WO2001024724A1 - Method for curing a dental composition using a light emitting diode - Google Patents

Method for curing a dental composition using a light emitting diode Download PDF

Info

Publication number
WO2001024724A1
WO2001024724A1 PCT/US2000/027609 US0027609W WO0124724A1 WO 2001024724 A1 WO2001024724 A1 WO 2001024724A1 US 0027609 W US0027609 W US 0027609W WO 0124724 A1 WO0124724 A1 WO 0124724A1
Authority
WO
WIPO (PCT)
Prior art keywords
dental
light emitting
emitting diode
curing
radiation
Prior art date
Application number
PCT/US2000/027609
Other languages
French (fr)
Inventor
Noureddine Melikechi
Ranjit Dinkar Pradhan
Original Assignee
New Photonics, Llc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by New Photonics, Llc filed Critical New Photonics, Llc
Priority to AU10740/01A priority Critical patent/AU1074001A/en
Publication of WO2001024724A1 publication Critical patent/WO2001024724A1/en

Links

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61CDENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C5/00Filling or capping teeth
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61CDENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C19/00Dental auxiliary appliances
    • A61C19/003Apparatus for curing resins by radiation
    • A61C19/004Hand-held apparatus, e.g. guns

Definitions

  • the present invention relates to curing photo-curable dental compositions
  • the present invention provides a method to cure dental compositions using a light-emitting diode (LED) as a source of curing radiation placed proximate to the composition to be cured
  • LED light-emitting diode
  • Certain polymeric materials useful in the field of dentistry for adhesion, sealing and restoration may be cured or hardened upon exposure to a source of radiation
  • photoactive materials are known as "photo-curable dental compositions" and generally harden when exposed to radiation having wavelengths in the visible range
  • Photo-cured dental compositions are convenient for use by a dentist because the curing process can be initiated when the dental composition has been accurately placed in its proper position
  • a source of radiation energy positioned proximate to the material to be hardened, for example an appropriate amount of composition placed inside a tooth cavity, is activated to initiate polymerization and subsequent curing of the composition to secure the repair
  • Photo-cured dental compositions were initially hardened by the application of concentrated beams of ultraviolet (UN) radiation
  • UN radiation concentrated beams of ultraviolet
  • dental guns and other apparatuses for producing concentrated beams of UV radiation were developed See U S Patent ⁇ os 4,112,335 and 4,229,658, for example Later, visible light curable dental compositions were used and dental radiation guns for producing concentrated visible light were provided like that disclosed in U S Pat No 4,385,344
  • a relatively high divergence about 25 degrees of the light beam from such visible light sources reduces penetration into the tooth structure, leading to their relative inefficiency and unreliability for photo-curing dental composition that are thicker than about two millimeters
  • Photo-curable dental materials have also been developed that are hardened by exposure to radiant energy in a preselected spectral range
  • a photo-activated chemical reaction in many photo-curable dental materials is initiated by application of a high intensity blue light having a wavelength of 400-500 nanometers
  • a reflector is coated to reflect only visible light
  • the filters are selected to substantially block non-visible radiation and visible light other than blue light in the range of 400-500 nanometers, in order to produce the desired range of radiation, as shown for example in U.S. Pat. No. 5,147,204.
  • Laser-based radiation sources have also been employed, using for example, a Nd YAG laser producing radiation at a wavelength of about 1060 nanometers, in combination with a frequency doubling material as disclosed for example in U.S. Pat. No. 5,885,082.
  • a laser source In the instance that a laser source is used, the beam must be de-focused to cover the area being cured and this is done by varying by hand the distance between the dental composition and the laser dental gun.
  • the area illuminated by conventional blue-filtered metal-halide radiation is usually in the range of about a 1/2 -inch diameter circle and over a typical curing cycle of about 60 seconds.
  • the relatively high energy output and beam divergence of such dental guns leads to the possibility of increased heating of the pulp tissue which is sensitive to small changes in temperature.
