NBSIR 80-2168

Properties and Interactions of

Oral Structures and Restorative

Materials

James M. Cassel, J. A. Tesk, G. M. Brauer, J. M. Antonucci,

W. Wu, J. E. McKinney, R. P. Whitlock, and R. Hinman

Dental and Medical Materials

Polymer Science and Standards Division

Center for Materials Science

National Measurement Laboratory

National Bureau of Standards

Washington, DC 20234

Annual Report for Period

October 1, 1979 thru September 30, 1980

November 1980

Interagency Agreement

YOI-DE-4001 5-1

1

—QO

100

. U56

80-2163

1980

Ci 2

r ed for nal Institute of Dental Research

isda, MD 20014
I
NBSIR 80-2168

PROPERTIES AND INTERACTIONS OF

ORAL STRUCTURES AND RESTORATIVE

MATERIALS

James M. Cassel, J. A. Tesk, G. M. Brauer, J. M. Antonucci,

W. Wu, J. E. McKinney, R. P. Whitlock, and R. Hinman

Dental and Medical Materials

Polymer Science and Standards Division

Center for Materials Science

National Measurement Laboratory

National Bureau of Standards

Washington, DC 20234

national bureau

of standards

LIBRARY

AUG 7 1981

not dec - c; rc

.

CXcfdo

no- %0'c5/6#

mo

Annual Report for Period

October 1, 1979 thru September 30, 1980

November 1980

Interagency Agreement

YOI-DE-4001 5-1

1

Certain commercial materials and equipment are identified

in this report to specify the experimental procedure.

In no instance does such identification imply recommendation

or endorsement by the National Bureau of Standards or

that the materials and equipment identified are necessarily

the best available for the purpose.

Prepared for National Institute of Dental Research

Bethesda, MD 20014

U S. DEPARTMENT OF COMMERCE, Philip M. Klutznick, Secretary

Luther H. Hodges, Jr., Deputy Secretary

Jordan J. Baruch, Assistant Secretary for Productivity, Technology, and Innovation

NATIONAL BUREAU OF STANDARDS. Ernest Ambler. Director
• V. ;

nun

•"

si». * * V
TABLE OF CONTENTS

Page

ABSTRACT i

SUMMARY U

INTRODUCTION viii

TECHNICAL REPORT 1

I. Dental Composite, Resin, Sealant, and Cement 1 Chemistry and Development

A. New Monomers for Reducing Polymerization 1 Shrinkage

1. Diurea Dimethacrylate Monomer 1

2. Methacryloxyethyl-l-Adamantane Car- 3

boxy! ate

3. Bi s-p- ( 2 Methacryloxyethoxy-hexafluoro- 4

2-propyl) Benzene (Bis-p-MEHFPB)

B. Development of New Initiator/Accel era tor 4

Systems

1. Amine Accelerators 4

a. Structure-Property Studies Employing 5 Slower Acting Amine Types Including

Surface Active or Adhesive Generating

Ami nes

b. Development of Fast-Acting, Biocompatible 12

Amine Accelerators

c. Amines as Photoinitiators of Polymeri- 16

zation

d. Amines for Improved Color of Denture 17

Base or Repair Materials

2. Non-Amine Accelerators 21

C. Analysis for Degree of Polymerization of Dental 21

Resins

1. Differential Scanning Calorimetry (DSC) 21

2. Solid State ^C NMR Spectroscopy 24
3. Laser Raman Spectroscopy 24

4. Fourier Transform Infrared Spectroscopy 25

D. Resin/Filler Coupling Improvement for 25

Composites

E. Peroxy Esters and Hydroperoxides as More 29

Storage Stable Initiators for Composite

Resins

F. Autocurable Polymer Blends as Routes to 35

Improving Chemical and Mechanical

Properties of Denture Base and Other

Dental Materials

G. Status Report - The Desirability of Using 36

Radiopaque Plastics in Dentistry

H. Improving Dental Cements 38

II. Development of Adhesive Bonding Techniques 41

A. Adhesion Promoting Functional Monomers 41

1.

Isocyanate Urea Methacrylates 41

B. Surface-Active Amine Accelerators as 43

Adhesion Promotors

C. Patent Literature Adhesives with Potential 46

for Dental Application

III. Wear Resistance and Mechanical Properties of Dental 51

Materials

A. Pin and Disc In Vitro Wear Measurements 52

B. Subsurface Damage Analysis Investigations 67

1. Analysis Applied to Clinically Worn 67

Composite Materials

2. Analysis Applied to In Vitro Worn 69

Composite Materials

3. Analysis Applied to Thermal Cycled, 71

Acid Immersed or Compression Fatigued

Composite Specimens

4. Analysis Applied to Organic Solvent

Immersed Composite Specimens

C. Three-Body Wear Test 73
IV. Dental Alloys, Ceramics and Implants 79

A. Porcelain-Alloy Characterization ou

1. Thermal Expansion 80

2. Compatibility Index 81

3. Porcelain/Alloy Split Ring Studies 82

B. Dental Alloy Castability 84

C. Radiation Dose from Neutron Activated 85

Dental Materials

REFERENCES 86

INVITED TALKS 88

ABSTRACTS (PRESENTED AT AADR & I ADR 1980) 89

PAPERS PUBLISHED 90

MANUSCRIPTS IN REVIEW 91

ABSTRACTS SUBMITTED FOR 1981 MEETINGS IADR & AADR 92
VVniM0

II

ilaa
ABSTRACT

Significant accomplishments in the field of dental research for the

past year include:

(1) Development of more efficient, less toxic polymerization

accelerators . Biocompatible 4,4,N-diethylaminophenylacetic acid, which

is reactive at four-fold reduced concentration relative to currently

used amines is very promising.

13

(2) Raman, IR and C NMR spectroscopy and DSC are being compared

for investigation of dental resin polymerization.

(3) Solvent carrier and amine catalysts have been shown to influence stability of silane-silica bonding in composites.

(4) A state-of-the-art report on radiopaque plastics in dentistry

was prepared.

(5) A silver staining technique developed to assist investigation

of mechanisms of degradation and wear in composite restorations yields

useful information on subsurface microdefects in in vivo and in vitro

worn specimens. In vitro wear with a pin-on-disc machine indicates

increased wear of a composite is generated by going from a very hard

(apatite) pin to a softer (stainless steel) pin. A wear test placing

greater emphasis on shear forces generated via food particle interplay

with teeth has been developed.

(6) With thermal expansion measurements, significant differences

in the excess volume retained on cooling porcelains fired as per manufacturers' recommendations. Gap and shape changes in a porcelain

veneered to alloy split ring offer promise for determining compatibility

of porcelains for alloys.
SUMMARY

The research on dental materials that is described in this report

is a part of a larger total effort that is carried out in collaboration

with the American Dental Association Health Foundation. The U. S. Army

and Navy Medical R&D Command and the School of Dentistry, Georgetown

University are also part of this collaborative effort through support

funding and/or assignment of research personnel.

While the bulk of the research progress in this report represents

only the efforts of NBS staff supported under the Interagency Agreement

with NIDR, there will of necessity be a degree of contribution that

originates through the intentionally strong interaction among all

persons participating in this collaborative dental program.

The objective is to effect improved dental health through development of new knowledge and better understanding of the mechanical, chemical,

and physical properties of restorative and caries-preventive materials

and the mechanisms by which clinical performance is governed.

A wide variety of techniques has been brought to bear to generate

approaches to new and improved adhesive restorative dental materials

These include: syntheses of components to improve current composite

restorative materials and pit and fissure sealants and development of

techniques that can be used to examine the extent of the polymerization

reaction in dental resins and components, investigation of new approaches

to bonding restorations to tooth surfaces, determination of the mechanisms

by which composite systems wear and degrade in clinical use coupled with

production of accelerated laboratory wear test data, and development of

characterization methods and data for analyzing the compatibility of

dental porcelains for base metal alloys.

ii
A wide range of analytical techniques have been explored for utility

in the investigation of the state, e.g. reacted or unreacted, of the

carbon-carbon double bonds characteristic of the methacrylate monomers

that are polymerized in the hardening reaction of dental resins and

composites. Complete reaction of this double bond in a dimethacrylate

produces chain lengthening as well as cross linking - both characteristics

which influence mechanical properties and probably wear resistance.

Unreacted double bonds incorporate potential oxidative degradation sites

and if they are present in the hardened composite as a component in a

monomethacrylate, a plasticizing effect can occur and the potential for

extraction by oral fluids exists. The advantages and disadvantages of

Fourier transform infrared (FTIR), Raman and C NMR spectroscopy as

well as differential scanning calorimetry are being assessed, and initial

data have been obtained with the analytical techniques that are most

appropriate to the problem.

Evaluation of several previously synthesized amines as polymerization

accelerators for dental resins and composites has been completed with

the result that one amine, 4,4,N-diethylaminophenylacetic acid, is

sufficiently reactive to be used at a concentration one fourth to one

fifth that of currently employed amines. This very low amine concentration coupled with its anticipated generic biocompatibility offers much

promise for its use with dental composite systems. On the other hand,

these more reactive amines when combined with very heat stable peroxyester initiators unfortunately did not produce composite formulations

with significantly improved storage stability.
An important factor in the durability of dental composite restorations

is the effectiveness of the coupling between reinforcing filler and the

resin matrix. Experimentation on the effect of the nature of the carrier

solvent used to deposit a silane coupling agent on the filler particles

has now shown that certain solvent types in conjunction with selected

amines resulted in greater reaction of the coupling agent and a consequently improved hydrolytic stability in the silica-silane bond.

A state-of-the-art report on the use of radiopaque plastics in

dentistry was prepared for review by the American Dental Association

Council on Dental Materials, Instruments and Equipment. The frequency

of incidents such as ingestion, inhalation, or embedding plastic materials

or devices has been shown to be low but the severity of such incidents

demands rapid location, diagnosis and removal. Most foreign body accidents

are found to involve partial or full plastic dentures but a case for

radiopaque materials can also be made for composite filling materials,

temporary crown and bridge materials and impression materials. Applicable

radiopaque standards will be a requirement.

Synthesis of several 2-ethoxyphenol (guaiacol) derivatives, investigation of their reaction with metal oxides and evaluation of the properties

of the resulting cements indicated cements with properties intermediate

to those of zinc oxide eugenol and ethoxybenzoic acid can be readily

formulated.

PolySAM-1 , a multifunctional surface-active amine polymerization

accelerator and several simpler surface-active amine promoters were

evaluated as polymerization accelerators and adhesion promoters. While

strength measurements on BIS-GMA composites formulated with hydroxyapatite

iv
as filler did not yield adhesion results as definitive as those obtained

by applying a similar analysis to silanized and unsilanized glass filler

composites, the indication is that certain surface-active amine promoters

under selected conditions enhance bonding of dental resins to hydroxyapatite.

Understanding the mechanism of degradation and wear in dental

composite is a crucial first step to developing more durable materials.

To this end a silver staining technique has been demonstrated to yield

useful information regarding the presence or absence of subsurface

microdefects in both in vivo and in vitro worn specimens. Examination

of a limited number of removed class 2 restorations that showed anatomical form loss revealed zones of damage 10-200 pan beneath the external

surface. As a result of preliminary silver staining results, an in

vitro wear test was developed to place greater emphasis on shear forces

via viscous media that simulate those of three party (opposing teeth and

food particles) interplay in the mouth. Replica microscopy and the

silver staining techniques are to be used to determine wear damage in

this accelerated in vitro test. A parallel project involves efforts

to ascertain the extent of interaction of solutions of known solubility

parameter with BIS-GMA resin. Microhardness measurements and silver

staining indicate negligible interaction with organic acids or water but

strong interaction with certain organic solvents. These effects are to

be correlated with in vitro wear results.

Using a pin-on-disc accelerated wear test where the volume of

restorative material in the disc that is lost per unit time or distance

is the measure of the wear rate of a pin-on-disc couple, the wear rate

of a composite has been shown to be much increased by going from a very

hard (tooth enamel or synthetic apatite) to a softer (stainless steel)

v
pin. By contrast, the wear rate of dental amalgams is little affected

by choice of pin. In pin-on-disc wear measurements involving amalgam,

the presence of a passive layer on the amalgam similar to that presumed

to be present constantly in the clinical situation, has been shown to

significantly retard wear.

In the area of dental alloy and ceramic research, thermal expansion

measurements on a number of porcelains and alloys have been completed, a

preliminary report presented at the 1980 IADR meeting and an invited

paper given at the 1980 Annual Meeting of the International Precious

Metals Institute. Significant differences in the porcelains, fired

according to manufacturers instructions, have been observed in that

large variations in the amount of excess volume retained upon cooling is

indicated. Since compatibility of porcelain for alloy (emphasis is on

base metal alloys) depends not only on stresses set by differences in

thermal contraction but on geometrical shape and the thermal relief of

stress, a split ring constructed from porcelain veneered to the alloy

and approximately equal in size to a dental crown has been designed.

Experimental and theoretical results of studies of gap and shape changes

with the split ring indicate that a previously derived mathematical

expression for compatibility is not adequate to describe the complex

interactions and that some form of stress relief occurs at temperatures

lower than the glass transition temperature, T , of the porcelain. A

modification of the sprue system used in an earlier version of a castability test developed in this laboratory has reduced specimen to specimen

variation with base metal alloys by more than one-half. Preliminary

visual examination of cast clinical crowns indicated a direct correlation between castability test scores and the quality of the margins of

clinical crowns cast from the same materials.
In an effort to define isotopes that may present hazards upon

neutron activation following sublethal neutron exposure, calculations

have been made to estimate the additional dose of radiation (3 and y)

delivered to local oral tissue by neutron activated gold crowns. The

calculations indicate a 50 REM neutron dose could subsequently be accompanied by as much as 30 REM.

vii
INTRODUCTION

The National Bureau of Standards is primarily a measurement organization.

Paths from measurement to improved dental service lead from measurement and

characterization to development of new techniques for using materials, to

laboratory prototypes of improved materials and devices, to clinical evaluation, and finally, to commercial production by industry.

The dental research program at NBS is a cooperative effort both in

personnel and funding, involving the American Dental Association and the

U. S. Army and Navy Medical R&D Commands. With the exception of the research

on porcelain fused to base metal alloy - research also participated in and

partially funded by the U. S. Navy Medical R&D - the research described herein

is only that portion of the dental program supported by interagency agreement

with the National Institute of dental Research.

The objective of the research effort discussed briefly in the following

pages is to effect improved dental health through development of new knowledge

and better understanding of the mechanical, chemical and physical properties of

materials used or potentially of use in restorative and preventive dental

practices. The four major areas of research as approved in the interagency

agreement are given below:

I. Dental Composite, Resin, Sealant and Cement Chemistry and Development

II. Development of Adhesive Bonding Techniques

III. Wear Resistance and Mechanical Properties of Dental Materials

IV. Dental Alloys, Ceramics and Implants

viii
I. Dental Composite, Resin, Sealant, and Cement Chemistry and Development

A. New Monomers for Reducing Polymerization Shrinkage

1. Diurea Dimethacrylate Monomer

The synthesis of the diurea dimethacrylate, TBAEM-HDI,

from the reaction of N-t-butyl -2-ami noethyl methacrylate (TBAEM) and

hexamethylene di isocyanate (HDI) was described earlier [1],

CH..

I 3

2ch

2

=c-c-o-ch

2

ch

2

-nh + ocnch

2

ch

2

ch

2

ch

2

ch

2

ch

2 nco

0

TBAEM

CH^-C-CH q O | o CH 0

ChL

i 3

HDI

CH

2

C1

2

, Et

3 N

25°C

0

ll 0 CHo

ll i d

CH

2

=C-C-0-CH

2 CH2

-N-C-NHCH

2 CH2 CH2 CH2

CH

2

CH

2

-NHC-N-CH

2

CH

2

OC-C=CH

2

0 CH

3

-C-CH

3

CH 0

W TBAEM-HDI ch3

-c-ch

3

CH 0

Preliminary structural confirmation of the white waxy solid monomer was

obtained by infrared and NMR spectral analyses. TBAEM-HDI has a molecular

weight of 538 compared to 512 for BIS-6MA and has two tri -substituted

urea groups, each having a bulky t-butyl substituent. The relatively

high molecular weight and hindered nature of the urea linkages in this

monomer should yield dental resin formulations with low polymerization

shrinkage. Setting time and tensile strength values for a few formulations are given in Table 1.

The diametral tensile strengths of the composites, all of

which exhibited excellent initial color and very good color stability,

were above the ADA specification minimum (34 MPa). These formulations

1
Table 1 i

o

SETTING TIMES AND 24-HR. DIAMETRAL TENSILE STRENGTHS OF

EXPERIMENTAL COMPOSITES* BASED ON TBAEM-HDI

Diametral Tensile Strength

Formulation Monomer System Wt. %

Setting Time

(Min.

