Upload
m-ito
View
219
Download
3
Embed Size (px)
Citation preview
In vitro properties of a chitosan-bonded hydroxyapatite bone-filling paste
M. Ito Institute for Dental Science, Matsumoto Dental College, 1780 Gobara, Hwooka, ShlolmL Nagano 399-07, Japan
(Recewed 3 1 July 1989; revised 25 August 1989; accepted 2 November 1989)
A possible bone substitute material for dental treatment was developed and tested. The material is
composed of powdered hydroxyapatite (HA), ZnO and CaO, kneaded into a chitosan sol to make a quick-
hardening paste. A composittion was found which showed neutral pH, short setting time, and relatively
high compressive strength. The use of such a paste for the treatment of periodontal defects or the
augmentation of edentulous alveolar ridges may alleviate problems now associated with the implantation
of particulate HA, such as early migration of particles and recontouring of the implant.
Keywords: Hydroxyapatite, bone substitutes, dental materials, chitosan
The past decade has seen many favourable reports on the
use of particulate hydroxyapatite (HA) as a bone substitute in
dental treatment. Applications include repair of periodontal
defects’, ‘, implantation of tooth extraction sockets to
maintain alveolar ridge height3,4, and augmentation of
deficient alveolar ridges to improve denture support and
stability5-8. At the same time, however, dissatisfaction with
the delivery system of particulate HA has been expressed.
When placed in the implant site, the particles are loose and
can migrate beyond the intended area or be lost through
dehiscence of the incision6, ‘, ‘.
Stabilization of the implant moreover appears to
require at least one month. During this time some settling
and recontouring occurs, with a corresponding reduction in
implant sizelo,“. These problems have prompted research
on improved methods of implantation. Thus Gongloff eta/.”
report that confining the particles at the implant site with
tubes of resorbable collagen prevents particle migration;
similar success has been claimed for tubes made of
polyglycolic mesh13. Whether either of these materials will
also prevent the settling and recontouring of the implant
remains to be investigated.
A different solution to the problem of HA delivery may
lie in thedevelopment of a quick-hardening paste, containing
powdered HA, that can be easily syringed into the implant
site. This paper reports the experimental development of
such a paste, made with powdered HA (Mitsui Toatsu), and
using a sol made with chitosan (Shin Nippon Chemical) as a
binder. Chitosan was chosen because, like collagen, it is
resorbable, biocompatible, and readily available (being easily
derived from the naturally abundant macromolecule chitin);
Correspondence to Dr M. Ito.
0 1991 Butterworth-Helnemann Ltd. 0142-9612/91/010041-05
in addition, chitosan has been reported as having haemo-
static and wound-healing properties’4,‘5. Because the
chitosan sol is highly acidic, however, it was necessary to
include some substance in addition to HA to achieve
neutralization. A number of common non-toxic reagents
were tested for this purpose. The oxides of Zn (Kant0
Chemical) and Ca (Junsei Chemical), when mixed In minor
proportions with HA, were found to neutralize the chitosan
sol while inducing an acceptably short setting trme.
The purpose of the experiments described here was to
find a ratio of these three substances that would yield a
paste, when kneaded into a fixed amount of chitosan sol,
having a suitable setting time and hardness when set, aswell
as a neutral pH value. Table 7 lists the various proportions of
powdered elements tested; designations of the mixtures
hereafter follow the code given in the table. Data on the
setting times, compressive strengths and pH values of these
mixtures are reported.
The C2/26 powder m’xture appeared most promising
in that it showed a neutral pH value, one of the shortest
setting times, and the highest compressive strength of all the
mixtures tested. It was accordingly selected for further tests
of its suitability for potential application.
Samples of the hardened paste made with this mixture
were subjected to X-ray microanalysis and X-ray diffraction
pattern analysis. Experiments were also conducted which
involved several factors associated with the kneading of the
paste: the effects on pH level, setting time and compressive
strength of varying the amount of chitosan sol kneaded with
the powdered ingredients; the changes in pH level and
compressive strength over time elapsed from the onset of
kneading; and the effect on compressive strength of varying
the time that the chitosan sol is allowed to stand before
kneading.
B/omatenals 19.9 1, Vol 12 Januaw 4 1
Hydroxyepafite bone-filhng paste: M. tto
Table 1 Percentage composition of powder mixtures tested
Code CaO ZnO Hydroxyapatite
c2/Z2
C2/Z4
C2/26
C3/‘Z2
C31Z4
C3/26 C4/22
c4/24
C4/‘Z6
96 94 92
95
93
91
94 92
90
MATERIALS ARID ~ETHDDS
The sol was made by dissolving 2.5 g of chitosan SC in a solution of 2.5 g malic acid (Junsei Chemical) in 47.5 ml distilled water. Except where noted, this was allowed to stand for 24 h. The powder mixtures listed in Table 1 were kneaded manually with a spatula into the chitosan sol to make pastes. All procedures were conducted at a controlled room temperature of 23 + 1 “C.
