Me(I)=alkali metal ion, e.g. Na, K or Li
In one embodiment of the invention, at least a part or most preferred all of the reactive groups in the polycarboxylic based material bond to the CBC system.
The system may comprise one or more expansion compensating additives adapted to give the ceramic material dimensionally stable long-term attributes, as is described in WO 00/21489. Other additives and aspects of the system may follow that which is described in SE 463,493, SE 502,987, WO 00/21489, WO 01/76534, WO 01/76535, PCT/SE02/01480 and PCT/SE02/01481, the contents of which are incorporated herein by reference. For example, it is preferred at least for dental filling materials that the system comprises additives and/or is based on raw materials that contribute to translucency of the hydrated material.
According to one aspect of the invention the inert filler particles are composed of pre-hydrated chemically bonded ceramics of the same composition as the main binding phase. This improves the homogeneity of the microstructure and enhances the binding between reacting chemically bonded ceramics and the filler material.
According to another aspect of the present invention an additional system can be included to improve the closure of pores initially, namely by introducing a system that works independently of the pH, e.g. the semihydrate of CaSO4, gypsum. And a further system to solidify the total system initially, the combination of phosphoric acid and zinc oxide-forming Zn-phosphate. These phases will not contribute to the long-term properties but will enhance the initial pore closure and initial strength.
By using granules the w/c ratio (water/cement ratio) can be lower than for the loose powder. The flow-ability of the material is higher when it is granulated. The granules should preferably be of a size below 1 mm, more preferably below 0.5 mm and most preferably below 0.4 mm. The compaction density of the granule, the granule density should be above 35%, preferably above 50% most preferably above 60%.
By using such highly compacted small granules, the shaping of the material can take place in a subsequent step, without any remaining workability limitations of highly compacted bodies. A facilitated shaping in such a subsequent step, such as kneading, extrusion, tablet throwing, ultrasound etc., can be made while retaining a mobility in the system that has a high final degree of compaction, exceeding 35%, preferably exceeding 50%, even more preferred exceeding 60%.
The principle is based on the fact that a small granule—after granulation of a pre-pressed, highly compacted body—contains several tenths of millions of contact points between particles in the same, which particles are in the micrometer magnitude. When these small granules are pressed together to form new bodies, new contact points arise, which new contact points are not of the same high degree of compaction. The lower degree of compaction in these new contact points results in an improved workability, while the total degree of compaction is only marginally lowered by the lower degree of compaction in the new contact points. This is due to the new contact points only constituting a very slight proportion of the total amount of contact points. Even if for example a thousand new contact points are formed, these contact surfaces will be less than per mille of the total contact surfaces, i.e. they have a very slight influence on the end density, which will be determined by the higher degree of compaction of the granules according to the present invention. Moreover, the contact zones between individual, packed granules will hardly be distinguishable from the other contact points, as the general hardening mechanism for systems according to the invention comprises dissolution of solid material by reaction with water, which leads to the formation of ions, a saturated solution and hydrate precipitation.
In a system in which the cement hydrates due to an added liquid, the new contact points will furthermore be filled by hardened phases, which means that the homogeneity increases after the hydration/hardening. By the final degree of compaction being increased in that way, a more dense end product will be obtained, which leads to an increased strength, a possibility to lower the amount of radio-opaque agents and an easier achieved translucency, at the same time as the workability of the product is very good.
According to one aspect of this embodiment, the granules preferably exhibit a degree of compaction above 60%, even more preferred above 65% and most preferred above 70%. Preferably, the granules have a mean size of at least 30 μm, preferably at least 50 μm and even more preferred at least 70 μm, but 250 μm at the most, preferably 200 μm at the most and even more preferred 150 μm at the most, while the powder particles in the granules have a maximal particle size less than 20 μm, preferably less than 10 μm. It should hereby be noted that it is only a very slight proportion of the powder particles that constitute particles having the maximal particle size. The particle size is measured by laser diffraction. The highly compacted granules are manufactured by the powdered material being compacted to the specified degree of compaction, by cold isostatic pressing, tablet pressing of thin layers, hydro-pulse technique or explosion compacting e.g., where after the material compacted accordingly is granulated, for example crushed or tom to granules of the specified size.
The system and material according to the invention have the advantages compared to systems/materials such as glass ionomer cements and pure Ca-aluminate based systems or monomer based filling materials, that it maintains its bioactivity, that it has improved initial strength and that it has long time stability regarding both dimensional aspects, strength and minimised deterioration. The viscosity of the material can be controlled within wide ranges, upon initial mixing of the powdered material and the hydration liquid, from moist granules to an injectable slurry. The material is unique in that it solidifies in at least two steps, i.e. by cross-linking of the organic acid or salt thereof with cat-ions from both the inorganic cement system and the added reactive glass, and by hydration of one or more systems.
Tests were performed to investigate the influence of amount of poly acid and the composition of the chemical bonded ceramic on the mechanical properties. The values are compared to commercial glass ionomer cement and amalgam.
Calcium aluminate ((CaO)3(Al2O3), (CaO)(Al2O3), (CaO)12(Al2O3)7), calcium silicates (CaO)(SiO2, (2CaO)(SiO2), (3CaO)(SiO2), dental glass filler (Schott), poly acid (PAA=poly acrylic acid Mw=50,000, Na-PAMA=poly(acrylic-co-maleic acid) sodium salt Mw=50,000) and reactive glasses (Schott and experimental glass). Glass ionomer cement (Fuji II, GC-corp) and Amalgam (Dispersalloy, Dentsply).