)

± Std. Dev. in MPa

(No. of Specimens)

1 TBAEM-HDI 77.0% 3.0 43.7 ± 2.5 (5)

NPGDMA 22.7%

DHPPTa 0.27%

2 TBAEM-HDI 77.0% 2.5 42.6 ± 3.1 (4)

NPGDMAb 22.6%

DHPPT 0.37%

3** TBAEM-HDI 75.0% 2.0 39.6 ± 3.0 (5)

HMGDMAC 24.7%

DHPPT 0.3%

4 TBAEM-HDI 75.0% 2.0 44.6 ± 3.9 (4)

HMGDMA 24.7

DHPPT 0.3%

5 TBAEM-HDI 85.0% 2.5 45.2 ± 3.5 (5)

DMGDMAd 14.7%

DHPPT 0.3%

6 TBAEM-HDI 82.0% 3.5 37.6 ± 2.2 (5)

TEGDMA 17.9%

DMSXe 0.13%

7 *** Same as above 3.0 40.5 ± 1.4 (5)

8 TBAEM-HDI 70.0% 1.5 44.8 ± 1.4 (5)

TEGDMA' 29.8%

DMSX 0.23%

9 TBAEM-HDI 80.0% 2.0 42.2 ± 3.4 (5)

TEGDMA 19.7%

DHPPT 0.3%

10 TBAEM-HDI 80.0% 1.5 46.4 ± 1.5 (5)

TEGDMA 19.6%

DHPPT 0.4%

*Powder/l iqui d formulations used with P/L = 3 except where noted. Powder is usual glass filler silanized and coated with 1% Benzoyl Peroxide (BP).

**P/L = 2.5.

***P/L = 2.5 and blended glass filler used (equal parts 1% BP and 0.3% AA glass).

a DHPPT = N,N-di- (2-hydroxypropyl )-p-toluidine.

b NPGDMA = Neopentyl glycol dimethacrylate.

C HMGDMA = Hexamethyleneglycol dimethacrylate %

d DMGDMA = Decamethyleneglycol dimethacrylate.

e DMSX = N,N-dimethyl -sym-xyl idene.

^TEGDMA = Triethyleneglycol dimethacrylate.

2
employed diluent monomers that are commonly used with BIS-GMA dental

resin systems. Assuming a comparable degree of polymerization for

TBAEM-HDI and BIS-GMA monomer systems, the somewhat lower DTS values

found in the case of the former may be indicative of a less brittle

organic matrix.

2. Methacryloxyethyl-l-Adamantane Carboxyl ate

The synthesis of the bulky monofunctional monomer, methacryloxyethyl -1-adamantane carboxyl ate (MAC), from 1-adamantane carboxyl

chloride (AD^-Cl) and 2-hydroxyethyl methacrylate (HEMA) was described

earlier [1].

8 8 | H

3 CH

2

C1

2

ADC-C1 + H0CH

2

CH

2

0C-C = CH

2

8 8?h

3

adc-och

2

ch

2oc-c * CH2

Et^N = triethyl amine

A preliminary dental resin formulation employing this non-volatile

liquid monomethacrylate of relatively low viscosity, with silanized.

peroxidized glass filler gave encouraging results.

Setting

Experimental Formulations P/L Time (min)

BIS-GMA 64.8% 3 3.0

MAC 26.4%

CDMDMA

a 8.6%

DMAPE

b 0.2%

The composite exhibited excellent initial color

a = Cyclohexane dimethanol dimethacrylate

b = 4-N,N-dimethylaminophenethanol

Diametral

Tensile Strength

45.2 1.4 (4)

3
3. Bis-£-(2-Methacryloxyethoxyhexafluoro-2-Propyl ) Benzene

The previously described [1] method used in the synthesis

of the dimethacryloxyethoxy derivative of meta bis(2-hydroxyhexafluoro2- propyl) benzene was applied to the synthesis of the corresponding

para isomer as shown below.

CFo 0

i 3 ii C-0H+2BrCH o CH o 0C-C=CH9

| <- L | c cf

3

ch

3

k

2 co3

, bht

v DMSO, 90-100°C, 7 hours

CH,

i J CH0

= C-C-OCHoCHo-O-C-1 2

U,, 2

?

F 3 | H

3

-c-och

2 ch

2

oc-c=ch

2 :f„ o

Bi s-p-MEHFPB (MW = 634, m.p. 112-115)

Preliminary confirmation of the structure of this solid monomer was

obtained by IR analysis.

B. Development of New Initiator/Accelerator Systems

1. Amine Accelerators

Amines are crucially important to the hardening of dental

resins since vn situ polymerization requires chemical means rather than

thermal to generate free radicals from the peroxide initiator. Since

amines can be a source of discoloration, of toxic response and can

through the manner in which they influence the rate of free radical

formation affect the molecular weight and molecular weight distribution

4
of the polymeric matrix, it is very important to develop information

that can yield efficient, biocompatible and non-color inducing amines.

a. Stucture-Property Studies Employing SI ower Acti ng

Amine Types Including Surface Active or AdhesiveGenerating Amines

The critical properties (e.g. reactivity, color

stability, biocompatibility, etc.) of tertiary aromatic amine polymerization accelerators are governed by aromatic ring substituents as well

as substituents on the amine nitrogen. We have studied the effects of

such substituents by examining setting times (Gilmore needle test) and

diametral tensile strengths (DTS) of composites prepared from experimental powder/liquid (P/L) formulations consisting of silanized glass

filler coated with 1% BP and the liquid resin system B I S-GMA (7)/

TEGDMA (3), containing the amine accelerator.

From the structure-property considerations , the

commercially available tertiary aromatic amines, 4-N ,N-dimethyl aminobenzoic acid (4-DMAB) and its ethyl ester (4-EDMAB) would be expected

to be slow-acting accelerators and have enhanced oxidative and color

stability due to the electron withdrawal character of their respective

para substituents. Both 4-DMAB and 4-EDMAB, by analogy with their

respective parent compounds, 4-aminobenzoic acid (a Vitamin B, anticanitic and sunscreen agent) and ethyl -4-aminobenzoate (the local

anesthetic, Benzocaine), should have excellent biocompatibilities.

With relatively slow-polymerizing monomers such

as methyl methacrylate, the polymerization proceeds much slower by many

hours both with 4-DMAB and 4-EDMAB than with a fast-acting amine accelerator such as N,N-dimethyl -p-toluidine (DMPT). However with relatively

5
fast polymerizing monomer systems, such as BIS-GMA (7)/TEGDMA (3),

clinically acceptable setting times are obtainable with these slowacting amine accelerators (Tables 2 and 3), using the usual powder/liquid

formulation technique. In addition, the mechanical properties of these

composites, as evidenced by their DT5 values, are also quite acceptable

(minimum DTS = 34 MPa), comparable to those obtained with the usual

fast-acting amine accelerators . A manuscript entitled "Slow-Acting

Amine Polymerization Accelerators . I. Para-Dimethylaminobenzoic Acid and

its Ethyl Ester" has been accepted for publication in the Journal of

Dental Research.

. A parallel study of the accelerative behavior of the

corresponding meta isomeric amines, 3-N,N-dimethylaminobenzoic acid (3-

DMAB) and its ethyl ester (3-EDMAB) was initiated. The commerically

unavailable 3-EDMAB was synthesized from 3-DMAB by the method indicated.

CH

3

<n>-C-0H+CH

3

CH

2

I

0

3-DMAB

k

2 co

DMSO

CH

A

3-EDMAB

-C-0CH 9 CH 9

f? 2 3

0

The product, a pale yellow liquid, was at least 98% pure by gas-liquid

chromatographic analysis. Preliminary structural confirmation was

obtained by infrared analysis. The setting times and diametral tensile

strengths of composites prepared with 3-DMAB and 3-EDMAB over a wide

concentration range are summarized in Tables 4 and 5.

The initial appearances of composites prepared with

3-DMAB and 3-EDMAB were excellent. On storage in the dark at 37°C in a

100% relative humidity bath, the 3-EDMAB composi tes • retained their

6
Table 2

Effect of 4-DMAB Concentration on the Setting Time and

Diametral Tensile Strength of an Experimental Composite*

With No Added BHT

4-DMAB Setting Diametral Tensile Strength

Concentration Time ± Std. Dev. in MPa

Wt% mMolal (min) (No. of specimens)

0.10 6.0 9.0 44.7 + 2.6 (5)

0.165 10.0 6.0 46.9 + 3.0 (5)

0.20 12.1 6 .

5

48.8 + 2.5 (5)

0.25 15.2 5.0 50.5 + 2.0 (9)

0.28 17.0 5.0 48.0 + 1.5 (6)

0.30 18.2 5.0 47.9 + 5.3 (ID

0.33 20.0 5.5 50.8 + 1.6 (4)

0.40 24.2 5.5 49.9 + 3.5 (12)

0.45 27.3 4.0 51 .4 + 2.9 (ID

*Powder/l iquid formulations employing powder/liquid ratio of 3. Powder

is silanized glass filler and coated with 1% BP. Liquids are monomer

mixtures consisting of 7 parts BIS-GMA and 3 parts TEGDMA containing the

indicated concentrations of 4-DMAB but no added BHT.

7
Table 3

Effect of 4-EDMAB Concentration on the Setting Time and

Diametral Tensile Strength of an Experimental Composite

Material* With No Added BHT

4-EDMAB Setting Diametral Tensile Strength

Concentration Time ± Std. Dev. in MPa

Wt% mMolal (min) (No. of specimens)

0.20 10.4 11.0 44.3 + 1.6 (5)

0.26 13.5 8.0 50.6 ± 1.0 (3)

0.30 15.6 8.0 51.2 ± 2.2 (5)

0.40 20.7 7.5 47.7 ± 2.6 (7)

0.50 25.9 6.0 54.2 ± 1.1 (3)

0.60 31.1 5.5 50.9 4

* 1.4 (4)

0.70 36.3 5.5 54.9 + 1.5 (4)

0.80 41.4 5.5 51.7 + 1.9 (5)

0.90 46.6 5.0 52.0 ± 1 .5 (4)

1.00 51.8 4.5 46.3 ± 3.1 (12)

1 .10 57.0 4.0 49.9 ± 2.4 (6)

1 .30 67.4 4.5 53.8 ± 2.3 (7)

* Same as in Table 1 except for 4-EDMAB

8
Table 4

Effect of 3-DMAB Concentration on the Setting Time

And Diametral Tensile Strength of an Experimental Composite*

With No Added BHT

3- DMAB Setting Diametral Tensile Strength

Concentration Time + Std. Dev. in MPa

Wt.% mMolal (Min.

)

(No. of Specimens

)

0.12 7.3 4.5 43.1 + 1.2 (7)

0.165 10.0 3.5 48.5 + 1.9 (5)

0.20 12.1 3.0 50.2 + 2.5 (6)

0.25 15.2 2.5 51 .5 + 3.8 (6)

0.28 17.0 2.5 49.0 + 4.2 (8)

0.33 20.0 2.0 52.9 + 2.6 (4)

0.40 24.2 2.5 49.4 + 2.6 (8)

0.50 30.3 2.0 56.8 + 4.9 (4)

0.60 36.4 2.0 50.6 + 4.2 (12)

0.70 42.4 1.5 56.3 + 4.0 (5)

* Same as in Table 2 except for 3-DMAB

9
Table 5

Effect of 3-EDMAB Concentration on the Setting Time and

Diametral Tensile Strength of an Experimental

Composite* with no Added BHT

i

3-EDMAB Setting Diametral Tensile Strength

Concentration Time ± Std. Dev. in MPa

Wt% mMolal (min) (No. of specimens)

0.10 5.2 6.0 46.1 + 3.3 (8)

0.20 10.4 5.0 48.9 + 3.2 (ID

0.25 13.0 4.0 52.2 + 2.4 (6)

0.30 15.6 3.25 52.1 + 1.9 (6)

0.40 20.7 3.75 48.2 + 3.8 (6)

0.50 25.9 3.5 51.3 + 3.4 (7)

0.60 31.1 3.0 53.1 + 2.0 (7)

0.70 36.3 3.0 51.1 + 2.6 (6)

0.80 41.4 2.75 53.8 + 2.9 (5)

0.90 46.6 2.5 52.4 + 3.0 (6)

1.0 51.8 2.75 52.6 + 2.9 (6)

1.4 72.5 2.0 51.6 + 3.8 (10)

2.0 103.6 2.0 51.8 + 2.8 (5)

* Same as in Table 2 except for 3-EDMAB

10
initial appearance almost as well as those prepared with 4-EDMAB which

is excellent from this standpoint.

Although classified as slow-acting amine accelerators,

an examination of the setting time data of Tables 2-5 reveals significant

differences in reactivity between 4-DMAB, 4-EDMAB, 3-DMAB and 3-EDMAB.

Of these less reactive polymerization accelerators, 4-EDMAB is the slowest

promotor while the most reactive is 3-DMAB. The order of decreasing

accelerative reactivity appears to be 3-DMAB > 3-EDMAB > 4-DMAB > 4-EDMAB.

This is in accord with the relative electron-withdrawing character of

the aryl substituents -(^H and -CO2C2H5 and their ring position; that

is, the reactivity data correlate well with the accepted a+ values.

Within experimental error, average diametral strengths of composites prepared using these amines were not significantly different, although the

fastest of these accelerators, 3-DMAB, did give some of the highest individual DTS values (^60 MPa).

These relatively less reactive accelerators may have

several advantages over the commonly used fast-acting accelerators:

1) there is less need for the use of inhibitors or retarders to

control working and setting times,

2) they permit a wide amine concentration range to be studied with

dental resin systems which are usually fast polymerizing in nature.

This may prove helpful in obtaining a better understanding of the acyl

peroxide/amine initiator system and may permit the determination of the

extent of polymerization occuring in thermosetting monomers by such

techniques as differential scanning calorimetry.

11
3) The use of surface-active accelerators such as 4-DMAB and 3-

DMAB may improve the adhesiveness of dental restorative and sealant

materials to apatitic tissue.

4) The relatively superior retention of the excellent initial

appearance on storage at 37°C in* the dark of composites prepared with 4-

EDMAB and 3-EDMAB compared to the similar composites prepared with fastacting amine accelerators may have implications for improving the esthetics

of these dental materials by the use of less electron-rich accelerators.

b. Development of Fast-Acting, Biocompatible Amine

Accelerators

This research was undertaken to synthesize color

stable amines which are more reactive accelerators than those commercially available, and to evaluate those accelerators which can be expected

to be more biocompatible and less toxic than tertiary amines presently

used. This year (1) the synthesis and characterization of structurally

related homologues and derivatives of 4-N,N-dimethylaminophenyl acetic

acid (DMAPAA) I, and N ,N-dial kylaminophenethanol , II, was completed.

R

2

N ^^(CH

2^n

C00R ' and R

2 NC3

CH

2 CH20H

I II

(2) Correlation of the structure of resulting acids, esters and alcohols

of varying chain length and N-alkyl substitution (where R = CH^ ,

C

2 H5

;

R' = H,CH

3

,C

2 H5 and n = 1 or 2) with their reactivity in the peroxideinitiated polymerization of composites was determined, and (3) presently

used accelerators were compared with these compounds with regard to

their effect on such properties of the cured composite as mechanical

strength, color stability and water sorption.

12
Infrared, NMR, gas chromatographic and elemental

analysis were used to establish the structure and purity of previously

synthesized 4-N,N-diethylaminophenethanol , 4-N,N-diethylaminophenylacetic acid-ethyl ester and 4-N,N-dimethylaminophenylpropionic acid.

A number of unsuccessful attempts were made to

synthesize 4-N,N-diethylaminophenylacetic acid (DEAPAA) by basic hydrolysis of the ethyl ester. Acid hydrolysis of this compound yielded

the desired product.

During this reporting period the evaluation of the

amines previously synthesized [1,2] as accelerators in the benzoyl peroxide initiated cure of dental composite formulations was completed.

The 4-N,N-diethylaminophenylacetic acid (DEAPAA) was found to be the

most reactive amine ever prepared. As can be seen from Table 6, concentrations as low as 3 mmolal of this accelerator (compared to 15

mmolal concentration for the commonly used dimethyl-p-toluidine, DMPT)

in the monomeric liquid of standard formulations yield a cure in 4.5

min. Without BHT inhibitor this curing time is reduced to 1.5 min, a

time which is too short for clinical practice. Too rapid a polymerization can be avoided by increasing the BHT inhibitor concentration in

the liquid to 0.3 or 0.4%, which decreases the strength of the composite

only slightly.

The mechanical characteristics of composites containing the amines under study were highly satisfactory. Thus, the

cured composites had physical properties equal or better than those

obtained for commercial composites. For all formulations the tensile

strength considerably exceeded the minimum requirement of 34 MPa of the

Specification for Direct Filling Resins. Optimum properties (tensile

13
Table 6

Properties of Composites Cured With 4,-N ,N-01ethylam1nophenyl

Acetic-Acid as Accelerator

Powder: Corning Glass 7724, sllanized and coated with 12 benzoyl peroxide

Liquid: 72.42 BIS-GMA, 27.62 1 ,6-hexamethylene, glycol dimethacrylate

and 0.22 BHT

Powder-liquid ratio: 3/1

nMolal Cone.

In Liquid

Setting Time

Min.

Tensile Compressive

Strength, MPa Strength, MPa

h

2 o Sorption

mq/cm2

3 4.5 36(2)’

f .

3* 1.5 49(3) • m

5 2.5 44(1) 245 (7

)

f

0.56(.03)

7 2.5 45(1) 275(3) -

7

b 2.5 44(5) m - 9 2.0 46(4) 275(10) -

11 2.0 46(4) 284(6) - •13 2.0 49(4) 272(6)

15 1.5 52(3) 268(9) - 17 1.5 54(4) 303(9) 0.58( .02)

\f 2 52(2) 280(6) -

17

d

2 50(3) 294(6) - 17

b 1.25-1.5 55(2) - 0 . 57 (

.