  • United States Patent 4,385,344 discloses a dental gun device for production of light in the low visible range for photo-curing dental compositions, the device comprising a tungsten halogen lamp with a concentrating reflector which reflects visible light and passes middle and far infrared wavelengths.
  • a dichroic heat reflecting filter which passes light from 400 to 700 nm and reflects energy in the visible red and near infrared wavelengths back to the lamp envelope, enhances lamp halogen cycle efficiency.
  • the dichroic heat reflecting filter is followed by a dielectric filter which provides a high efficiency bandpass at the desired visible range.
  • a fiber optic light guide is positioned to receive the focused and filtered light and to transmit it to a reduced surface light applying tip at the end of the handpiece.
  • the fiber light guide is encased in a specially designed sheathing which provides protection to the optical fibers and carries two electrical conductors which are connected between a control switch on the handpiece and the power supply for the lamp.
  • United States Patent 5, 147,204 is representative of conventional blue-light filtered dental guns.
  • This patent discloses a blue light emitting apparatus for curing photo-curable dental material including a handpick having a housing, a depending handle and a detachable light guide. The light guide is received in a head connected to the housing.
  • a source of tungsten-halogen light is coupled to the housing, and a light guide is detachably connected to the head for communication with the source of light. Since the tungsten-halogen light produces the entire visible light spectrum as well as some non-visible radiation, a reflector is coated to generally reflect only visible light, and a blue-pass filter and a heat filter are selected to substantially block non-visible radiation and visible light other than blue light in the range of 400-500 nanometers.
  • United States Patent 5,885,082 is representative of the use of pulsed laser radiation having a selected wavelength for performing a variety of dental procedures, including curing and hardening of a dental composition containing hydroxyapatite and phosphoric acid.
  • the use of laser radiation for curing employs a housing provided with an optical fiber coupled to a source of monochromatic light, such as an Nd YAG laser operating at a wavelength of 1060 nanometers.
  • the optical fiber directs light radiation onto a curved mirror which deflects the radiation onto the receiving end of a further optical fiber.
  • a frequency doubling material influences the laser radiation so that such a laser-based dental gun has the capability of applying either 1060 nanometers or 532 nanometers radiation to the area to be treated.
  • cooling water is disclosed as being sprayed onto the tooth in the vicinity of the spot which is being irradiated, especially when radiation at 532 nanometers is applied.
  • a further disadvantage of the use of laser radiation is de-focusing the laser beam to be coextensive with the surface of filling composition by varying by hand the spacing between the laser dental gun and the tooth surface.
  • a dental composition curing method has been developed that consists of exposing the dental composition to be hardened to radiation from a light emitting diode having output wavelengths selected to photo-activate a hardening chemical reaction within the target composition.
  • the inventors have surprisingly discovered that the radiation beam from a LED provides the same depth of cure as achieved by a conventional blue-light filtered dental gun, even though the LED irradiation intensity is between about 50% to 80% lower for the same exposure time.
  • an energy density of about 25 mW/cm 2 at the target composition is required for a LED-based dental gun vs.
  • an energy density of about 53 mW/cm 2 required for a conventional blue-light dental gun an energy density of about 53 mW/cm 2 required for a conventional blue-light dental gun.
  • an energy density of about only 38 mW/cm 2 at the target composition is required for a LED-based dental gun vs. about 200 mW/cm 2 required for a conventional blue-light dental gun.
  • the amount of shrinkage that occurs during the curing process is about 7% lower when a LED-based dental gun of the present invention is employed instead of a conventional blue light dental gun.
  • the smaller size of a LED permits a smaller dental gun to be employed so that the level of thermal discomfort experienced by a patient is decreased.