Calcium aluminate was mixed with dental glass, reactive glass, poly acrylic acid and poly(acrylic-co-maleic acid) sodium salt. The calcium aluminate phases were synthesised via a sintering process, wherein first CaO and Al2O3 were mixed to the desired composition and then sintered at elevated temperature for 6 hours. The formed calcium aluminate lumps were crushed and jet-milled to a mean grain size of 1.5 μm and a maximum grain size of 9 μm. The dental glass, calcium aluminate and poly acids were mixed with acetone and Si3N4 marbles for 14 hours to obtain the desired homogeneity. The same procedure was used for the Formulation 8 using Ca silicates. Formulations were made according to (in wt. %):
The formulations were placed in 5 ml jars and wet with liquid and blended in a “Rotomix” (3M ESPE) for 15 seconds followed by centrifugation for 3 seconds. In addition 18 mM of LiCl was added to further increase the hydration speed. The liquid contents were controlled via
with a wc/c=0.32 (refers to the inorganic cement-system), PAA/(reactive glass)=0.14 and w/(reactive glass)=0.37 (refers to the glass ionomer system).
The diametral tensile strength was measured for the six formulations, the amalgam and the glass ionomer cement. The strength was measured after 15 min, 60 min, 4 hours and 24 hours. All samples were stored in phosphate buffer solution (pH 7.4) before measurement of DTS. The pH was measured by soaking a defined amount of material in distilled water (material/water ⅓ by volume) for the same time periods as the DTS-measurements. All storages were at 37° C.
The results of the tests were:
By adding PAA and reactive glass to the calcium aluminate system an increased initial strength can be achieved. Also, by adding (CaO)12(Al2O3)7 the reaction speed is increased and thus also the initial strength. The increase in pH over time for the formulations with calcium aluminate shows that the hydration reaction is similar to the pure calcium aluminate system.
A series of tests was performed to investigate the influence of poly acid on the acid erosion resistance. The values are compared to commercial glass ionomer cement (Fuji II) and to commercial calcium aluminate based dental material (DoxaDent, Doxa AB).
Calcium aluminate (CaO)(Al2O3), dental glass filler (Schott), Na-PAMA=poly(acrylic-co-maleic acid) sodium salt, poly acrylic acid Mw 50000, reactive glass.
The calcium aluminate phases were synthesised via a sintering process where first CaO and Al2O3 were mixed to the desired composition and then sintered at elevated temperature for 6 hours. The formed calcium aluminate lumps were crushed and jet-milled to a mean grain size of 3 μm and a maximum grain size of 9 μm. The dental glass, reactive glass, calcium aluminate and poly acids were mixed with acetone and Si3N4 marbles for 14 hours to obtain the desired homogeneity. The samples in the tests c) and d) were blended to the desired water to cement ratio in 5 ml jars and rotated at 500 rpm for 15 seconds. DoxaDent and Fuji II samples were made according to the manufactures instructions. The acid erosion was measured according to ISO-9917.
The results showed that the tests in b) and c) and d) exhibited an acid erosion of below 0.01 mm/h (below the detection limit) whereas the glass ionomer cement showed a acid erosion of 0.1 mm/h. Thus the results show that addition of poly acid to calcium aluminate does not reduce its acid resistance.
A series of tests was performed to investigate the possible in vitro bioactivity of the calcium based cement material, the glass ionomer cement and the combination of the two. Bioactivity is defined herein as the ability to form apatite on the surface in contact with body fluids.
Calcium aluminate was mixed with dental glass, reactive glass, poly acrylic acid and poly(acrylic-co-maleic acid) sodium salt. The calcium aluminate phases were synthesised via a sintering process where first CaO and Al2O3 was mixed to the desired composition and then sintered at elevated temperature for 6 hours. The formed calcium aluminate lumps were crushed and jet-milled to a mean grain size of 2.5 μm and a maximum grain size of 9 μm. The dental glass, calcium aluminate and poly acids were mixed with acetone and Si3N4 marbles for 14 hours to obtain the desired homogeneity. The same procedure was used for the Formulation 8 using Ca silicates. Formulations were made according to (in wt. %):
0.5 grams of each the formulation were placed in 5 ml jars and wet with liquid and blended in a mixer by 3M/ESPE for 15 seconds followed by centrifugation for 3 seconds. In addition 18 mM of LiCl was added to further increase the hydration speed. The liquids composition were controlled via
with a wc/c=0.32 (refers to the CBC-system), PAA/(reactive glass)=0.14 and w/(reactive glass)=0.37 (refers to the glass ionomer system). For comparison samples of GIC were also made.
The bioactivity was studied by soaking a defined amount of material in simulated body fluid (SBF) (material/SBF ⅓ by volume) for time periods of 1 day, 7 days and 21 days at 37° C. After storage the samples were removed from the SBF, rinsed in distilled water and dried at 37° C. for 48 hours. The surface composition of the formulations was studied with thin film X-ray diffraction (1° angle) and SEM combined with EDX. For each formulation and time period 5 samples were analysed. For SEM the presence of Ca and P on the surface with a ratio 1.67 indicates formation of apatite. In XRD the peaks according to the powder diffraction file for apatite must comply with the pattern from the sample.
The results from the analysis can be seen in the Table below. All formulations with calcium based cements formed apatite on the surface after 21 days. The formulations with low amounts of calcium aluminate did not form the apatite layer as quick as the formulations with much calcium aluminate, which all had apatite on the surface after 1 day. The GIC material did not form apatite on the surface. Thus the combined material can be considered bioactive.
The invention is not limited to the embodiments described herein, but can be varied within the scope of the claims.
| Number | Date | Country | Kind |
|---|---|---|---|
| 0302844-6 | Oct 2003 | SE | national |
| 0401026-0 | Apr 2004 | SE | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/SE04/01577 | 10/29/2004 | WO | 00 | 5/14/2007 |