02 ) 19

e 1.5 54(2) 292(15) -

19 1.25-1.5 49(3) - •

For comparison identical composite formulations polymerized with 4,-N,N-dimethyl

jHtoluldine (DMPT) have the following properties>

15 4.5 45.9(4) 276(22) .60( .05)

17 3 43.0(3) 246(10) •58( .00)

19 4.5 47.6(3) 246(17) .56( .03)

* Prepared without inhibitor e Prepared with 0 .25* BHT

b 0.42 ultraviolet absorber added f .Values in parenthes1s give

c Prepared with 0.32 BHT standard deviation

d Prepared with 0.42 BHT

14
strength 55 MPa, compressive strength 303 MPa) were found for formulations containing 17 mmole concentration of the accelerator. On

lowering the BHT inhibitor concentrations in these formulations

even higher mechanical strength values were obtained. Substituting

1 ,10-decamethylene glycol dimethactylate for the 1 ,6-hexamethylene homologue as diluent did not change the characteristics of the composite

appreciably

.

The much lower concentration of DEAPAA required to

give an adequate cure for the composite ( i. e., about one-half the concentration of accelerators such as DMPT) imparted a nearly colorless or

very light shade to the resin which is much less than is obtained

with commercial products. Incorporation of an ultraviolet stabilizer

in 0.4% concentration did not change the physical properties of the composite. The cured specimens containing this stabilizer showed no visible

change after being subjected to the color stability test of the ADA

Specification No. 27.

4-N,N-dimethyl ami nophenyl acetic acid is absorbed on

hydroxyapatite and appears to improve bonding of reactive adhesive formulations to dentin. Thus an attempt has also been made to synthesize the

diethylaminophenethanol monosuccinate. This compound should be a highly

reactive accelerator containing free acid groups which may interact with

dentin. Equimolar concentrations of dimethyl ami nophenethanol and succinic

anhydride were heated to 68°C for 1 1/2 hours. After separation of the

reaction mixture and recrystallization from ethanol-water a tan-colored

solid MP 85-86°C was obtained which proved a rapid accelerator for the

15
1

3

polymerization of composites. C NMR analysis indicates, however, that

this compound is the diester probably formed through the stabilized

intermediate (I).

ch

2

oh

-Ol-P

C

2 H 5\ + y

C

2 H

5

N

/\

H

2

C - CH

2

C

2 H 5\ /

C

2

H

N

5

Further efforts will be made to synthesize the monosuccinate by employing

even milder reaction conditions.

c. Amines as Photoinitiators of Polymerization

The 4-N,N-dimethyl-and 4-N,N-diethylaminocinnamic acids

previously synthesized act as photo-initiators for the polymerization of

resins in sunlight or under UV radiation. To evaluate their possible

usefulness as initiators for resins cured by visible light, typical BIS-GMA

formulations containing these compounds were prepared. However, the low

solubility of the cinnamic acids in BIS-GMA and diluent allowed too little

amine (< 0.2%) to be incorporated for effective polymerization under a sunlamp.

To obtain a more soluble initiator the ethyl ester of

diethylaminocinnamic acid (DEACA-EE) was synthesized. Monoethylmalonate

was prepared by hydrolysis of diethylmalonate according to Breslow [3].

The DEACA-EE was prepared from p-di ethyl ami nobenzaldehyde and the monoethylmalonate by the procedure of Bolat [4]. The product melted at 47-48. 5°C

and had a A max

at 372-374 ym. A very yellow one-percent solution of the

16
product in BIS-GMA and diluent retained its prohibitive color on being

cured by sun lamp irradiation for three minutes. Although the shade of

the resin was improved by reducing the photoinitiator concentration, the

time to cure was increased excessively and this photoinitiator does not

offer promise for dental application.

d. Amines for Improved Color of Denture Base on Repair

Resins

For some clinical applications of denture base or

repair resins .colorless or nearly colorless shades are required. A

study was initiated to determine the suitability of the di alkyl ami noacetic acids or phenethanols previously synthesized in this laboratory

as accelerators for room temperature-curing denture resins. Mixes

using commercial powder without or with benzoyl peroxide (3%) and

different concentrations of the tertiary amines in methyl methacrylate

had adequate working times. The cured resin showed no trace of discoloration when dimethylaminophenethanol (DMAPE) was used as accelerator

and exposure to a sun lamp produced only a light yellow shade. On

addition of 0.4% Tinuvin P (an ultraviolet stabilizer) to the formulation the color stability of all specimens was improved greatly and only

a very slight, hardly perceptible, discoloration of the irradiated specimen containing 0.5% DMAPE was observed. The shade and color stability

of the DMAPE containing materials appeared slightly better than those

polymerized with N,N-dimethyl-£-tert-butylanil ine which previously was

considered the least color-producing accelerator.

Measurements to compare the physical properties of

resins containing these accelerators are being made. Water sorption of

17
2 materials employing the various amines ranged from 0.4 to 0.8 mg/cm

which is within the requirements of the ADA Specification No. 12 for

Denture Base Resins.

2. Non-Amine Accelerators

a. Ascorbic Acid Systems

Previously [2] we had shown that minute amounts of

copper compounds either dissolved in the monomer system from the start

or added in an apparently insoluble form (copper mordanted hydroxyapati te

powder) could significantly decrease the cure time of peroxide-ascorbic

acid type initiator systems. Using an experimental glass containing

minute amounts of copper salts, we have preliminary evidence that copper

even in this state can have catalytic properties on the free radical

initiation reaction provided an ascorbic type reducing agent is employed.

No additional acceleration is noted in the setting time unless ascorbic

acid or palmitate is part of the initiator system along with the copper

containing glass. Table 7 compares the effect of this catalytic glass

on the setting time of several composite formulations. The composites

exhibited no visible coloration and had excellent color stability.

Analogous results were obtained with a cumene hydroperoxide-ascorbic

acid type initiator system.

The copper containing glass was then silanized with

3-methacryloxypropyl trimethoxysilane using the cyclohexane propylamine

method described elsewhere in this report (Section I.D.). In Table 8

are given the results showing the effect of this silanized copper glass

on the setting time and the DTS values of composites using only t-butylperoxymaleic acid as the initiator. Blending 10% of silanized coppercontaining glass with copper-free silanized glass coated with 1 % T-BPM

18
TABLE 7

COMPARATIVE SETTING TIMES

3 0F EXPERIMENTAL ^COMPOSITES

6 USING ASCORBIC ACID TYPE INITIATOR SYSTEMS WITH AND WITHOUT CATALYTIC GLASS

Formulation Liquid Monomer Powder P/l Settinq Time

1 BIS-GMA(7)

TEGDMA(3)

0.06? Tyrosine

1.0? BP 1.3? TBPMC

0.3? AP

d on silanized

gl ass

3 7.0

2 Same as (j) 0.3? AP

d on silanized

glass + 11? Cu glass

3 4.0

3 BIS- GMA ( 7

)

TEG0MA(3)

0.06? Tyrosine

1.0? BP 1.6? TBPB

e

0.3? AP<*

. on silanized

glass

3 4.0

4 Same as Q) Same as (?) 3 2.5

5 Same as (j} Only Cu glass 3 No Set

6 Same as (3) Same as (5) 3 No Set

a G11more needle test at 37°C.

6 Powder/l iqui d formulations used throughout.

C TBPM = t-butylperoxymaleic acid.

d AP * Ascorbyl palmitate.

e TBPB = t-butyl perbenzoate

.

19
0) "O •*— C A

«3

O

Q.

31 •© C 4->

CO

01

0) CO

JO

L.2LX

CJ

fc. o

Q. £

a. <-> o w u c

•o

L « *i M to

<e </» c i if > O

OJ 0) O Cl CO

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Ha> c © LO o to c

«*"- & CO CO to

«L>

0) to

co

CMHo

CO

CO

CM

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on

in o

CO

•H CMC*3* CO

to *9

ui « * M o0) £ N

Cl •*- CO c

h- «

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a. <o £ ^3 * < CO

NJ 01 01

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**- 13 »« «T3 r- C WiO O O SJ SC'" 3 <o § ^ i/> + CJ 40 <o

CLU ?*» < 0> •*- i- "3 wM < O L-> OJ u 4> r- fO L ^ a. 01 to 01 +J <T5 -C 13 •c • « *— E -*-> a. CD £ o E S, a; <u l O >=* £y a> X £ L. to CD tO gs £ E © — a *+ UJ • (& O (a

CL L. “3

m

h o to CD to p0) 01 Q. U O

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cr c ^0) u

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i- 4-> O 3 U JO A I < hC «*-> « •*• JT 4*

«*->

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a; cl

!lH CZSIf- <a.Q< CO ZD 1I

flI

20
halved the setting time obtained with similar formulations using the

same silanized peroxidized glass filler but without the copper glass.

The effect of this catalytic glass on the diametral tensile strength of

composites was less pronounced, although formulation D did show approxk

: imately a 10% increase over that of C (without Cu glass). All the composite specimens exhibited excellent initial color and color stability

(no change on exposure to ultraviolet irradiation for 24 hours and no

change on storage at 37°C in 100% constant humidity chamber for 2 weeks).

C. Analysis for Degree of Polymerization of Dental Resins

Infrared spectroscopy has been employed by several workers to

examine the extent of polymerization of dental monomers. In the case of

dental composite materials especially this technique can be hampered by

the difficulties of sample preparation and by a strong interference in

the critical vinyl absorption region by the siliceous filler component.

We have initiated an investigation into alternate analytical techniques

which may alleviate some of these problems. These techniques are: (1)

1

3

differential scanning calorimetry (DSC), (2) C solid state NMR spectroscopy and (3) laser Raman spectroscopy. In addition, we are conducting the traditional infrared spectroscopic comparative analyses of

uncured vs cured dental resin systems by means of a recently acquired

Fourier transform infrared (FTIR) instrument.

1. Differential Scanning Calorimetry (DSC)

DSC has been used to assess the extent of polymerization

of both monofunctional and multifunctional vinyl monomers. The technique measures the thermal change, i.e. heat of polymerization, that

accompanies the conversion of vinyl groups to saturate

21
carbon to carbon bonds by self addition. The area under the recorded

exothermic peak is proportional to the heat of polymerization and therefore, to the number of such vinyl groups reacted.

In this preliminary study DSC was used to ascertain the

degree of polymerization or conversion, C, of an experimental monomer

system consisting of 7 parts by weight of BIS-GMA and 3 parts by weight

of triethylene glycol dimethacryl ate (TEGDMA). The molar heat of

polymerization (AHp) of lauryl methacrylate as determined by DSC (13.6

Kcal/mole) was used as the basis for calculating the conversion of vinyl

groups to polymer. Thermally activated polymerizations of BIS-GMA (7)/

TEGDMA (3) were conducted using benzoyl peroxide as the initiator. Both the

concentration of BP and heating rate employed in the DSC experiment

affected the extent of polymerization as shown in Table 9 below:

Table 9. DSC Examination of BIS-GMA(7)/TEGDMA(3) Polymerization

BP Concentration Heating Rate/Peak Exotherm % Vinyl Reaction

0.4 2. 5°C/min; 90°C

1.0

2.2

0.4

1.0

1 0°C/mi n ; 110°C

37

51

61

73

59

Several chemically activated polymerizations of the same monomer system

yielded the results shown in Table 10.

22
Table 10. DSC Examination of Chemically Activated Polymerization of

BIS-GMA (7)/ TEGDMA (3)

Accelerator, Cone,

(wt %)

BP Cone,

(wt %)

Peak Exotherm

(°C)

% Vinyl Reacti

1) DMBA, 0.23 0.39 41 48

2) a) DHPPT, 0.42 1.0 57 56

b) " 2.2 49 48

3) a) 4-DMAB, 0.5 1.0 58 46

b) 78% Glass paste 78% glass

paste 82 61

4) 4-EDMAB, 1.3 2.2 52 53

5) AP, 0.56 1.0 40 51

From the above results it is evident that even at a high peak exotherm

(e.g. paste/paste systems) approximately 40% of the vinyl groups have

not reacted in the chemically activated system. Experimental difficulties

are encountered when fast acting amine polymerization accelerators, such

as p-t-butyl-N,N-dimethylaniline (DMBA) are employed. However, these

fast promoters may be studied if the concentration of BP and amine are

relatively low or if additional quantities of inhibitor are added to the

monomer system. The use of a slower polymerizing monomer system would

also permit their use in this type of DSC study. On the other hand, the

slower-acting amine accelerators such as 4-dimethyl ami nobenzoic acid (4-

DMAB) and its ethyl ester (4-EDMAB) as well as the relatively slow nonamine accelerator, ascorbyl palmitate, are well suited for this type of

DSC experiment. The moderately fast amine promoter, N, N-bis (2-hydroxypropyl )-p-toluidine (DHPPT) is also amenable to this type of study.

The low melting solid analog of BIS-GMA,

BIS-EDMA (the dimethacryloxyethoxy derivative of bisphenol A) with 1%

BP had only about 40% conversion of vinyl groups on thermal polymerization

23
(peak exotherm = 72°C), this result supports the expected relatively

immobile nature of many pendant vinyl groups in the initial network

polymer resulting from the polymerization of a rather inflexible difunctional monomer. BIS-GMA would be expected to yield similar results.

An obvious potential application of the DSC method would be to evaluate

diluent monomers that can maximize the conversion of these vinyl groups.

In addition, DSC should be useful in studying the efficacy of different

initiator systems and inhibitors.

2. Solid State

^ 3

C NMR SpectroscoDy

This technique is based on the change in the chemical

shift of the carbonyl carbon of methacrylate monomers on their conversion

to polymer. CH 9

I J

n CH 9 =C —

d

I *c=o

I0

IR

An example of the potential of this method is shown below for thermally

and photochemically polymerized BIS-GMA. Quantitative analysis appears

feasible and the presence of inorganic filler as occurs in the composite

should only have a diluting effect which can be dealt with. (See Fig. 1)

3. Laser Raman Spectroscopy

The intense vinyl absorption plus a much less intense

carboxyl absorption compared to that characteristic of IR spectroscopy

offer potential advantages in terms of sensitivity for the analytical

CH-,

I 3

ch

2 -c

*C=0

I 0

I R

24
determination of degree of polymerization of dental resins. Also, sample

geometry is-less restrictive in laser Raman spectroscopy than it is in

transmission IR spectroscopy.

4. Fourier Transform Infrared Spectroscopy

As compared to previously available IR instrumentation,

the recently acquired FTIR instrument (Nicolet Model 7199) offers the

potential for optimizing the sensitivity of IR spectroscopic analysis

and thus to yield more quantitative data on the percent conversion of

vinyl groups. Vinyl absorption is distinctive and uncomplicated by the

usually overwhelming absorption due to the filler content of a composite.

D. Resin/Filler Coupling Improvement for Composites

The service life of composites is assumed to be strongly dependent on the bonding between the resin matrix and reinforcing filler. This

bond is greatly improved by addition of a coupling agent which is usually

applied at the surface of the filler.

The objective of this study was to determine 1) the nature and

extent of interaction with the filler and resin achieved by the silane

coupling agent, 2) what mode of application of the coupling agent produces

optimum bond formation, 3) the extent of debonding that may occur on storage

in a simulated oral environment and, 4) the improvement in physical or wear

properties of composites which may result from optimizing interfacial bonding.

Colloidal silica wafers were molded and subjected to various

silanizing treatments for 2 hours. Formation of chemical bonding between

the silica and the silane was determined from the disappearance of the free

hydroxyl band of silica at 3740 cm"^ and the siloxane peak of the bulk

25
silica at 1850 cm^ as internal infrared absorption standard. The effect

of the solvent used for the 3-methacryloxypropyl trimethoxysilane (MPTS)

as well as the effect of the addition of 2% n-propylamine to the reaction

mixture are given in Table 11. Treatment with silane dissolved in

various solvents yielded silica surfaces which generally had a reduced

free hydroxyl absorption band. A high percentage of bond formation

occured in 50% ethanol. Initial reduction of the hydroxyl absorption

was also large when dimethyl sulfoxide or dimethyl formamide were used as

solvents. However, on standing of the sepcimens in air this value

increased again, probably due to the hydrolysis of an unstable complex

of silica with these solvents which was also observed from spectroscopic

data when silica was exposed to the respective solvents. Little or no

bond formation took place on treating the silica with silane dissolved

in acetone (in which the silane may decompose on standing) or toluene.

Addition of n-propylamine greatly increases the coupling effectiveness

of the silane studied. Complete elimination of the free hydroxyl band

occurs when acetone, n-pentane or cyclohexane are used as solvents in

the presence of n-propylamine.

The stability of the bonding was studied by aging specimens at

68°C for 280 hours. Most water-stored specimens showed a considerable

increase in the free hydroxyl present indicating a hydrolytic fission,

i.e. a reversal of the silanization (Table 12). However, no reappearance

of the hydroxyl band was observed for silica modified with silane dissolved

in cyclohexane in the presence of n-propylamine. Thus, under these

conditions a stable bond is formed.

The silanizing reaction is also influenced greatly by the type

of amine used as catalyst. Optimum bonding was obtained with n-propyl

26
TABLE 11

EFFECT OF SOLVENT AND n-PROPYL AMINE ON CHEMICAL

BONDING OF SILANES TO SILICA SURFACES

Silane: 2 vol % solution of A-174 (3-methacryloxypropyltrlmethoxysilane)

Reaction Time: 2 hours at room temperature.