Setting time
A 0.5 g sample of each powder mixture listed in Table 1 was kneaded into 1 .O g of chitosan sol for 30 s, and the resulting paste poured into a cylindrical mould (3 mm high, 10 mm inside diameter). The setting time was measured as the time elapsed from the onset of kneading to the point when the paste did not adhere to the end of a methyl methacrylate rod. Five assays were conducted with each powder mixture. The largest and smallest values were discarded, and the average of the remaining three values was taken as the setting time. The same procedure was followed using the C2/Z6 powder (see Tab/e I) to test the effect of increasing the ratio of chitosan sol to powder. The ratios tested used 0.5 g of powder with 1.2 g and t .5 g of sol,
pH value
For each powder mixture, five hardened specimens were made using 0.5 g each of powder and 1 .O g of sol, kneaded for 30 s and injected with a syringe into a stainless steel mould (10 mm high, 4 mm inside diameter). The moulds were covered with stainless steel plates and firmly secured with screw jacks. At 30 min after the onset of kneading, all five specimens were removed from the moulds and submerged in a bottle filled with 20 ml of Ringer’s solution. At 12 h after the onset of kneading, the pH value of the solution was measured with a pH meter (Hitachi-Horiba). Three assays were made for each powder mixture, and the average taken as the pH value for that mixture. The same procedure was followed with the CZLZ6 mixture using higher ratios of chitosan sol (0.5 g powderto 1.2 g and 1.5 g sol).
The C2/Z6 mixture was also used to test the relationship between the time elapsed from the onset of kneading and the pH value. The procedure followed the one just described, except that the specimens were removed from their moulds and submerged in the Ringer’s solution 15 min after the onset of kneading, and the pH value of the
Compressive strength
For each powder mixture, three hardened specimens were made with the procedure followed in the test of pH values. At 30 min after the onset of kneading, all three specimens were removed from the moulds and submerged in a bottle filled with 20 ml of Ringer’s solution and stored until 12 h had elapsed from the onset of kneading. The compressive strength of each specimen was measured using a universal testing machine (Shimadzu DSS-500), at a head ram speed of 5 mm/min. Three assays were conducted and their values averaged for each mixture. The same procedure was followed with the C2/Z6 mixture using higher ratios of chitosan sol (0.5 g powder to 1.2 g and 1.5 g sol).
The C2/Z6 mixture was also used for two further tests involving different times after the onset of kneading. In the first, measurement of the compressive strength was conducted at 3 h, and again at 24 h after the onset of kneading. In the second, the time elapsed between the preparation of the chitosan sol and the initiation of kneading was varied: 10, 60, 90, 120, 180 and 480 min.
~o~hological obse~ation and X-ray diffraction analysis
One gram of the C2/Z6 mixture was kneaded with 0.5 g chitosan sol, spread on a glass plate, and allowed to harden for 12 h. A 3 mm2 segment was cut from the hardened specimen, coated with vapourized gold, and the coated surface analysed with an X-ray microanalyser (Nippon Electronics JCXA-733). A larger segment, prepared in the same manner but with no coating, was examined with an X- ray diffraction analyser (Shimadzu CD-l 0), operated at 5 kV and 500 mA, using a copper Ka target and a nickel filter.
RESULTS
Setting time
The average values and 99% confidence levels for each powder mixture are presented in Figure 1. The general tendency was for a decrease in setting time with an increase in the amounts of both CaO and ZnO. The C2LZ6 mixture had a low setting time of 2 min 20 s. When the ratio of sol to the C2/‘Z6 mixture increased, however, the setting time also increased (Figure 2).
pH value
pH values of the powder mixtures ranged from a low of 6.5 (C2LZ2) toa high of 8.0 (C4/Z6). Higher pH values resulted from increases in both CaO and ZnO. Neutral values of 7.0 were obtained for two mixtures, C2/Z4 and C2/‘Z6. pH values decreased with higher ratios of chitosan sol to the C2/Z6 powder (Figure 3).
The time efapsed from the onset of kneading had moderate effect on the pH value. For the C2/‘Z6 mixture, the pH level was 6.86 f 0.2 at 15 min after kneading, and increased to a peak of 7.3 i 0.09 at 4 h. By 5 h it declined to 7.18 f 0.10, a value close to that measured at 12 h of 7.03 + 0.04.