  • the degree of heating has been measured and found to be about 8% less when the LED-based dental gun of the present invention is employed instead of a conventional blue light dental gun.
  • the failure mode of operation with a LED is catastrophic in nature so that energy output remains essentially constant during use.
  • the present dental composition curing method using a low-cost LED radiation source is more efficient for affecting dental composition curing than the conventional use of filtered white light or laser radiation, thereby providing significant benefits to both dentist and patient alike.
  • FIG. 1 is a schematic view of an apparatus suitable for performing the dental composition curing method of the present invention using a LED radiation source;
  • FIG. 2 is a schematic view of a mercury dilatometer testing method suitable for evaluation of shrinkage rate and heating using the LED radiation dental composition curing method of the present invention
  • FIG. 3 is a graphical representation of temperature measurements obtained with the dental composition curing method of the present invention using a LED radiation source
  • FIG. 4 is a graphical representation of depth of cure measurements obtained with the dental composition curing method of the present invention using a LED radiation source.
  • FIG. 1 shows schematically the elements of a dental curing apparatus 10 suitable for performing the dental composition curing method of the present invention using a LED radiation source.
  • the curing apparatus 10 comprises an elongated handle 12 shaped for operator convenience in positioning a light emitting diode (LED) 14 proximate a target dental composition 16 so that curing radiation emitted from the LED 14 is directly incident upon the dental composition target 16.
  • LED 14 may be attached to handle 12 by any of several methods, including clamping, receiving in a recess, gluing and the like.
  • LED 14 is activated by means of a pair of low voltage power wires 18 illustrated for convenience as being contained within handle 12.
  • Wires 18 are joined by means of a suitable connector 20 and power cord 22 to a programmable power supply 24 selected to provide the desired power parameters.
  • LED 14 When activated, LED 14 irradiates radiation energy, illustrated by arrow 26 onto the target material 16. If desired, a conventional radiation radiometer, not illustrated, may be used to ensure that power output from the LED 14 is within normal operating ranges.
  • Exemplary LEDs 14 useful in practicing the present invention include Panasonic's "LED Blue Clear” 1500 millicandela T 1-3/4, LNG992CFBW and similar devices commercially available from Hewlett Packard and Toshiba Such LEDs emit radiation in the range from about 440 to about 500 nanometers with a power output of about 1500 millicandela
  • a programmable power supply 24 employed in conjunction with the above identified Panasonic LED is well known in the industry, specifically a model PS 281 produced by Tektronix was to obtain the results described below
  • Dental compositions 16 suitable as a filling material for cavities in teeth are well known in the art and may be obtained by mixing liquid phosphoric acid, water and a paste composed of a ceramic and hydroxyapatite, in a proportion to form a suitably workable composition
  • a typical dental composition has a liquid component of about 40% phosphoric acid in water and a paste component of about 80% ceramic and 20% hydroxyapatite Increased amounts of hydroxyapatite demand more energy to cure the composition
  • the ceramic component may be composed of corderite, silica or silicium oxide, or aluminum oxide, for example
  • the powder components will have the grain sizes normally used for dental filling materials
  • the dental curing apparatus 10 was operated at an energy output level of about 25 mW/cm 2 and was stationed at a distance of about 7mm ⁇ 2mm above the dental composition target 16 for a pe ⁇ od of 60 seconds
  • the conventional SpectrumTM 200R Cu ⁇ ng Unit was operated at an energy output level of about 300 mW/cm 2 at the target 16 for a pe ⁇ od of 60 seconds
  • Depth of cure was measured in accordance with the established industry standard depth of cure measurement technique defined by the International Organization for Standardization as ISO DIS 4049, 1998 This technique employs a 7 mm thick stainless steel mold having a 4 0 mm diameter cylinder that extends through the mold The thickness of the mold is 2mm greater than twice the maximum depth of cure claimed