Bonding, %

a

Silane Solvent No Catalyst 2% n-Propyl Amine

0.05 Vol % Acetic Acid (pH = 3.6)

c 31.5 b

0.05 Vol % Acetic Acid (pH = 3.6)

d 32 b

20* Ethanol -80% H

2 0 (pH = 3.6) 2 b

50% Ethanol-50% H

2 0 (pH = 3.6) 53 b

95% Ethanol 13 70

50% Acetone-50% H

2 0 31 b

90% Acetone- 10% H

2 0 23 100

Acetone

e 0 100

Dimethyl sul foxlde 89 (48.5)

f 41.5

Dimethyl formamide 48.5 78.4

n-Pentane 33.5 100

n-Hexane 26.5 85

Cyclohexane 26.5 100

Toluene 4 70

Calculated from relative intensity ratio of infrared absorption peak at 3740 cm

-

' (free OH band) and around 1850 cm

-

' (siloxane linkage in the bulk

of the silica). Samples were washed with acetone for 15 minutes and airdried prior to infrared measurements. Solution became cloudy on addition of n-propyl amine.

c S11ane was hydrolyzed in 0.05 vol % acetic acid for 7 days prior to reaction

with silica.

d S11ane was hydrolyzed in 0.05 vol % acetic acid for 1 hr. prior to reaction

with silica.

e Solution decomposes on standing.

^Numbers in parentheses indicate change in absorption at 3740 cm"

1 of wafer

after 1 hour.

27
TABLE 12

STABILITY OF SILICA-SILANE BOND

After silane treatment silica wafer was stored In water at 68°C for 280 hours.

Bondi nq

Silane Solvent

% n- Propyl Amine

In Solvent Before Storage After HjO Storage

95% Ethanol - 9 0

95% Ethanol 2 70 14.5

50% Ethanol (pH = 3.6) - 12 0

20% Ethanol (pH = 3.6) - • 2 0

Acetone 2 100 26.5

90% Acetone-1 0% H

2 0 - 23 20

90% Acetone-1 0% H

2 0 2 100 41.1

Dimethyl sul foxlde - 75

b

0

Dimethyl sulfoxide 2 100

b 26.5

Dimethyl formamide - 17.

7

b 17.5

Pentane - 33.5 33.5

Pentane 2 100 71.5

n-Hexane - 33 9

n-Hexane 2 85 34

Cyclohexane 26.5 0

Cyclohexane 2 100 100

Toluene - 4 0

Toluene 2 70 38

Calculated from relative

1850 cm-'. intensity ratio of IR peaks at 3740 cm and

^Bonding decreased on standing.

28
or diethylamine (Table 13). Tertiary aliphatic amines are less effective.

The aromatic N,N-dimethyl-p-toluidine and a heterocyclic amine (pyridine)

characterized by much lower basicities, were less effective catalysts.

Improvement in the strength of a composite prepared from colloidal

silica si 1 an i zed in the presence of n- propyl amine (PA) is shown in Table

14. This composite had a tensile strength of 23.3 MPa as compared to 4.7

MPa for a composite prepared from pastes containing SiC^ silanized without

PA. A concentration of 2% PA is most effective for silanizing glass powder.

The resulting composites have excellent mechanical properties (tensile

strength 51.6 MPa, compressive strength 278 MPa) which is respectively

10% and 26% higher than is obtained with glass silanized in the absence

of PA (Table 15). The tensile and compressive strengths of composites

containing the glass treated with the coupling agent and amine were not

reduced by storage in 60°C water for 3 days or on thermocycling in 5° and

55°C water for 6 days. Thus silanization of the substrate in cyclohexane

containing 2% PA yields materials with an increased strength which is

maintained on storage.

E. Peroxy Esters and Hydroperoxides as More Storage Stable

Initiators for Composite Resins

A deficiency of commercial dental composites formulations is

their limited storage stability. The constituents, especially the

initiator-containing pastes, often harden prior to use. Alternati vely

,

the curing time of the mixed pastes either becomes too long for clinical

applications or mixes do not harden at all. The main cause for this

storage instability is the benzoyl peroxide component. Replacement of

this initiator by other peroxides (e.g. hydroperoxides or peroxy esters)

with longer thermal half-life decomposition values appeared to be desirable.

29
TABLE 13

EFFECT OF AMINES IN THE SILANIZATION OF SILICA SURFACES

Silanizing solution: 2 vol

Reaction time: 2 hours at

s11ane*% *and 2 vol % amine

room temperature.

In cyclohexane

Amine

Base Ionization

Constant Bondi nq,

%'

n- Propyl amine 3.8 x 10"4 100

Diethyl amine 9.5 x 10" 4 100

Triethyl amine 5.5 x 10' 4

49.5

Tri -ii-butyl amine 8.52 x 10" 5 49.3

N,N-Dimethyl -£-toluidine 1.1 x 10"9

20.5

Pyridine 2.3 x 10" 90

Calculated from relative intensity ratio of IR peaks at 3740 cm

-1 and

1850 cm"

1

. * 3-methacryloxypropyltrimethoxy silane

30
Table 14

EFFECT OF SILANE (A-174) TREATMENT ON HARDENING TIMES

AND

ON THE TENSILE STRENGTH OF A PASTE-PASTE COMPOSITE

Composition of Composite

Initiator paste

% by weight

Catalyst paste

% by weight

BIS-GMA 53.62 53.88

TEGDMA 22.99 23.11

BHT 0.154 0.154

Benzoyl peroxide 0.766 - -

Dimethyl -p-toluidine — 0.386

Filler 22.47 22.47

Equal weights of initiator and catalyst paste were used.

Properties

Cabosil Filler Treatment

1% (vol) silane

in CgH^*

1% (vol ) silane + 1%

n-propyl amine in C6

H12*

Hardening time at 23°C,

in minutes 5 3

Tensile Strength, MPa 4.7 ± 0.7 23.2 ± 0.9

* Cyclohexane

31
Table

15

CO

Q£LU1 __1 —i Ll. LU go (—

go i—i <c go

_J o o Cls:

Ll. o O o

1— _J z < LU 1— s z

H— LU < O LU

oe: Ll. i— O

CO go

LU

i—i

4—1

M h~

1—4 cc z LU < CL _1 O 4—1 oc go D_

Ll. z O o 1—oLUU.

Ll. LU • ON

CD s-s r— c co CD +1 1 1 +i 1 1— •1“ ON to

rc E • r—

CD rtf LD CM SS >,

CM Cl • O o E

CL

X) | CM o LO e C s-s • • CO ON

CO CM r— to CM r— r—

+1 +1 +1 +i +i

CD CM to 00 to 00 r— E CO • • • r^. 00

•r— 3 ,

o CO CM CM

CD X> LO LO LO

XJ *1— Q-

•1“ 3 )< x r—•

CNJ o o r— E +-> z O) i CD to

CL CL CJ • CO 1 crS CO r—

r— r— E CO +1 1 1 +1 1 >1

•P— r— o -C • N +-> <0- LO CM e CD

CD E p—

-Q •r— i | <C z ID CM CM CO

-c: z • • • • <3- ^1* +j O LD r— CO CO r— r—

•r— • CO +i +1 +1 +i +i s co O CO ON CO

CXI E • • • 00

-a • O CO r^- CM CM

CD

a •r— +J +-> cO to CO O 3 N o •1— Q. E

•s CO CM o ON

*N r— \ • • • CM

CM •i— n— CM r— CM CM CM

I-'. SL CO

O +1 +i +1 +1 +1

Q ON ON r— r— CO • • • CM

to ca to r-. to CM CM

to •=3- CO ON

CO • CO '

r—

CD e ***>. E

4-> •1— CO <D CJ

•r— e c +-> E 0 E E E Sl to CO cO CD LO CD a> o o CO • • CD CL 2 -M LO .e 4-> 4-> CL o 1 o 4J s: C0 | 4-> lO CO F C/> ‘r— 3 c_> 2 LO ON 2 2 o a M 4-> E #» 0 E o <D CO CO •r— .E O ON CD O o N e E M CO 0 E E O 0 M— •1— CD o •r— +J o O e r— -D C* E E to r— GO CO to

CO • •r- CD <d •r—

a e r— LO E e E >4 CD E E o •r— 00 cr •r— +-> 00 •1— CJ > •P— •r—

•r- go ">—

•r— i— GO E •1TM

4-> r“ 3 to to to to to

•r— • • • • on CD

O >N >4 to E >N

LO 1- -O E E r— -E CO CO CD Z CO O CD •r— CD •r— •r— X) x: E X3 CL -o 3 X) +j CO Q- E 2 C7 2 •»j E CM CO to F CM CO O O •r— o CD CD o O Q_ _i CL GO 1 o I

32 6

days

cycling

5-55°C

249±13

282±10 -

288±13 2

HpO

sorption

mg/cm

.62±.02
It was the objective to determine the reactivity of more stable peroxides

with currently used amines, and the rapidly reacting amines synthesized

in our laboratory. More stable initiators investigated were t-butyl

peroxymaleic acid (TBPM), 2,5-dimethyl-2,5-bis (benzoyl peroxy ) hexane

(DMBPH) and cumene hydroperoxide (CHP). The TBPM proved to yield composite formulations with much lower setting times than those obtained

with DMBPH. Materials cured with CHP as initiator hardened but the

resulting composites were of undesirable shades. Results of setting

time tests indicated that composite formulations containing 4% TBPM and

from 1.5 to 3.0% DEAPAA required from 16 to 21 min to cure, those containing 2.5% dimethylamine or di ethyl ami nophenethanol , 6.5 and 7.5 min,

respectively. Faster curing times of 4, 4.5 and 2.5 min. were found when

2.5% dimethyl-p-toluidine (DMPT), 2.5% ami nophenethanol or 2.5% p-toluidine

were used as accelerators. However, the shades of the resulting composites

were not considered to be satisfactory for dental restoratives. The cure

and physical properties of the more promising TBPM-containing formulations

are given in table 16. Generally in the presence of primary or secondary

amines a fast set is obtained but the former yields resins with darker

shades whereas the latter amines give materials with poor strength, but

the cure is somewhat faster. With 3% TBPM and 2.5% DMPT, composites with

satisfactory strength are obtained (Table 16). Thus, all but the MPTcontaining formulations pass the requirements of ADA Specification No.

27, but had lower mechanical properties than similar compositions cured

with benzoyl peroxide.

The storage stability of the components of these composites

is, quite unexpectedly, not better than that of typical commercial composites.

33
TABLE 16

Properties of Composites Cured with t-Butyl peroxymaleic

Acid (TBPM) Initiator

Powder: Corning Glass 7724, silanized and coated with TBPM.

Liquid: 70% BIS-GMA - 30% 1 ,10-decamethylene glycol dimethacrylate.

2.5% amine and 0.1% BHT.

Powder-Liquid Ratio: 3 to 1

Setting

Time

(min)

Strength

Amine

Tensil

e

MPa

Compressi ve

4% TBPM Initiator

t- Butyl dimethyl ani 1 ine 7-7.5 38.5 t 2.9 210 ± 9

Methyl ester of p-tolylglycine 3-3.5 28.4 + 2.1 157 ± 4

N-Methyl-p-tol uidine (MPT) 4-4.5 28.4 * 2.2 162 ± 5 Dimethyl -p-toluidine (DMPT) 6.5-7 38.1 ± 3.6 209 ± 11

3% TBPM Initiator

2.5% DMPT 6 41 .8 + 2.2 223 + 10

2.3% DMPT + 0.2% MPT 5-5.6 41 .6 + 1.0 223 + 4

2.2% DMPT + 0.35% MPT 5-5.5 40.6 + 3.8 222 + 4

1.5% DMPT + 1% MPT 5 37.6 + 3.6 200 + 9

2.5% MPT 4-4.5 28.4 + 2.2 .162 + 6

34
From the larger thermal half-life decomposition time of TBPM versus

benzoyl peroxide one would expect a greater storage stability of the system

containing the former initiator. A composite formulation from a TBPM coated

glass powder mixed with room temperature-stored monomer showed a

25% increase in setting time after 48 hour storage of the powder at 60°C.

The higher percentage of TBPM on the glass surface (3% vs. 1% for benzoyl

peroxide) may be responsible for the increased deterioration of the initiator

This peroxy-ester may hydrolyze in air at elevated temperatures resulting

in the longer cure. Furthermore, the monomeric BIS-GMA/ diluent ingredients

of the resin gel within a few days when stored at 60°C, probably because of

the large concentration of amine (2.5% vs. about 0.25% for a benzoyl peroxide

initiated composition). These results indicate that peroxyesters are not

particularly suitable initiators to increase the storage life of composites.

F. Autocurable Polymer Blends as Routes to Improving Chemical and

Mechanical Properties of Denture Base and Other Dental Materials

The polymer blend approach is being pursued rigorously to improve

industrial plastics for specialty applications and may provide a route to

improving dental resins. Our interest specifically is in exploring this

approach as a means of achieving tougher but not significantly less strong

dental resin systems.

A copolymer (PVF

2

-TFE) consisting of 27% tetrafluoroethylene (TFE)

and 73% of vinylidene fluoride (VF

2

) was dissolved to the extent of 5%

by weight in methyl methacrylate (MMA) containing 0.5% dimethyl-p-toluidine

(DMPT). This liquid was mixed with 2 parts by weight of poly(methyl methacrylate) PMMA, containing 3% benzoyl peroxide. The blend cured well in 15

minutes at 37°C in a 100% relative humidity chamber and the diametral

35
tensile strength results (25 MPa) were comparable to the control (28 MPa).

At least at the 5% Pl^-TFE level this blend does not adversely affect

curing time or strength and its less brittle nature is a step in the desired

direction.

G: Status Report - The Desirability of Using Radiopaque Plastics

in Dentistry

Ideally any material used in the mouth or in the dental operatory

should be radiopaque. A motion by the House of Delegates of the American

Dental Asssociation to require that all dental plastics possess this property

resulted in the preparation of a status report. An extensive library

research including computerized search for foreign bodies in the human

body was conducted to determine the frequence of occurrence as well as

the severity of episodes of the ingestion and inhalation of plastics of

dental origin. Dates of accidents resulting from dental objects from 1972

to 1979 were obtained from the U. S. Consumer Products Safety Commission

and were evaluated* The tentative summary and conclusions of the report

were as follows:

(1) The widespread use of plastics in dental practice has increased the risk of ingestion, inhalation or of embedding of such materials

in the soft tissues. The frequency of such accidents is relatively small

compared to the number of plastic materials or appliances used. Nevertheless, the severity of such incidents may make it mandatory to rapidly locate,

diagnose and remove such foreign bodies. The need for immediate removal

and assurance of total retrieval of ingested, aspirated and embedded plastic

36
materials suggests that plastics of sufficient x-ray radiopacity be used,

or if necessary, be developed, wherever an intraoral application is anticipated.

(2) The following recommendations for specific types of dental

application were suggested:

a. Restorative Materials

Radiopaque composites with properties comparable to those

of translucent products are marketed commercially and are the materials of

choice for anterior restoratives. Adding a radiopacity requirement to

Specification No. 27 for Direct Filling Resins would encourage their usage.

b. Temporary Bridge and Crown Materials

Radiopacity for temporary bridge work and crowns is

highly desirable. Such material is available which appears to have adequate

physical and clinical properties. Whenever special factors point to the

possibility of loss of adhesion or fragmentation of the appliance a radiopaque material is indicated.

c. Denture Base Materials and Plastic Teeth

Radiopaque denture base materials and plastic teeth,

combining adequate physical, biocompatible and esthetic properties with

ease of processing and finishing similar to the acrylic plastics most

commonly used, are not available commercially. Porcelain teeth when

mechanically interlocked in heat-cured (composite) radiopaque denture

resin will be weakened or fractured. A satisfactory radiopaque resin

tooth has not been developed. To overcome present deficiencies further

studies to incorporate radiopaque glass fillers or novel techniques to

synthesize radiopaque resins should be explored. Even if the technical

difficulties of redesigning porcelain teeth or of manufacturing radiopaque

37
resin teeth could be overcome, the initial production and stocking of such

teeth would run into millions of dollars and would probably require several

years to accomplish. In the interim period the commercial availability

of a non-toxic radiopaque denture base formulated according to the existing

"state of the art" should be encouraged. The use of such a product is

indicated for patients with a high risk of accidental ingestion due to

neuromuscular, epileptic, asthmatic, mental or other health or occupational

problems, where the decreased danger of injury caused by the appliance far

outweighs its somewhat poorer physical and esthetic properties.

d. Impression Materials

The need for radiopacity in impression materials has

been clearly established. Inclusion of this requirement in existing American

Dental Association specifications may require some changes in formulation of

present materials. There may be delays in establishing a test procedure,

because of the difficulty in determining quantitatively the radiopacity of

materials and its relevancy to clinical practice. The advisability of adding

at an early date an ad interim semiquantitative requirement for radiopacity

of impression materials should be considered.

e. Development of Radiopaque Standards

Investigation to standardize techniques for the reproducible measurement of the radiopacity of dental materials should be encouraged. The primary goal of these investigations should be the development

of satisfactory standards that correlate with clinical needs.

H. Improving Dental Cements

Chelating agents such as eugenol react with zinc oxide to form

cementitious materials which, because of their excellent tissue tolerance.

38
have found many applications in dental practice. However, their mechanical

properties as well as their hydrolytic instability are factors limiting

their use as longer lived temporary restorations.

The initial objective of this study was to (1) synthesize 2-

methoxyphenol (guaicol) derivatives such as 2,5-dimethoxyphenol (DMP)

and esters of vanillic (4-hydroxy-3-methoxybenzoic acid) or its isomers

which are liquids at room temperature, (2) study their reaction with

metal oxides and (3) evaluate the properties of the resulting cements.

2,5-Dimethoxyphenol (DMP) was obtained by diazotization of

2,5-dimethoxyamil ine with NaNC^ in dil H2SO4, similar to the procedure

of Asti 11, Fassett and Rondabush (Biochem. J. 72^, 451 , 1959).