Compressive strength
solution was measured immediately. Subsequent measure- The compressive strengths measured for the various ments were made every 5 min until 30 min after the onset of powder mixtures are presented in Figure 4. The greatest kneading, and from then on at every hour from the onset of value was for the C2LZ6 mixture (22 kg/cm2). Greater kneading until 5 h had elapsed. compressive strength was generally observed for increases
42 Biomaterials 199 1, Vol 12 January
Hydroxyapatite bone-filling paste: M. lto
6
Ia
2
20
18
-16
*; 14 w
12
; 10 .-
k8
.E 6 =: a,4 U-I
2
/l.O /l. 2 A 5
Powder/Sol Ratio cm Figure 3 pH values for different ratios of chitosan sol with the C2/Z6 mixture.
L
2 4 6 Zn 0 %
Figure 1 Setting times for the powder mixtures tested: ?WaO 2%; q CaO 3%; q CaO 4%
*
-
2 4 6 Zn 0 Oio
Figure 4 Compressive strengths for the powder mixtures tesfed. 12 hr E? CaO 2%; q CaO 3%; 0 CaO 4%
aJ 8 E i=6
n OS y2 OX5
Powder / Sol Ratio g/g *
-
Figure 2 Setting times for different ratios of chitosan sol with the C2/26 mixture r -
0.5/ l-rl- in both CaO and ZnO. When higher ratios of sol to powder
were used with the C2/Z6 mixture, the compressive
strength decreased (Figure 5). No significant variation was observed in the compres-
sive strength for different intervals between the onset of
kneading and the time of measurement for the C2LZ6
powder. Varying the time between the preparation of the
chitosan sol and the onset of kneading, however, did have a significant effect (Figure 6). Whereas values slightly under
20 kg/cm2 were observed with the C2LZ6 powder for times
0.5/ 0.5/ /l.O /1.2 /1.5
Powder/Sol Ratio s/s Figure 5 Compressive strengths fordifferent ratios ofchitosan sol with the C2/Z6 mixture.
Eiomateuals 1991, Vol 12 Januav 43
Hydroxyapatite bone-filling paste: M. ho
Figure 6
10 60 90 120 150 180 460
Elapsed Time (min)
Effect on compressive strength of varying the time elapsed between the preparation of the chitosan sol and the onset of kneading for the C2/26 mixture.
of 10 and 60 min, the compressive strength measured roughly 50% more (32.1-33.6 kg/cm*) for times of 90- 150 min. For longer intervals, values of slightly more than 20 kg/cm* were similar to that obtained under the normal procedure in which the sol is allowed to stand for 24 h before kneading.
Morphological observation and X-ray diffraction analysis
The results of an X-ray microanalysis of the hardened paste made with the C2/26 mixture are shown in Figure 7. The
even distribution of Zn suggests thorough mixture of all elements in the paste. The similarities between the distribu- tions of Ca and P indicate that the hydroxyapatite remains stable in the paste. This was further substantiated by the results of the X-ray diffraction analysis (Figure 8). The
-I ~..
Figure 8 X-ray diffraction patterns: (a) hydroxyapatite, lb) hardened C2/Z6 paste. Peaks caused by the presence of ZnO in the mixture are labelled.
Figure 7 X-ray microanalysis of the hardened C2/26 paste: (aJ composite, (b) phosphorus, (cl calcium. (d) zinc.
44 Biomaterials 199 1. Vol 12 Januaw
Hydroxyapat& hone-filltng paste: M Ito
pattern obtarned from the paste made with the C2126
mixture is virtually identical to that produced by hydroxy-
apatite alone.
DISCUSSION
The results of these tests indicate the C2/26 mixture as the
most suitable for use in a quick-hardening paste, containing
powdered HA, for possible applications as a bone substitute
material. The paste made with this mixture achieves a stable
and neutral pH value within 5 h of kneading. It also has a
short setting time (approx. 2 min), and the highest compres-
sive strength of the mixtures tested. Moreover, with a slight
increase in the ratio of chitosan sol to the powder (using
1.2 g of sol to 0.5 g powder), the setting time may be
lengthened to more than 4 min with only a moderate loss in
compressive strength, and without seriously affecting the
pH level. The loss in compressive strength may perhaps be
compensated for by letting the chitosan sol stand for at least
90 min, but not more than 150 min, before kneading the
paste, a procedure which increased compressive strength
more than 50% when a ratio of 1 .O g sol to 0.5 g powder
was used.