By substituting DMP for eugenol the setting time of a commercial

ZOE powder mix was reduced from 4 min to 30 sec. Properties of cements

prepared from various compositions made from DMP, o-ethoxybenzoic acid

(EBA) or eugenol are shown in Table 17. Presence of EBA speeds up

Table 17

Properties of Cement Prepared from 2,5-Dimethoxyphenol

Powder: 64% ZnO, 30% A^O^, 6% hydrogenated rosin

Powder-liquid ratio: 1.7 g/ 0.2 ml Concentration of Liquid Setting Time Compressive Strength

EBA

a DMP

b EUGC (min) MPa

80 20 - 6.5 56.0 ± 4.7

62.5 37.5 - 6.5-7 47.7 ± 0.8

50.0 50.0 - 5.5 36.9 ± 0.3

41.7 33.3 25.0 3.5-4 52.4 ± 3.6

62.5 - 37.5 4. 5-5.

5

81.3 t 15.5

_ 50.0 50 n, 30 •

a o-ethoxybenzoic acid

b 2,5-dimethoxyphenol

c eugenol

39
setting time and improves strength which is considerably higher than

that of zinc oxide eugenol, but somewhat lower than that of EBA cements.

Thus DMP cements may be useful where cements with properties intermediate

to those of ZOE or EBA are desired provided DMP has the same biocompatibility

as the structurally related eugenol.

Hexyl 4-hydroxy-3-methoxybenzoate (hexyl vanillate, HV) was

synthesized from vanillic acid, n-hexanol in the presence of p-toluene

sulfonic acid. After refluxing for 26 hours and distilling under reduced

pressure 24.5 g. of product was obtained. An initial HV-ZnO mix required

several hours to harden. The setting time was reduced greatly when EBA-HV

liquid was employed. Whereas eugenol, and to a much lesser extent DMP, inhibit

polymerization of composite formulations, HV does not retard this reaction.

(Table 18). Hence, HV containing (non-eugenol) cement will be further

studied for possible use with composite resins.

Table 18

Inhibition of the Polymerization of Composites by Phenolic Compound

Composite: Adaptic

Phenolic compound was added to the mix

Percent Phenol in Mix Setting time, min. Comments

- 4.5 •

5% Eugenol does not harden Yellow-brown

5% DMP II H II Ptnk

1% DMP 90 Soft set, dark pink red

1% HV 4.5 - 0.1% Eugenol ^ 30 Soft, slightly yellow

0.1% DMP * 15 Pink

0.1% HV 4.1 -

40
II. Development of Adhesive Bonding Techniques

The objective is to develop a basis for clinically applicable adhesion

techniques suitable for bonding polymer materials to mineralized tissues,

e.g. dentin and bone. A clinically acceptable technique which establishes

durable adhesive bonding between calcified tissues and dental restorative

and sealant materials probably would not only reduce significantly the

incidence of secondary caries that can arise from microleakage between

restorations and tooth surfaces, but it would also lead to a greater preservation of sound tooth structure through the increased use of conservative

dental therapy.

One approach toward achieving such effective adhesion involves the

design of suitable coupling agents that can form stable chemical bonds

between the polymers used in dental preventive and restorative materials

and one or more of the components of hard tooth tissue.

A. Adhesion Promoting Functional Monomers

1. Isocyanate Urea Methacrylates

The well known reactivity of organic isocyanates with compounds having active hydrogens (e.g. -OHj-Nh^, etc.) and the latent presence

of such groups in dentin suggested the synthesis of urea methacrylates with

pendant isocyanate groups as potential adhesion-promoting functional monomers.

The syntheses of two isocyanato urea methacrylates are conveniently effected

by the controlled reaction of N-tert- but.yl -2-ami noethyl methacrylate (TBAEM)

and di isocyanates that have isocyanate groups of different reactivities such

as toluene diisocyanate and 3-isocyanatomethyl-3,5,5-trimethylcyclohexyl

isocyanate, usually identified as isophorone di isocyanate (IPDI).

41
The isocyanato urea methacrylate, TBAEM-TDI, a white solid, was

derived from N-t-butyl-2-aminoethylmethacrylate (TBAEM)and toluene diisocyanate (TDI) by the route shown below

20°C n-hexane

CH^ 0

I 3

II H

CHo = C-C-O.CH0 CH 0 -N-C-N2

II 2 2

| 0 ch

3 -c- ch 3

CH.

TBAEM-TDI

Similarly, we have prepared a liquid isocyanato urea methacrylate from TBAEM and IPDI as shown below:

0

CH«=C-C-OCH0 CH«-NH +

‘ 1 t t , 0CN-CH

2

-r

ch

3

TBAEM

CH

3

C_CH

3

CHo CH

U/ N

o n-hexane, 20°C

CH

3 IPDI

42

TBAEM- I PD

I
II. Development of Adhesive Bonding Techniques

The objective is to develop a basis for clinically applicable adhesion

techniques suitable for bonding polymer materials to mineralized tissues,

e.g. dentin and bone. A clinically acceptable technique which establishes

durable adhesive bonding between calcified tissues and dental restorative

and sealant materials probably would not only reduce significantly the

incidence of secondary caries that can arise from microleakage between

restorations and tooth surfaces, but it would also lead to a greater preservation of sound tooth structure through the increased use of conservative

dental therapy.

One approach toward achieving such effective adhesion involves the

design of suitable coupling agents that can form stable chemical bonds

between the polymers used in dental preventive and restorative materials

and one or more of the components of hard tooth tissue.

A. Adhesion Promoting Functional Monomers

1. Isocyanate Urea Methacrylates

The well known reactivity of organic isocyanates with compounds having active hydrogens (e.g. -OhU-N^, etc.) and the latent presence

of such groups in dentin suggested the synthesis of urea methacrylates with

pendant isocyanate groups as potential adhesion-promoting functional monomers.

The syntheses of two isocyanato urea methacrylates are conveniently effected

by the controlled reaction of N-tert- butyl -2-ami noethyl methacrylate (TBAEM)

and di isocyanates that have isocyanate groups of different reactivities such

as toluene diisocyanate and 3-isocyanatomethyl-3,5,5-trimethylcyclohexyl

isocyanate, usually identified as isophorone di isocyanate (IPDI).

41
The isocyanato urea methacrylate, TBAEM-TDI, a white solid, was

derived from N-t-butyl-2-aminoethylmethacrylate (TBAEM)and toluene diisocyanate (TDI) by the route shown below

20°C n-hexane

CH q 0

I 3

II H

CHo * C-C-O.CHoCHo-N-C-N2

I! 2 2

| 0 ch

3 -c- ch 3

CH.

TBAEM-TDI

Similarly, we have prepared a liquid isocyanato urea methacrylate from TBAEM and IPDI as shown below:

n C^3^S^HC0

CH

2

=C-C-0CH

2

CH

2

-NH + 0CN-CH

2-p

ch

3

TBAEM

CH

3

C-CH

3

CH. CH

U

3

N

CH

3 IPDI

0 0

CHo =C-C-0-CHoCHo -N-C-NH-CHo-v* i \ £ Z | 2

ch

3

ch

3

-c-ch

3

CH.

n-hexane, 20°C

CH.

42

TBAEM- I PD

I
These materials have been produced in sufficient quantity

for characterization measurements and for evaluation of their adhesionpromoting ability to bone and dentin.

B. Surface-Active Amine Accelerators as Adhesion Promotors

Another type of potential adhesion-promoting agent under study

is the surface active amine accelerator. Our study of the effect of surfaceactive amine accelerators on hydroxyapatite- (HA) filled composites has been

extended to include 4-N,N-dimethylaminobenzoic acid (4-DMAB) and 3-N,Ndimethylaminobenzoic acid (3-DMAB). By determining the influence of coupling

agents on the strength properties of a HA-filled composite, an estimate of

the usefulness of a substance as a potential adhesive bonding agent can be

made. HA containing preadsorbed 4-DMAB (2.3%) prepared by Dr. Misra of this

laboratory was used in the preparation of composite specimens for a formulation of BIS-GMA (7)/TEGDMA (3) containing 1% BP and 0.06% tyrosine. The

setting times and diametral tensile strength were determined and are given

in Table 19 (Formulations VI and VII). Some of the previous results are

shown for comparison.

In Table 20 are shown the results for HA composites prepared by

paste/paste formulations and using 4-DMAB (H, I) and 3-DMAB (J, K) dissolved

in the monomer system rather than preadsorbed onto HA. The DTS of the composites are considerably higher for 4-DMAB in these formulations (H, I)

compared to those obtained with formulation VI (Table 19). Table 21 is an

attempt to devise a control applicable to these HA-filled composites using

a very effective amine accelerator (DMSX) that has virtually no surface-active

character. The DTS results for HA composites formulated with DMSX were

significantly lower than those obtained using dissolved 4-DMAB and 3-DMAB.

43
TABLE 19

Setting Times and Diametral Tensile Strengths of

HA-Filled Composites* Using Adsorbed Surface-Acti ve Amines

Diametral

Tensile

Formulation

Monomer

System HA P/L

Setting

Time

(mini

Strength

MPa + Std.Dey.

(No. of Specimens}

I BIS-GMA(7)

TEGDMA (3)

BP = 1%

TYR = 0.1%

DMAPAA =1.9% 5/6 very fast

<1.0

19.9 + 4.9

(41

II Same as I but BP = 0.25%

and TYR = 0.05%

Same as I 2/3 1.75 24.5 + 6.6

(4)

- Ill Same as I but TYR = 0.07%

DMAPAA =0.18% 2/3 3.0 21.6 + 2.7

IV Same as I 4 -DMAS = 2.4% 2/3 5.0 24.1 + 5.4

C5)

V Same as I but BP = 2.1%

and TYR = 0J%

4- DMAS = 2.4% 2/3 3.0 23.2 + 2.9

(4}

VI Same as I but TYR = 0.06%

4-DMAB = 2.3% 2/3 5.0 21.5 + 7.4

(6)

VII Same as VI but stored at 37°C and 100%

relative humidity for 72 hours rather

than 24 hours

19.8 t 4.1

(5}

* Composites prepared by powder/liquid technique

44
TABLE 20

Setting Times and Diametral Tensile Stregnths of

HA-F111ed Composites* Using Dissolved SurfaceActive Amine Accelerators

Diametral

Tensile

Setting Strength

Time MPa ± Std.Dev.

Formulation Peroxide Paste Acc. Paste P/L (min) (No. of Specimens)

A BIS-GMA(7)

TEGDMA (3)

BP = 1%

TYR = 0.1%

BIS-GMA(7)

TEGDMA (3)

P0LYSAM-1 = 1%

5/6 <1 min

fast

20.9 + 1.5

t4)

B+ Same as A P0LYSAM-1

» 0.5%

2/3 VIQ.O 36.5 + 4.4

(4)

C Same as A DMAPAA

= 0.18%

2/3 3.0 22.3 ± 5.2

C5>

D Same as A

BP * 0.25%

TYR = 0.05%

DMAPAA

= 0.18%

2/3 8.0 31.9 ± 3.7

(4)

E Same as A

but TYR - 0.06%

DMAPAA

= 0.36%

2/3 1.0 23.2 + 4.6

(6)

F+ Same as A 4- DMAS

» 0.36%

2/3 15.0 16.9 t 2.7

15)

G+,a Same as A A-4-DMAS

- 0.5%

2/3 17.0 34.0 ± 8.4

(5)

H+ Same as E 4-DMAB

• 0.5%

5/6 16.0 28.8 + 1.5

(4)

1+ Same as E 4-DMAB

* 0.5%

2/3 17.0 31.8 + 0.9

(4)

J , Same as E 3-DMAB

= 0.5%

5/6 5.5 28.0 i 0.9

(5)

K Same as E 3-DMAB

= 0.5%

2/3 6.0 28.8 + 3.1 (4)

* Composites were prepared from equal parts of peroxide and accelerator paste

t Cured in mold for 20 minutes instead of the usual 15 minutes

a Formulation G was stored for 72 hours In 100% humidity bath at 37°C

45
Formulation 0 of Table 21 which is for unfilled resin but using the same

catalyst and other ingredients also gave DTS values significantly higher

than those prepared with HA filler. Apparently the uncoated HA can act

to reduce the tensile strength of the BIS-GMA copolymer, perhaps by

introducing defect sites in the organic matrix.

As a method for assessment of the adhesion potential of these

surface-active amine accelerators, comparative diametral tensile strength

measurements, performed on hydroxyapatite filled composites, did not

yield results as definitive as those obtained from similar measurements

comparing the strengths of silanized and unsilanized glass composites.

Nevertheless, the results of this study indicate that some surfaceactive amine promotors, under some conditions, can lead to improved

adhesion of dental restorative or sealant materials to apatitic surfaces.

A manuscript entitled"The Accelerative and Adhesive Bonding

Capabilities of Surface-Active Accelerators" was submitted to Journal of

Dental Research for publication.

C. Literature Survey of Reactive Adhesives with Potential for Dental

Application

The possible usefulness of dental applications of "reactive

adhesives", which have been suggested in the patent literature for

bonding various metals at room temperature has been investigated. These

adhesives are based on two component systems that are brought together

when two substrates treated with these components contact each other.

The components react to produce a chemical cure within a few minutes.

The adhesive is usually prepared by dissolving an elastomer in

a monomer or oligomer solution. Curing is by a free radical mechanism

and rapid polymerization occurs. The cured system is toughened by the

elastomeric domains which are incorporated into the structure by grafting.

46
Table 21

Setting Times and Diametral Tensile Strengths of

HA- Filled Composites* Using DMSX+

• Diametral

Tensile

Setting Strength

Time MPa + Std.Dev.

Formulation Peroxide Paste Acc. Paste P/L Onin) (No. of Specimens)

L BIS-GMA(7)

TEGDMA(3)

BP = 1%

TYR ? 0.1%

BIS-GMA(7)

TEGDMA(3)

DMSX = 0.23%

5/6 4.0 23.7 + 1.7

(5)

M Same as L Same as L 2/3 2.0 23.2 * 2.6

(5)

N Same as L but TYR = 0.06%Same as L 2/3 1.5 21.7 + 1.4

(5)

0

a Same as N but no HA

Same as L but no HA

2.0 30.7 + 3.8

(6)

Composites were prepared using equal parts of peroxide

and accelerator paste

t DMSX * N,N-dimethyl-sym-xylidine, a non-surface-active accelerator used here^

to provide a control for the investigation of surface-active accelerators.

a Unfilled resin, prepared from equal parts of 81 S-GMA(7)/TEGDMA(3)

with 12 BP and 0.06% TYR, and the same monomer system with 0.23%

DMSX

47
In our initial studies formulations similar to those described by

Wolinski (U.S. patent No. 3,994,764) were used which are made from soluble

polyurethanes, acrylic or methacrylic acid and methyl methacrylate monomers,

benzoyl peroxide initiator and an inhibitor such as butyl ated hydroxytoluene

(BHT). The second component is a solution of amine accelerator with which

the substrate surfaces (bone) are treated prior to application of the

urethane-monomer component. In this exploratory work adhesion between flat

bone substrates in air, 100% relative humidity and on storage in water was

evaluated.

Problems in developing suitable formulations involved selecting a

urethane which was completely soluble in the monomers. A commercial polyurethane (Estane 5712) which is claimed to be a reaction product of tetramethyleneglycol ethers of varying molecular weight and methylene di isocyanate was found to be monomer soluble.

Initial formulations cured much too slowly at room temperature to

be clinically useful. On employing high concentrations of accelerator the

viscous adhesives cured within 30 minutes which is still too slow for

clinical application. Partial substitution of a dimethacrylate (decamethylene dimethacrylate, DMDMA) increased the reactivity so that bonding

occurred within the period of several seconds to three minutes. In order to

use urethanes other than Estane which does not have pendant isocyanate

groups , efforts were made to replace acrylic acid by monomers which do not

contain carboxylic acid groups. Highly viscous solutions of Estane in

DMDMA and methyl methacrylate resulted. Substitution of isodecyl acrylate

and isobutyl methacrylate for methyl methacrylate gave monomer mixtures in

which the Estane polyurethane was not soluble.

48
Other changes in the compositions of the solutions were made

to study the effect of the following parameters on the characteristics

of the reactive adhesive formed and the resulting bone-to-bone bond:

(1) ratio of DMDMA to methyl methacrylate concentration, (2) substituting

other monoacrylate or monomethacrylates for methyl methacrylate, (3) replacement of acrylic acid by other monomers not containing carboxylic acid

groups, (4) changes in the amine accelerator or solvent used.

Curing of the adhesive occurred for all compositions in which the

urethane was soluble. Good adhesion between the substrates was obtained

in air. However, for most formulations, debonding occurred quite rapidly

in an aqueous environment. Most joints broke fairly readily after storage

for 3 hours at 37°C and 100% RH or after storage in water. A joint prepared from a reactive adhesive formulation composed of 33% Estane, 33%

DMDMA, 17% acrylic acid, 17% methyl methacrylate, 0.04% BHT and 3.6% benzoyl

peroxide in which the substrate had been treated with 10% alcoholic dimethyl-p-toluidine did not debond on extended storage in water. Preliminary

results do not indicate whether substrate treatment with 10% dimethyl -ptoluidine dissolved in ethanol or 1 ,6-hexamethylene glycol dimethacrylate or

10% dimethyl aminophenyl acetic acid in ethanol yields adhesives with better

bond strength. The latter amine was employed because it can be absorbed

irreversibly on dentin from non-polar solvents.

Estane was found to be soluble in DMDMA-methyl methacrylate. Such

monomer mixtures may prove useful as vehicle for adhesives containing polymerizable molecules with residual isocyanate groups which react with active

hydrogen. Thus the reaction product of isophorone di isocyanate and tertbutyl ami noethyl methacrylate (IPDI-TBAEM) previously synthesized in this

49
laboratory does not dissolve benzoyl peroxide. To evaluate the adhesive

characteristics of this compound the following composition was prepared:

30% IPDI-TBAEM, 30% DMDMA, 40% methyl methacrylate, 3% benzoyl peroxide,

0.4% BHT. Bone treated with amine accelerator and this composition gave

a joint that readily separated on storage in a 100% RH environment.

D. Dental Tissue Debris Cleansing, Toxicity and Adhesion

The work conducted on our suggestion by Mclnnes and Clayton Jones

of the Unvierstiy of Witwaterstrand, South Africa, to evaluate the cleansing

effects of very dilute acid solutions and to determine the response of the

underlying pulpal tissues to these acid solutions was completed. The

pulpal responses elicited by 1% and 0.1% citric acid solutions in unlined

and Dycal lined cavities after acid application were compared. The pulpal

responses were evaluated in the permanent maxillary and mandibular incisors

in 48 monkeys using labial class V cavities. Most severe pulpal responses

were obtained with 1% aqueous and 1% dilute alcoholic citric acid solutiontreated cavities followed by a silicate cement. Based on these results the

use of these dilute acids to remove the smear layer and improve bonding to

dentin, as was suggested in our previous in vitro work with 2-cyanoacrylate

adhesives, cannot be recommended. The possible combination of Dycal with acid

treatment to eliminate poor tissue response and yet obtain at least adequate

temporary bonding is to be examined.

50
III. Wear Resistance and Mechanical Properties of Dental Materials

The principal immediate objective is to develop, or make use of,

appropriate techniques to measure wear resistance and mechanical properties

of dental materials and to use the forthcoming data as performance indicators to predict in vivo durability of these materials. The completion

of the development of these methods to a satisfactory state -is. particularly

important because of the long times and efforts required for clinical evaluations. In order to accomplish this task,. some fundamental research on

wear and related mechanical properties is being done to obtain a better

understanding of the relevant degradation processes. This information

will be of use in determining the principal variables of influence from

which appropriate modifications may be incorporated in the wear apparatus

to obtain meaningful results. In addition, the improved understanding of

ways in which specific mechanical properties of composite systems correlate

with wear behavior is expected to be instrumental in developing more durable

systems.

Two types of wear tests have been developed here which comprise a

classical pin and disc apparatus and an erosion technique. Although these

particular methods are not necessarily expected to be used as final performance indicators, they do give basic information relevant and possibly

essential to the development of an appropriate durability test, as will be

apparent in later sections of this report. Complementary efforts involve

microdefect analysis using x-ray and optical microscopic observation of

damaged regions made resolute by a silver staining technique. In order

51
to obtain a relevant wear test we assert that the subsurface damage

resulting from in vitro wear should resemble that obtained from i_n vivo

worn specimens. Another aspect studied is the coupling between certain

chemical solvents and wear. The following paragraphs describe the work

performed during this fiscal year on wear and mechanical properties of

dental materials.

A. Pin and Disc hi Vitro Measurements

The pin and disc apparatus is completely automated comprising

three identical rotating platforms containing the disc shaped specimens

of the material to be investigated. The principal of operation is

depicted by Figure 1. A stationary slider (pin) of human enamel, or

appropriate substitute, impinges on each of the rotating specimens

producing a wear track of 12 mm mean diameter. The slider is loaded

with weights to obtain the desired normal stress which is usually 10

MPa. The depth of the wear track is measured periodically at 10 equally

spaced positions along the track circumference using linear variable

differential transformers with ruby tipped probes as shown in the figure.

Distilled water at 37°C flows over the specimens to control temperature,

lubricate, and wash away debris. Figure 2 is a close-up photograph

showing the specimen and cup, wear pin and mounting collet, probes and

transformer, and the thermocouple junction.

In this work the wear rate G (with respect to distance traveled)

is defined as

G = V/LF (1)

Where V is the volume of material removed, L is the total track length,

and F is the normal force or load. Using the relations V

= -rrabs, L = Tran,

52
LVDT

Wear Track

Fig. 1. Schematic illustration of principle of pin and

disc measurement.

53
Close-up

photograph

showing

wear

pin

and

mounting

assembly,

transformer

assembly,

and

water

jet

nozzle.
and F = ira 2 /4, where a and b are the wear pin and track diameters, respectively, s is the track depth, n is the number of revolutions and x is the

normal stress, the operating equation

G = 4m/TTax (2)

is obtained from eq. (1). Eqs. (1) and (2) are equivalent only over a

region where m = ds/dn is constant with time.

A considerable portion of our activity over the past year has been

devoted to obtaining an appropriate substitute for human enamel wear pins.

Human enamel is objectionable in this application for the following reasons:

(1) It is inhomogeneous and anisotropic.

(2) Sample to sample variation is large.

(3) Fabrication of wear pins is difficult.

(4) It is chemically unstable.

(5) Enamel layer is too thin for long time wear tests.

In view of these objections it is difficult to obtain, or even conceive

of, high quality experimental procedure with so many additional variables

of influence introduced through the use of enamel wear pins.

To date three possible substitutes for enamel have been investigated for which the results are given in Table 22. In addition to the

wear rate G, two kinds of standard deviation are included to depict the

irregularities observed in these measurements. a-| is obtained from the

residuals about a linear regression over an apparent linear region of

track depth versus revolutions data, a

2

is obtained from the residuals

about an average of G values over the 10 positions around the track circumference. (See Figure 1) Accordingly, a-j is a measure of the apparent

irregularity of wear with time including experimental imprecision, whereas

55
a

2 is presumably a measure of specimen inhomogenuity . Since o

2 has always

been found to be considerably larger than a-j , it is apparent that additional

improvements in experimental precision will not enhance the facility of this

technique to evaluate dental materials.

TABLE 22

Summary of Wear Rates

Using Various Pin Materials

Couple

G

TPa"

1 TPa"1 °2

TPa"

1

Velvalloy - Enamel 0.0518 0.00051 0.0064

- Durapatite* 0.0533 0.00049 0.0058

- Stainless Steel 1

" 0.0488 0.00036 0.0055

- Sapphire 0.0795 0.00043 0.0051

Adaptic - Enamel 0.0106 0.000038 0.0014

- Durapatite 0.0084 0.00012 0.0032

- Stainless Steel 0.0615 0.00070 0.0036

- Sapphire 0.00416 0.00022 0.0026

* A form of sintered hydroxyl apatite made by Sterl ing-Winthrop

Research Institute

t 18-8, 303 (austenitic)

Velvalloy and Adaptic were chosen as wear specimens because they were used

in the three year clinical tests of Phillips and coworkers [5-7]. In their

work based on deterioration of anatomic form, the amalgam was found to be

superior to the composite. On the contrary, according to the results in Table

22, the composite displays superior in vitro wear performance when enamel,

durapatite, or sapphire wear pins are used. With stainless steel pins.

56
however, the wear increases markedly on the composite and a correlation,

although very marginal, with the clinical tests is obtained. Although

the results in the table show that either durapatite or sapphire is a

good substitute for enamel, in vivo wear on restoratives from opposing

enamel does not appear to be the most significant contributing factor to

the degradation of restoratives.

When the values of G in Table 22 were plotted against the hardness

of the wear pins, an interesting result was obtained as illustrated by

Figure 3. With the amalgam the wear rate increases with increasing pin

hardness displaying regular monotonic response as expected from a normal

wear mechanism. With the composite an inverse trend is observed for which

the wear rate decreases with increasing hardness. Although the response is

monotonic, the stainless steel pin produces an outstanding amount of wear,

about six times as much as any of the others.

Although the result with stainless steel may at first be a paradox,

the wear dependence of composites on pin hardness may be explained using the

illustration of Figure 4. For materials with hardness values approaching,

or greater than those for the reinforcing filler, the matrix and filler wear

slowly together and a polishing effect is obtained as observed from our

post wear microdefect analysis. With sufficiently soft materials, but

presumably harder than the matrix, the rough edges of the filler wear the

pin, and the resulting rough edges of the pin penetrate and preferentially

wear the matrix. Eventually essentially unworn filler particles are dislodged and washed away with the wear debris. It is conceivable that some

filler particles are lodged in the surface of the pin and thus produce

accelerated wear on the composite. The microdefect analyses described later

in this report substantiates the validity of this mechanism.

57
•

Velvalloy

o

Adaptic

CM

ro

O

to

CO

CM

CM

ro

8

O W •

%

t » cd in

a>E

o

c

Ui

ro CM

(,J>dl) 201X9

CM

CM

CM* — O

58

Log

K.

H.

P.

Fig.

3.

Wear

rates

of

Velvalloy

and

Adaptic

plotted

against

Knoop

Hardness

Number.
Reinforcing

Filler

Matrix

59

Fig.

4.

Schematic

drawing

illustrating

the

reason

for

increased

wear

of

dental

composites

with

a

softer

wear

pin.
In a previous annual report [1] we stated that we observed a

low initial wear for Vel vail oy using a stainless steel pin. The initial

transient with a small wear rate and a subsequent steady state of much

higher rate are repeated after a sufficiently long rest period. This

behavior is believed to be somewhat general for alloys and is attributed

to a passive surface layer which reforms during dormant periods [8].

Accordingly, as illustrated in Figure 5, the formation of the passive

layer leads to two wear regimes called oxide and metallic wear. Presumably, the wear in the oxide region is less because of the reduction

of adhesion. As shown in Figure 5, the process is repeated after a

dormant period. It is desirable to repeat this process because the

initial response during the first time may be obscured from "break in"

scatter, which is usually encountered in wear measurements.

In order to obtain some insight into the nature of composition

change with penetration of the surface, some preliminary Auger spectroscopy measurements were made on several dental alloys in collaboration

with the NBS Surface Chemistry Division. Observations were made on

Vel val loy ; the crown and bridge alloys, Ticon , Ceramalloy and Pent i 11 ium ;

and nickel was used as a control. All measurements revealed a decrease

in oxygen concentration with sputtering time which is a measure of the

depth penetration of the sputtering ions and of material removed. In

addition to the observed depletion of oxygen with depth, some changes

were observed in the distribution of the metallic elements. For example,

with Vel val loy , silver appears below the surface, but is completely

absent at the surface. On the other hand there is a decrease in tin

content with penetration. At present we have only two measurements on

each material mentioned above:

60
Metallic

Q)

CL

<D

E

h

m

cn

sso-j 8un|o/\

61

Typical

wear

response

of

alloys

illustrating

initial

transients

of

low

wear

following

rest

periods.
one initial (without sputtering) and one after sputtering with Argon ions

o for ten minutes, which is estimated to remove 100 A of material. We intend

to obtain more extensive depth profiles on dental alloys in the next year.

The behavior described above is expected to have relevance to

in vivo wear. Mastication occurs over short periods with long rests in

between (except possibly in cases where bruxism persists). Consequently,

it is doubtful that the passive surface is ever completely removed, which

would result in very little wear as observed for amalgams. Finally, we

point out that if the initial value of G = 0.0019 TPa~^ for Vel valloy

(with stainless steel pin) instead of its steady state value 0.0488

(Table 22) along with 0.0615 for Adaptic , a very strong correlation (a

factor of 32) is obtained with clinical tests.

Pin and disc wear tests were made on the three crown and bridge

alloys mentioned above. These alloys are being evaluated in collaboration

with the base metal -porcelain interface activity described in Part IV of

this report. On these materials sapphire pins were used. Attempts to use

durapatite were unsuccessful because of repeated pin fracture when worn

against these materials.

The results for the crown and bridge alloys are given in Table 23.

The meanings of the standard deviations a-j and are the same as those

included in Table 22. tQ

i s the extent of the transient time over which low

initial wear is observed. There are essentially no differences between the

low wear rates of these materials which approximate that for Adaptic worn

against a hard pin (see Table 22). Of the three Ceramalloy is the only

one which did not exhibit any initial transient wear. This may result

from the presence of boron in this alloy (which is apparently not present in

the others .

)
TABLE 23

Wear of Crown and Bridge Materials

And Microfilled Composite Using Sapphire Wear Pins

Material

G

TPa"

1

a i TPa"

1 o 2 TPa"

1

t

hrs

Ticon 0.0064 0.00076 0.0012 4

Ceramalloy 0.00770 0.000054 0.00037 0

Penti Ilium 0.0062 0.000050 0.0022 2

Profile 0.043 0.000088 0.016 -

The results for a Strontium glass filled composite Profile are

also included in the table. Profile wears much faster than the conventional composite Adaptic and approaches that for the amalgam (see Table

22). Note that according to the standard deviations, o-j and » the wear

is very smooth with time; however, the sample is quite inhomogeneous.

We plan to obtain wear data on Profile using stainless steel wear pins

for the reason mentioned earlier with respect to influence of pin hardness.

According to the microdefect analysis using a silver staining

technique described later in this section, in vivo worn composite specimens

show considerable subsurface damage. In vitro worn specimens show considerable damage using stainless steel pins at 10 MPa. In order to determine the

influence of stress on damage, pin and disc wear measurements were made on

Adaptic specimens at six different stress levels using stainless steel pins.

During these experiments we obtained a trend in the wear rate

which we have not noticed before. The wear proceeds at constant rate (with

time) over a certain region and then increases by roughly a factor of two

63
and then continues at the larger constant rate indefinitely. Examples

are illustrated by Figure 6, where the track depth is plotted against

time at 5 and 12.5 MPa normal stress. The damage accumulated during the

first region is believed to cause the change of rate at the onset of the

second region. Similar behavior is observed by Dowson [9] and coworkers

at the University of Leeds on high molecular weight polyethylene. They

attribute the first region to an adhesive mechanism and the second,

adhesive plus fatigue.

The wear rates (G-j and G^) for the two different regions for

Adaptic are summarized in Table 24 along with their ratio. The stress

dependence of the wear rates appears to be somewhat constant at the low

stresses (except at 2.5 MPa where no significant wear is observed) and

then increase rapidly with increasing stress. From the microdefect

analysis the qualitative damage rankings (with increasing damage) are

given on the right. Damage appears to increase with increasing stress

to about 10 MPa and then gradually decreases. We believe that the

reason for the decrease in the observed damage above 10 MPa is that the

wear there is more severe, hence damage layers are removed as wear

progresses.

No damage is apparent on Adaptic specimens when wear is terminated within the first region (using stainless steel pins) or at anytime

when enamel, or enamel like, pins are used. We have also not observed

the changes in the wear rate as described above when enamel, or enamel

like, pins are used. Since in vivo worn specimens reveal subsurface

damage, these results preclude the possibility of using enamel, or

enamel like, wear pins to simulate in vivo wear.

Pin and disc wear measurements were also made on Adaptic

specimens immersed in certain chemicals as part of a study described

later in this section.

64
12.5

MPa

I

I

>

0>

(uirf)s

65

I

I

I

f(hrs)

Fig.

6.

Track

depth

versus

time

curve

for

Adapti

c

at

a

stress

level

of

5

and

12.5

MPa

revealing

two

regions

of

different

wear

rates.
Of the specimens stored in ethanol, cyclohexanol , and distilled water

for two weeks at 37°C, only the last revealed no damage. Wear measurements on the others showed up to 90 ym of material removed over the

first revolution in contrast to the water immersed specimen for which no

material loss was observed. From there on the steady state wear rates

are essentially the same. It is apparent that the damage resulting from

ethanol and cyclohexanol is so severe that the wear resistance of the

inflicted damage regions is essentially null.

Table 24

Wear Measurements on Adaptic

At Different Normal Stresses Using

Stainless Steel Wear Pins

Stress

MPa

G

1 TPa

G

2

TPa

G

2 /6

1 Damage

Ranking

2.5 0 0 0

5.0 0.37 0.58 1.57 1 10.0 0.92 3

12.5 0.57 1.43 2.49 2

15.0 1.91 5.10 1.46 1 20.0 6.5 7.4 1.14 0

66
B. Subsurface Damage Analysis Investigations

A staining technique was developed to reveal the micro-defects

inside dental composites, specifically in the damage zone immediately beneath

the worn surface. Fine silver particles were introduced into the defect

region and the extent of damage, e.g. development of microdefects, was

examined qualitatively with optical microscopy and quantitatively with microprobe technique.

1. Analysis Applied to Clinically Worn Composite Materials

Fifteen in vivo worn dental composites and two unfilled plastic

(PMMA) components from a clinically worn partial denture were examined. These

clinically worn specimens were provided through Dr. Everett Cobb, a guest

worker on the staff from the Georgetown University Dental School. The

results of the examination of these specimens are summarized as follows:

(1) Only few crazes or microcracks were observed at the wear surface

of the PMMA denture teeth. These cracks are found to be perpendicular

to the wear surface. No severe damaged zone was found. However, it is

noteworthy that this observation was made on two samples (molar) from a

partial denture, consequently, the force exerted on these pieces may not be

as great as that on a normal tooth.

(2) Damage layers of 10 ym to 200 ym were observed on occlusal

surfaces of the dental composites, on the mesial surfaces covered with plaque

and around internal air bulbs opened to the wear surface, (e.g. see Fig. 7)

(3) The thickness of the damage layers varied from location to

location; whereas the damage zones around the air bulbs opened to the wear

surface had rather uniform thickness.

(4) Within the damage layers, the silver seemed to collect preferably around the filler particles, especially around the larger ones.

67
I eoonq

jenOu ;

|

68

Fig.

7.A

longitudinal

section

of

a

clinically

worn

dental

restorative

composite,

the

subsurface

damage

beneath

the

occlusal

surface

becomes

visible

after

silver

staining.
(5) The wear surfaces of the in vivo worn composites were not

smooth; filler particles protrude on the wear surface.