The paste described in this report has a slightly elastic
consistency when set. Clinical application of this paste, as a
bone substitute in dental treatment, may accordingly reduce
the incidence of inflammation in the surrounding soft tissues
noted when sharp-edged HA particles are used for this
purpose’6. Before such applications can be considered,
however, thorough evaluation of the suitability of the HA
paste as an implant material is necessary. A histological
study is currently being conducted as one aspect of this
research, and the results will be reported in the near
future.
ACKNOWLEDGEMENTS
The author wishes to acknowledge Mr S. Akahane for his
assistance with the X-ray diffraction analysis and the X-ray
microanalysis for this study. Dr W. Edwards is acknowledged
for his help with the preparation of the manuscript.
REFERENCES
1
2
3
4
5
6
7
8
9
10
11
12
13
14
15
16
Ogltvte, A., Frank, R.M.. Benque, E.P., Gtneste. M.. Heughebaert. M.
and Hemmerle, J.,The btocompatrbtlrtyof hydroxyapattte implanted rn
the human pertodontum. J. Periodont. Res 1987, 22, 270-283
Crantn. A-N.. Tobin, G.P. and Gelbman. J., Appltcattons of hydroxyl-
apatite tn oral and maxtllofactal surgery. I. Perrodontal and endosteal-
Implant reparrs. Compend. Contm. fduc. Dent. 1987, 8, 254-256,
258, 261-262
Dentssen. H.W. and de Groat. K., lmmedtate dental root Implants from
synthetrc dense calcrum hydroxylapatrte. J Prosthet. Dent. 1979.42,
551-556
Scheer. P. and Boyne, P.J., Matntenance of alveolar bone through
rmplantatton of bone graft substttutes rn tooth extraction sockets,
J. Am. Dent. Assoc. 1987, 114. 594-597
Cranrn, A.N., Tobtn. G.P. and Gelbman. J., Applicattons of hydroxyl-
apattte rn oral and maxillofacral surgery. II. Rtdge augmentanon and
repair of major oral defects, Compend Conttn Educ. Dent. 1987. 8,
334-335, 337-338, 340, 342-344
Kent, J.N., Qutnn. J.H., Ztde, M F, Frnger, I.M., Jarcho. M. and
Rothstetn, S.S.. Correctton of alveolar ridge deftctenctes with
nonresorbable hydroxylapattte, J Am Dent. Assoc 1982, 105,
993-1001
Larsen, H.D.. Frnger, I.M.. Guerra. L.R. and Kent, J.N.. Prosthodontrc
management of the hydroxylapatrte denture patient: a preltmtnary
report, J Prosthet. Dent. 1983. 49, 461-470
Rothstern. S.S., Paw, D.A. and Zacek. M.P.. Use of hydroxylapatite for
the augmentation of defrcrent alveolar ndges, J. Oral Maxillofac. Surg.
1984,42, 224-230
Takagr. Y.. Hydroxylapattte nt yoru shtsotet zoset no shtppat shore
kara manabu [Failure cases of alveoloaugmentatron wrth hydroxy-
apatrte ceramics], Nihon shika hyoron 1988, 543, 57-68
Deslardins. R.P.. Hydroxyapattte for alveolar ridge augmentanon:
rndrcatrons and problems. J. frosther. Dent. 1985. 54, 374-383
Larsen, H.D. and McDonald. G.T., Use of hydroxylapattte to correct
maxtllary. antenor hypermobtle ridge trssue, General Dentlstly 1984,
32, 237-240
Gongloff. R K. and Montgomery, C.K.. Experimental study of the use of
collagen tubes for lmplantatton of parttculate hydroxylapatrte. J. Oral
Maxillofac. Surg. 1985, 43, 845-849
Stlverberg. M.. Singh, M.. Sreekanth. H. and Gans. 8.J.. Use of
polyglycolrc acid mesh to conftne partrculate hydroxylapattte for
augmentanon of bone rn the rat. J Oral Max/llofac. Surg. 1986, 44,
877-886
Murzarellr. R.C.C. Chmn. Pergamon Press, Oxford, UK, 1977,
pp 263-264
Hrrano, S. and Notshtkt. Y.. The blood compatrbrltty of chttosan and N-
acylchttosans, J. Biomed. Mater. Res. 1985. 19, 413-41 7
Mtstek, D.J.. Kent. J.M. and Can, R.F., Soft ttssue responses to
hydroxylapahte partrcles of drfferent shapes, J Oral Maxillofac. Surg.
1984, 42, 150-l 60
B/omatenals 1991, Vol 12 Jarwan/ 45