(6) The quantity of silver vs. the depth of the damage layer

was measured with microprobe using the copper La line. The result

indicated a rather sharp boundary exists between the damage layer and

the undeformed part.

The above observations tend to suggest that the in vivo

wear process in dental composites is a combination of chemical and

mechanical erosion, preferably occurring at the particle-matrix interface.

2. Analysis Applied to In Vitro Worn Composite Materials

Employing the silver staining technique to examine in vitro

worn composite restoratives indicated that:

(1) No damaged sublayer was observed beneath an Adaptic

sample worn by a durapatite pin in a pin and disc wear test. The normal

load used in this test was 10 MPa. Furthermore, the filler particles were

found to be worn away at the same rate as for the matrix. Consequently,

the wear surface was smooth without any protruding particles.

(2) Five in vitro worn Adaptic samples obtained from the

same pin and disc wear equipment but with a stainless steel pin were

examined. The normal loads applied on these samples were 5, 10, 12.5, 15

and 20 MPa, respectively. Protruding filler particles were found on the

wear surface of all samples. Maximum sublayer damage was observed on

samples worn with 10 MPa normal load; little sublayer damage was observed

when the load is increased to 20 MPa force.

(3) No sublayer damage could be observed on the thermal -cycled

composites that were not exposed to a physical wear process. The dental

69
composite samples were prepared with Concise material following the procedure recommended by the manufacturer. Samples had been aged in 37°C

water for 2 weeks prior to the thermal cycling test. During the cycling

test, the composites were immersed in the 5°C and 55°C water baths

alternatively and the dwell time in each bath was 75 seconds. Samples

were removed after completing 3800 cycles and 7600 cycles and subjected

to the silver staining technique.

(4) No sublayer damage was observed within acid immersed

composites. The samples used were identical to those for the thermal

cycling tests. Lactic acid, formic acid and acetic acid were chosen for

the etch test. The solution pH was maintained at 4.5 throughout the

test. Composite samples were stored in the solutions at 37°C for one

and two weeks before they were removed. No change in structure of these

acid treated composites could be detected using the silver staining

technique. These specimens were not subjected to any physical wear

process.

(5) Some minor amount of filler and matrix interfacial

damage was observed in compression fatigued dental composites. The

samples were again prepared in an identical way as those for the thermal

cycling or acid tes. A servo-control MTS equipment was used for the

compression fatigue test. For Concise material the fatigue limit has

been previously determined to be approximately 145 MPa for 5,000 cycles

[10]. Throughout the present work, the load was cycled between 0 MPa

and 145 MPa. Samples were obtained after 500, 1000, 2000, 4000 and 8000

cycles. Subsurface defects, mainly along the filler and matrix interface,

were observed using the silver staining technique. However, the extent

of damage caused by compression fatigue appears to be much less compared

with that observed among clinically worn samples that were examined in

the same manner.

70
3. Analysis Applied to Thermal Cycled, Acid Immersed or

Compression Fatigues Composite Specimens

Change in mechanical properties of these samples subjected to

thermal cycling, acid etching and compression fatigue was monitored by Knoop

microhardness tests. The results are listed in Table 25, and the data presented are an average of ten measurements. These microhardness test results

suggest that (1) thermal cycling between 5°C and 55°C does not degrade the

physical properties of the composites. In fact, the hardness seems to increase

as a result of the thermal cycling. This may be caused by further polymerization of BIS-GMA in the 55°C environment. (2) Except with lactic acid, no

deterioration in mechanical property as revealed by hardness was introduced

by the organic acid treatments. Verification of the lactic acid results is

being sought. (3) Although certain minor amounts of filler-matrix interfacial defect was introduced through the compression fatigue test, the

structure damage caused by fatigue is apparently not enough to cause any

decrease in hardness.

4. Analysis Applied to Organic Solvent Immersed Composite

Specimens

Eight chemicals with solubility parameter 6 ranging from

3 1/2 7.4 to 14.7 (cal/cm ) were chosen to study their effects on the

mechanical strength and the structure of BIS-GMA based polymer. Water

was used as the control for this study. One commercial dental restorative

composite (Concise) and one unfilled BIS-GMA (70)/TEGDMA (30) resin were

immersed in these chemicals. Changes in sample weight and surface hardness were monitored with time.

No significant change in sample weight was observed over

the test period of four weeks, e.g. the data of weight change of Concise

71
Table 25

Knoop Microhardness Test Results

of Dental Composites (Concise)

Sample Specification Average Standard Deviation

Compressive fatigue

144 MPa/8000 cycles 57.5 2.82

Thermal cycled

5°C-55°C/7600 75.4 3.42

Thermal cycled

5°C-55°C/3800 cycles 59.4 3.03

Lactic acid, pH = 4.5

2 weeks 48.4 3.14

Acetic acid, pH = 4.5

2 weeks 74.1 3.02

Formic acid, pH = 4.5

2 weeks 69.4 3.37

Control 55.2 3.53

Control 56.04 7.25

Control 58.8 1.46

72
is given in Figure 8. However, dramatic decrease in hardness (KNH) was

observed in both Concise and the unfilled resin. After these materials

were immersed in chemicals with solubility parameters ranged from 8.9 to

14.7 (Figure 9 and 10). The decrease in hardness is quite severe, e.g.

in unfilled BIS-GMA resin more than 70% of the original hardness was

lost over a period of three weeks. For samples immersed in heptane (6 = 7.4)

and water (6 = 23.4), the hardness either increased or remained constant.

The structure of the chemical -immersed BIS-GMA composites

was examined by the silver staining technique. A defect layer was

observed in all the samples suffering a reduction in hardness. The

resultant structure of a composite after immersion in ehtanol is shown

in Figure 11 which is rather similar to that observed within the clinically

worn samples.

This work establishes the fact that BIS-GMA based polymers

or composites are susceptible to deterioration by various chemicals.

Initial wear test data from this laboratory's pin-on-disc

machine was obtained on samples immersed in ethanol, cyclohexanone and

water and is reported in Section III A of this report.

C. Three-Body Wear Test

The purpose of this effort is to explore the role of

three-body wear as one of or perhaps the dominant mechanism in the in

vivo wear process. The hypothesis here is that the wear medium in the

oral environment is essentially food particles or debris instead of the

opposing tooth, and that the wear mechanism involves a chemically accelerated

erosion process instead of rigid surface contact abrasive wear.

In this approach, aqueous polyvinyl alcohol (PVA) solution

of various viscosity were chosen to simulate the action of food particles.

73
tfefae

toluene

/c*bn*

cydohuanoruL

z

-prop€*ol

PMSo

etkoel

HeOti

7.4-

*•?

?.?

a

9-9

/y.S1

2.0

,

z

n

l4

. mS

-

(6lu) q.L|6 Lajv\ 0[diue$

74

Fig.

8.

Change

in

weight

of

samples

immersed

in

chemicals

of

different

solubility

parameters.
Ob

(/>

CDQJ5

CD

C

o

’r—

</> SCD

uaqiiinN ssoupuen doou)|

75

Fig.

9.

Effect

of

chemicals

with

different

solubility

parameters

or

Hardness

of

a

dental

restorative

composite

(Concise)
O'L

aaqiunN sseupaen doou>;

76

Effect

of

chemicals

of

different

solubility

parameters

on

Hardness

of

unfilled

BIS-GMA

(30%

TEGDMA)

polymer.
Fig. 11. Section of a dental restorative composite (Concise) after softening

by ethanol. The damaged layer becomes visible after being silver

stained.

77
The wear samples are dental composites and dental amalgam placed in

extracted teeth which are in turn mounted in a fixing medium in such

a manner that two amalgam and two composite specimens are simultaneously

subjected to the viscous medium which distributes a selected load to

the specimen surfaces in a manner simulating food particles between

occlusal surfaces. A confining cell for the PVA and the specimens has

been designed and assembled to operate with hydraul ic-servo testing equipment. The experimental variables to be examined are the viscosity of the

wear medium, influence of abrasive particles, and influence of chemicals

with known solubility parameters.

78
IV. Dental Alloys, Ceramics and Implants

Lower initial cost and often superior properties have rendered nonprecious alloys as an increasingly attractive option to the use of gold

alloys in fixed partial dentures, both with and without porcelain veneers.

Previous reports [1,2] addressed the problem of achieving clinically

acceptable fits with single unit castings and the ability of porcelain

powders to "wet" [11] nonprecious alloy surfaces, thereby leading to

potentially strong chemical bonding between procelain and alloy.

Current studies of porcelain/alloy compatibility are directed

toward defining the properties of porcelains and alloys as they relate

in terms of residual stress for veneered prostheses. It is anticipated

that clinicians, laboratory technicians and industrial personnel will be

able to use such information toward defining porcelain alloy combinations which will best achieve the desired end results in function.

Additional studies are in progress regarding fit and castability of

nonprecious and "semi-precious" dental alloys. Objectives include

development of practical tests for evaluation or ranking of castability

and for refining/defining techniques for production of clinically

acceptable multiple unit fixed partial dentures. Although the technique

for producing well fitting single unit castings has been described [12],

there is no assurance that said technique will produce the desired

results with multiple unit castings.

Peripherial studies in dental ceramics involve fluorescence in

dental porcelain and manufacturing of feldspathic frits. Manufacturers

are introducing porcelain products which utilize fluorescing agents

other than undesirable uranium oxide. If satisfactory fluorescence

79
quality is achieved in these products it may not be necessary to continue said studies, however, this remains to be determined. Regarding

manufacturing of porcelain from feldspar, the high quality, low ion

feldspars are becoming more difficult to procure, hence, new sources

and/or methods of producing porcelains are desirable.

Finally, areas of activity which were being pursued at the start of

FY80 included (1) calculation on the secondary radiation dose delivered

to local oral tissues following neutron irradiation of gold prostheses

and, (2) the start of finite element modeling studies of stress in

tissue around healthy and periodontial ly involved teeth, using refined

non-linear discrete fiber modeling of the periodontal membrane. The

radiation study was brought to conclusion before final recommendations

were made by N IDR to focus on the ceramic/alloy area. The second study

was brought to the point that development of a finite element tooth

model had been made, at which time, further activity with NIDR support

was terminated.

A. Pored ain-Alloy Characterization

1. Thermal Expansion

Characterization of porcelain materials used in veneering

of dental alloys has progressed to the point that the thermal expansion

of all materials currently of interest has been determined at least

once. In Fig. 12 the thermal expansion of opaque porcelains, fired from

either 1 to 7 times is shown. Similar results are presented in Fig. 13

for body porcelains. At this time, without additional determinations

for several of the porcelain firings, systematic trends in expansion

with number of firing cycles are not apparent except for Microbond

80
Opaque and Vita VMK-68 body porcelains. Table 26 lists the same data

along with the expansion values of a number of precious and nonprecious

alloys. The significant feature that may be derived from these data is

the large difference in thermal expansion which exists between the lower

expanding alloys and the higher expanding porcelains and, between the

higher expanding alloys and the lower expanding porcelains. The differences can be seen to approach 30%. As Neil son and Tuccillo [13] had

concluded that ^7% mismatch in thermal expansion is the most which can

be safely tolerated, it is clear that not all porcelain/alloy combinations can be expected to provide an unequivocal prognosis for successful use; in fact some must fail if thermal expansions were the only

factors determining success. As will be shown further in experimental/

theoretical studies of composite split rings, other factors must enter

into operation which no doubt "save" what could be otherwise unacceptable

combinations.

2. Compatibility Index

Another important result of the thermal expansion studies

lies in the relatively large differences in excess volume which are

trapped in porcelains cooled according to manufacturers recommendations

for fabrication of dental crowns. These differences are depicted - in

Figs. 14 & 15. Because of this trapped volume, a correction must be

applied to the compatibility index proposed by Ringle [14], et al , and

modified by Fairhurst [15]. According to Fairhurst:

Tg+bJUv| q|

c rKl

dT - (1)

Where is the compatibility index, T

g

is the glass transition temperature, b is a constant, characteristic of a given porcelain, q is the

absolute cooling rate and a is the thermal expansion coefficient for

p ,a

81
annealed porcelain and is the thermal expansion coefficient for the

alloy. In a paper in review for publication [16], it is shown that as

the thermal expansion for rapidly cooled porcelain should be used, a

correction Ac must be applied to eq. 1, rendering a corrected compatibility index, C

ic = + AC

Ac is shown to be

T +bJUi | q |

AC = f

9

/

(a pc-°PA

-'T

)dT

( 2 )

(3)

where cip C is the thermal expansion coefficient for rapidly cooled porcelain and a is the value for annealed porcelain.

P i “ From Figure 16:

AC = (f)

-

T .fast \ / T ,slow

(3a)

o cool cool

and hence is related to the excess volume, A V, recovered,

AC % 3aV (4)

3. Porcelain/Alloy Split Ring Studies

The advantages of using a porcelain veneered split metal

ring for compatibility studies were presented at the 1980 AADR meeting

in Los Angeles [17]. In such studies, the change in gap is taken as a

measure of compatibility, with zero change assumed to be associated with

a state of minimum overall residual stress within the system. Features

which suggest the split ring may be a reasonable indication of compatibility are 1) the self referencing feature of gap measurements, 2) curvilinear geometry which results in generation of radial as well as tangential stress, 3) dimensions which produce curvature such that stresses

generated should be of similar magnitude to those generated in a crown.

82
4) geometry such that cooling of a crown is reasonably approximated by

cooling of the split ring, i.e. a porcelain veneer of typical restoration thickness; porcelain on one side, metal on the inner side; cooling

from edges somewhat as might be experienced around margins, 5) gap

opening or closing should be indicative of opening or closing of margins.

In order to develop a balanced study, both experimental and theoretical .approaches are being pursued, with the objective of fine tuning the

theoretical studies via use of measured material properties so that theory

and experiment are brought into the closest agreement possible. As

detailed information on stress in multilayered systems should develop

from the theoretical studies, the hypothesis of using a split ring for

a compatibility test can be reviewed critically.

At the time of this report four porcel ain/split ring systems

have been fired experimentally according to porcelain and alloy manufacturers' instructions. Three specimens of each system were tested.

The porcelains evaluated were Ceramco

9

, Vita-VMK-68*3, Biobond c, and

d e Will -Ceram , the metal alloy ring in each case was Penti Ilium . Each

series was fired vs a control ring without porcelain. The total firing

sequence consisted of conditioning the alloy, applying opaque and firing,

applying body and firing and then firing through a natural glazing cycle.

Experimental results of the net change in gap are shown in Figure 17.

Generally, the precision is ^2-3% except for the Will-Ceram/Pentillium

system. The larger standard deviation of M0% could indicate that this

particular combination of porcelain and alloy may lead to 1 ess-consistency

a Johnson & Johnson Co., E. Windsor, NY

b Vita Zahnfabrik

c Dentsply International, York, PA

d Williams Gold, Buffalo', NY

e Pentron Corp., Wallingford, CT

83
during fabrication in the dental laboratory.

Theoretical calculations of the change in gap for Ceramco or

Vita-VMK-68 on Pentillium alloy yield changes several times greater than

the experimentally observed values. This indicates that stress relief

is occurring in the porcelain at temperatures well below the glass

transition temperature. This also leads to further need to use the

compatibility index (which currently has no allowance for viscous flow)

with caution in interpreting or predicting compatibility test results.

Finally, the stress system used in the compatibility index

appears rather over simplified, although there is often great merit in

simplicity. Shown in Figure 18 is a schematic representation of bimaterial stress as derived from the Timoshenko analysis (developed to

predict strain using simplified stress analysis). In such a representation, no shear stresses can be calculated, although shear must clearly

be present due to the stress discontinuity at the interface. Also, no

radial stresses are developed in the case shown. As viscous flow must

be responsible for relief of some stress in porcelain, shear stress is

an important parameter, and should not be ignored.

B. Dental Alloy Castability

During the past year, a practical castability test has been

used to rank the castability of numerous alloys. The test, originally

designed by Eden and Dickson [18] of this laboratory, was modified by

Whitlock, also of this laboratory, to reduce the standard deviation of

test results. Essentially, a rectangular 10 x 10 segment polyester

sieve screen of 18 gage is connected to a sprue at one corner with 10

gage runner bars extending along two sides of the mesh. The test pattern

84
is invested, burned out and then cast with an alloy, using the manufacturers' instructions. After devesting, the number of complete segments which are cast is recorded and the percent used to indicate castability. An advantage of the test is that it can be used in any dental

laboratory to rank the castability of new alloys vs ones with which the

laboratory is familiar. Evaluations are still in progress, however,

several nonprecious alloys demonstrate the ability to be cast as well as

some previous metal alloys. An abstract has been prepared on this

topic, for submission for the 1981 AADR meeting. Further modifications

of the test are also being evaluated. These modifications may render

the test more sensitive to processing variables, thereby lending the

test for use as a qualtiy control procedure to evaluate optimum technique

in laboratories.

An ancillary program of casting evaluation was initiated to

investigate how well multiple unit fixed partial denture castings fit

under the conditions shown by Eden [12] to produce the optimum fit for

single unit castings. Early results show clinically unacceptable fits

for multiple units, even though single units sectioned from the bridges,

fit wel 1

.

C. Radiation Dose from Neutron Activated Dental Materials

A paper was presented at the AACR meeting in Los Angeles in

1980 [19]. This paper has been refined for publication and is currently

under review at NBS,

Conclusions are that high levels of e-plus y radiation can be

delivered to local tissues following exposure to 50 REM of thermal

neutrons. For gold the dose is 30 REM, e + y. Silver, cobalt and

indium also have high thermal neutron cross sections and these, too,

would be expected to produce substantial secondary doses in basal cells

following activation by sub-lethal neutron doses, e.g. 50 REM.

85
References

[1] Cassel , J. M., et al . , Properties and Interactions of Oral Structures

and Restorative Materials, NBSIR 79-1943 (1979); NTIS: PB80-132020.

[2] Cassel, J. M., et al . , Properties and Interactions of Oral Structures

and Restorative Materials, NBSIR 78-1573 (1978); NTIS: PB 79-

289913.

-v [3] Breslow, D. S., Baumgarten, E. and Hauser, C. R. A New Synthesis

of B-Keto Esters of the Type RCOCH^COOC^H^. J. Am. Chem. Soc. 6(5,

1286 (1944).

[4] Galat, A. A Synthesis of a,3-Unsaturated Esters. J. Am. Chem. Soc.

68, 376 (1946).

[5] Phillips, R. W.; Avery, D. R.; Mehra, R.; Swartz, M. L.; and

McCune, R.J., One-Year Observations on a Composite Resin for Class

II Restorations, J. Prosth. Dent. 26^, 68 (1971 ).

[6] Phillips, R. J., et al .

Two-Year Observations on a Composite Resin

for Class II Restorations, J. Prosth. Dent. 28, 164-69 (1972).

[7] Phillips, R. J., et al .

,

Three-Year Observations on a Composite

Resin for Class II Restorations, J. Prosth. Dent. 30, 891-97 (1973).

[8] Eyre, T. S. Wear Resistance of Metals, in "Treatise on Materials

Science and Technology", Vol. 13, ed. D. Scott, Academic Press, New

York, 1979, pp. 363-442.

[9] Atkinson, J. R.; Brown, K. J. and Dawson, D. The Wear of High

Molecular Weight Polyethylene. Part I: The Wear of Isotropic

Polyethylene Against Dry Stainless Steel in Unidirectional Motion

Transactions ASME 100, 208-18 (1978).

[10] Draughn, R. A. Compressive Fatigue Limits of Composite Restorative

Materials. J. Dent. Res. 57_, Special Issue A, Jan. 1978.

86
[11] Weber, H. and Whitlock R. P. Wettability of Dental CiCr Alloys,

Electron Microscopy, 1, 224-225 (1980).

[12] Eden, G. T. et al . ; Fit of Porcelain Fused-to-Metal Crown and

Bridge Castings. J. Dent. Res. 58 (12): 2360-2368, Dec. (1979).

[13] Neilson, J. P. and Tuccillo, J. J.; Interfacial Stress in Porcelain

Bodies Bonded to Metal Prosthestic Restorations. 0. Biomed. Mats.

Res. Symp. No. 2, (Part 2), pp 395-404. (1972).

[14] Ringle, R. D., Weber, R. L.; Anusavice, K. J.; and Fairhurst, C. W.

Thermal Expansion/Contraction Behavior of Dental Porcelain-Alloy

Systems. J. Dent. Res. 57(B), Abstract #877, 1978.

[15] Fairhurst, C. W.; Hashinger, P. T.; and Twiggs, S. W.: Thermal

Glass Transition Temperatures (T ) of Porcelain, J. Dent. Res.

59(A), Abstract #656, 1980.

[16] Tesk, J. A.; Whitlock, R. P.; Widera, G. E. 0. and Hinman, R. W.;

The Porcelain/Metal Compatibility Index and Thermal Expansion/

Contraction, Under NBS review to be submitted to Journal of Dental

Research.

[17] Whitlock, R. P.; Tesk, J. A.; Parry, E. E.; and Widera, G. E. 0.

A Porcelain Veneered Split Metal Ring for Evaluation of Dental

Porcelain-Alloy Systems. J. Dent. Res.(59)A Abstract #660, 1980.

[18] Cassel , J. M. Properties and Interactions of Oral Structures and

Restorative Materials, NBSIR 77-1397 (1977); NTIS: PB 78-275392..

[19] Tesk, J. A. and Whitlock, R. P. Intraoral Secondary Radiation

Dose from Neutron Activated Dental Materials. J. Dent. Res. 59A,

Abstract #326. (1980).

87
Invited Talks

New Monomers for Use in Dentistry. J. M. Antonucci, American Chemical

Society Meeting, Houston, Texas.

The Accelerative and Adhesive Bonding Capabilities of Surface

Active Accelerators. J. M. Antonucci, 58th Annual Meeting IADR,

Osaka, Japan.

Initiator-Accelerator Systems for Acrylic Resins and Composites.

G. M. Brauer. American Chemical Society Meeting, Houston, Texas.

Derivatives of p-N,N-Dialkylaminophenylalkanoic Acid: New Accelerators for Dental Composites. G. M. Brauer. 58th Annual Meeting,

IADR, Osaka, Japan.

Dental Alloy and Ceramic Compatibility. J. A. Tesk. International

Precious Metals Institute, Toronto, Canada.

Wear Mechanisms of Dental Composites. Wen-1 i Wu. Johnson & Johnson,

East Windsor, NJ.

Structure and Stress of Cross-linked Polymers During Polymerization.

Wen-1 i Wu. Gordon Research Conference, New London, NH.

Plastic Deformation of Doubly Oriented Crystalline Polymers.

Wen-1 i Wu, University of Massachusetts, Amherst, MA.

88
Abstracts (AADR, Los Angeles, March, 1980) on Microfilm

Biocompatible Amine Polymerization Accelerators: Para- Dimethyl aminobenzoic Acid and its Ethyl Ester. Abstract 291, J. M. Antonucci

,

R. J. Peckoo, C. Schruhland E. E. Toth.

In Vitro Wear Measurements on Dental Materials. Abstract 327,

J. E. McKinney.

Intraoral Secondary Radiation Dose from Neutron Activated Dental Materials.

Abstract 326, J. A. Tesk and R. P. Whitlock .

A Porcelain Veneered Split Metal Ring for Evaluation of Compatibility

of Dental Porcelain-Alloy Systems. Abstract 660, R. P. Whitlock1

, J. A. Tesk

E. E. Parry1 and G. E. 0. Widera?

Theoretical Stress Analysis of Porcelain Veneered Split Metal Ring

for Evaluation of Compatibility of Porcelain-Alloy System. Abstract 652,

G. E. 0. Widera2

, J. A. Tesk and R. P. Whitlock1

.

Abstracts (IADR, Osaka, Japan, June 1980) on Microfilm

The Accelerative and Adhesive Bonding Capabilities of Surface-Active

Accelerators. Abstract 195, J. M. Antonucci, D. N. Misra3 and R. J. Peckoo.

Derivatives of p-N,N-Dial kyl ami nophenyl aklanoic Acid: New Accelerators for

Dental Composites. Abstract 194. G. M. Brauer and J. W. Stansbury.

Observations of Significant Differences in Thermal Expansion Characteristics

of Dental Porcelain. Abstract 40, R. P. Whitlock1

, J. A. Tesk, E. E. Parry1

, and G. E. 0 Widera2

.

1 Research Associate, U. S. Navy

2 University of Illinois, Chicago, IL

3 Research Associate, American Dental Association

89
Papers Published (FY80)

Storage Stability of Dental Composites. G. M. Brauer, N. Petrianyk

and D. J. Termini. J. Dent. Res 58(8) 1800 (1979).

New Initiator System for Dental Resins Based on Ascorbic Acid.

J. M. Antonucci, C. L. Grams and D. J. Termini. J. Dent. Res. 58(9) : 1887-1899 (1970).

Bonding of Acrylic Resins to Dentin with 2-Cyanoacrylate Esters.

G. M. Brauer, J. A. Jackson and D. J. Termini. J. Dent. Res. 58(9) : 1900-1907 (1979).

New Amine Accelerators for Composite Restorative Resins. G. M. Brauer,

D. M. Dulik, J. M. Antonucci, D. J. Termini and H. Argentar1

, J. Dent. Res.

58(9) :1 994-2000 (1979).

Fit of Porcelain Fused-to-Metal Crown and Bridge Castings. G. T. Eden 2

, 0. M. Franklin2

, J. M. Powell 3, Y. Ohta4 and G. Dickson. J. Dent. Res.

58(12) :2360-2368 (1979).

Isocyanato Urethane Methacrylates Derived from Hydroxyethyl Methacrylate.

J. M. Antonucci, G. M. Brauer and D. J. Termini. J. Dent. Res. 59(1

)

: 35-43

(1980).

Durability of the Bond Between Bone and Various 2-Cyanoacrylates in an Aqueous Environment. G. M. Brauer, J. W. Kumpula, D. J. Termini and

K. M. Davidson. J. Biomed. Mater. Res. l_3:593-606 (1979).

Initiator-Accelerator Systems for Acrylic Resins and Composites.

G. M. Brauer. Org. Coatings and Plas. Chem. 42^:321-326 (1980).

New Monomers for Use in Dentistry. J. M. Antonucci. Org. Coatings and

Plas. Chem. 42; 198-203 (1980).

Wettability of Dental Ni-Cr Alloys. H. Weber5 and R. P. Whitlock6

, Electron Microscopy 1_, 224 (1980.

1 Research Associate, American Dental Association

2 Research Associate, U. S. Navy, 1975-77

3 Research Associate, U. S. Air Force, 1972-77

4 Guest Worker, Aidhi-Gukium University, Japan

5 University of Dusseldorf, Germany, 1978-79

6 Research Associate, U. S. Navy, 1977-79

90
The following manuscripts are under NBS editorial review or have been

submitted for publication :

Effect of Diluent Monomer on the Physical Properties of BIS-GMA Based

Composites. D. Dulik, R. Bernier and G. M. Brauer.

4-N,N-Dimethylaminophenylethanols, Alkanoic Acids and Esters: New

Accelerators for Dental Composites. G. M. Brauer, J. W. Stansbury and

J. M. Antonucci.

Biocompatible Amine Polymerization Accelerators: Para-Dimethyl aminobenzoic Acid and its Ethyl Ester. J. M. Antonucci, R. J. Peckoo, C. Schruhl

and E. E. Toth.

In Vitro Wear Measurements on Dental Materials. J. E. McKinney.

Intraoral Secondary Radiation Dose from Neutron Activated Dental

Materials. J. A. Tesk, R. P. Whitlock1 and A. Holmes.

The Accelerative and Adhesive Bonding Capabilities of Surface-Active

Accelerators. J. M. Antonucci, D. N. Misra2 and R. J. Peckoo.

The Desirability of Using Radiopaque Plastics in Dentistry - A Status

Report. G. M. Brauer.

New Monomers for Use in Dentistry. J. M. Antonucci.

Initiator-Accelerator Systems for Acrylic Resins and Composites.

G. M. Brauer.

Consideration of Some Factors Influencing Compatibility of Dental Porcelain

and Alloys. R. P. Whitlock1

, J. A. Tesk, G. E. 0 Widera3

, A. Holmes

and E. E. Parry .

An Evaluation of the Porcelain/Metal Compatibility Index. J. A. Tesk,

R. P. Whitlock1

, G. E. 0. Widera3 and R. W. Hinman1

.

An Amine Accelerator for Color-free Curing of Autopolymerizable Methyl

Methacrylate Denture Systems. H. Argentar2

, J. A. Tesk and E. E.

- Parry1

.

The Porcelain/Metal Compatibility Index and Thermal Expansion/Contraction

J. A. Tesk. R. P. Whitlock1

, G. E. 0. Widera3 and R. W. Hinman 1

Consideration of Some Factors Influencing Compatibility of Dental Porcelains

and Alloys; Part I. Characterization. R. P. Whitlock1

, J. A. Tesk,

G. E. 0. Widera 3

, A. Holmes and E. E. Parry1

.

Consideration of Some Factors Influencing Compatibility of Dental Porcelains

and Alloys; Part II. Theoretical and Experimental Compatibility. J. A. Tesk,

R. P. Whitlock1

, G. E. 0. Widera 3

, A. Holmes and E. E. Parry1

.

Solders and Fluxes. J. A. Tesk. Pending publication in "Dentists' Desk

Reference" to be published by Council on Dental Materials, Instruments and

Equipment, American Dental Association.

1 Research Associate, U. S. Navy 91

2 Research Associate, American Dental Association

3 University of Illinois, Chicago
Abstracts Submitted for IADR/AADR Meeting, March 81, Chicago, IL

Effects of Porcelain/Alloy Interfacial Diffusion Zones on Thermo-mechanical

Strain. J. A. Tesk, R. W. Hinman 1

, G. E. 0. Widera2, J. M. Cassel , and

A. D. Holmes.

Fit of Multiple Unit Fixed Partial Denture Castings. R. W. Hinman 1

, J. A. Tesk, E. E. Parry1

.

Cements from 2,5-Dimethoxyphenol and Zinc Oxide. J. W. Stansbury, H. Argentar3 and G. M. Brauer.

Degree of Polymerization of Dental Resins by Differential Scanning Calorimetry.

J. M. Antonucci and E. E. Toth.

Influence of Chemicals on In Vitro Wear of Dental Restorative Composites,

W. Wu and J. E. McKinney.

Theoretical /Experimental Studies of Stress Compatibility in Porcelain-Veneered

Split Metal Rings. G. E. 0. Widera2

, J. A. Tesk, R. P. Whitlock1

, R. W. Hinman 1

. E. E. Parry 1

.

Application of Silane Coupling Agent to Inorganic Components of Composites.

T. M. Chen

4

and G. M. Brauer.

Peroxy Esters and Hydroperoxides as Initiators for Composite Resins. G. M. Brauer

and J. W. Stansbury.

Relationship Between Subsurface Damage and Wear of Dental Restorative Composites.

J. E. McKinney and W. Wu.

Effect of Hygroscopic Diluents on the Properties of Cured Composites. K. Dermann,

N. W. Rupp3 and G. M. Brauer.

A Practical Test to Evaluate the Castability of Dental Alloys. R. P. Whitlock , R. W. Hinman 1

, G. T. Eden1, J. A. Tesk, G. Dickson, and E. E. Parry1

.

Temperature Dependence of Shear Viscosity for Several Dental Porcelains, J. A. Tesk,

R. W. Hinman 1

, R. P. Whitlock1

, A. D. Holmes, E. E. Parry1

.

1 Research Associate, U. S. Navy

2 University of Illinois, Chicago

3 Research Associate, American Dental Association

4 Guest Worker, Food & Drug Administration

5 Guest Worker, Free University of Berlin, Germany

92
NBS-114A (rev. 2-ec) U.S. DEPT. OF COMM.

BIBLIOGRAPHIC DATA

SHEET (See instruction s)

1. PUBLICATION OR

REPORT NO.

NBSIR 8G- 1 o3

2. Performing Organ. Report No. 3. Publication Date

4. TITLE AND SUBTITLE

Properties and Interactions of Oral Structures and Restorative Materials

5. author(S) James M. Cassel , John A. Tesk, Gerhard M. Brauer, Joseph M. Antonucci

Wen-li Wu, John E. McKinney, R. P. Whitlock, R. W. Hinman

6. PERFORMING ORGANIZATION (If joint or other than NBS, see instructions)

NATIONAL BUREAU OF STANDARDS

DEPARTMENT OF COMMERCE

WASHINGTON, D.C. 20234

7. Contract/Grant No. Y01 - DE -4001 5-1

1

8. Type of Report & Period Covered

Annual Report

10/1/79 - 9/30/80

9. SPONSORING ORGANIZATION NAME AND COMPLETE ADDRESS (Street. City. State. ZIP)

National Institute of Dental Research

National Institutes of Health

Westwood Building, Room 506

Bethesda, MD 20205

10.

SUPPLEMENTARY NOTES

Document describes a computer program; SF-185, FIPS Software Summary, is attached.

11.

ABSTRACT ( A 200-word or less factual summary of most significant information. If document includes a significant

bi bl iography or literature survey, mention it here)

Development of more efficient, less toxic polymerization accelerators indicates

much promise for the generically biocompatible 4,4,N-diethylaminophenylacetic acid

which is reactive at four fold reduced concentration relative to currently used

amines. Raman, IR and u NMR spectroscopy and DSC are being compared for investigation of dental resin polymerization. Solvent carrier and amine catalysts have

been shown to influence stability of silane-silica bonding in composites. A stateof-the-art report on radiopaque plastics in dentistry was prepared. A silver staining technique developed to assist investigation of mechanisms of degradation and

wear in composite restorations yields useful information on subsurface microdefects

in iji vivo and im vitro worn specimens. Jjn vitro wear with a pin-on-disc machine

indicates increased wear of a composite is generated by going from a very hard

(apatite) pin to a softer (stainless steel) pin. A wear test placing greater

emphasis on shear forces generated via food particle interplay with teeth has been

developed. With thermal expansion measurements, significant differences in the excess volume retained on cooling porcelains fired as per manufacturers' recommendatior

were noted. Gap and shape changes in a porcelain veneered to alloy split ring offer

promise for determining compatibility of porcelains for alloys.

12.

KEY WORDS (Six to twelve entries; alphabetical order; capitalize only proper names; and separate key words by semicolons)

Accelerator; alloy; base metal; casting; composite; cyanoacrylate;

dental alloy; initiator; resin; wear.

13.

AVAILABILITY

J^] Uni i mi ted

|_j For Official Distribution. Do Not Release to NTIS

[ H Order From Superintendent of Documents, U.S. Government Printing Office, Washington, D.C. 20402.

Q3] Order From National Technical Information Service (NTIS), Springfield, VA. 22161

14. NO. OF

PRINTED PAGES

15. Price

USCOMM-DC 6043-P80

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