  • the dental composition to be cured in this instance, the Caulk TPH Spectrum Shade A 3 5 composition, is tightly filled into the cylinder and the open ends of the cylinder are covered with a polyester film
  • One end of the cylinder is irradiated with curing radiation under test conditions and then the uncured mate ⁇ al is removed from the cylinder
  • the cured cylinder is removed from the mold and the cured height is measured with a micrometer
  • the depth of cure is recorded as half the height of the cured cylinder and the test is repeated twice As described above, both radiation sources, the dental cu ⁇ ng apparatus 10 and the SpectrumTM 200R Cu ⁇ ng Unit were used to cure the cylinder of dental composition
  • Depth of cure for a 4 mm diameter cylinder mold was then measured and determined to be 1 5 ⁇ 0 1 mm for the LED radiation curing apparatus 10 at 25 mW/cm 2
  • the LED radiation cu ⁇ ng apparatus 10 was operated at 38 mW/cm 2 and the conventional blue-light radiation cu ⁇ ng gun was operated at about 200mW/cm 2
  • the LED curing apparatus 10 may be operated at a much lower irradiation intensity than conventional dental guns to obtain an essentially equivalent or greater depth of cure
  • the degree of shrinkage associated with polymerization with a polymer dental composition was measured in accordance with an established ADAHF industry standard technique using a dilatometer 30 like that illustrated in FIG 2
  • a dab of dental composition 14 with approximately 0 1 gram mass is placed on a standard microscope slide 32 that has been tared on a 4-d ⁇ g ⁇ t balance
  • the composition 14 is spread on the slide 32 with a spatula, keeping the composition less than 1 5 mm thick and less than 5 mm in diameter to assure complete curing
  • the weight of the composition is recorded to 4 decimals
  • An open glass measurement tube 34 having a cup-shaped end section 36 is positioned with the cup-shaped end section 36 facing upwards and the microscope slide 32 with dental composition 14 is inverted over the cup so that the composition is centered in the cup.
  • the slide 32 is clamped secured to the measurement tube with a clamp 38, rotated 180-degrees to the orientation shown in FIG. 2 and filled with mercury 40.
  • a prescribed linear displacement transducer 42 a Lucas Shaevitz LVDT, assembly is slowly lowered into the tube 34 until it rests on top of the glass measurement tube 34 with its plunger 44 floating on the mercury 40.
  • a prescribed thermistor 46, an Omega 44133 thermistor is built into the cup-shaped section 36 of the measurement tube 34 and positioned to be in contact with the mercury 40 surrounding the composition 14 being tested.
  • the LVDT assembly 42 and the Omega 44133 thermistor 46 are connected to a control box (not shown) and interfaced to a computer (not shown).
  • Both radiation sources, the dental curing apparatus 10 and the conventional SpectrumTM200R Curing Unit were used to irradiate the dental composition as illustrated in FIG. 2 for 60 seconds at output power levels of 25mw/cm 2 and 300 mw/cm 2 , respectively.
  • a software program developed by the ADAHF residing within the computer is used to acquire and analyze data related to an expansion of the mercury from the LVDT and mercury temperature changes registered by the thermistor.
  • the change in mercury level results from two sources: (1) shrinkage in dental composition due to polymerization, and (2) expansion in mercury due to irradiation induced heating.
  • the software program calculates the expansion in mercury from the thermistor temperature data.
  • the overall volume change is calculated based on LVDT data. From the combination of these data, the shrinkage within the dental composition may be calculated once the final density of cured polymer is provided. Final density of the polymer is measured using a Mettler Toledo AT 261 balance in combination with a Mettler Toledo 210485 density determination kit.
  • the increase in temperature associated with a 60-second exposure for achieving a depth of cure of 1.5 mm was measured using the ADAHF dilatometer described above.
  • both radiation sources, the dental curing apparatus 10 and the conventional SpectrumTM 200R Curing Unit were used to expose dental composition target 16 for 60 seconds at output power levels measured to be 25 mW/cm 2 for the LED curing apparatus 10 and 450 mw/cm 2 at the output end of the conventional blue-light dental gun.
  • Due to the relatively high divergence of the conventional dental gun its 300 mW/cm 2 output irradiation corresponds to an energy density of about 53 mW/cm 2 at the dental target 16.
  • the energy density of the LED curing apparatus 10 remains about 25 mW/cm 2 due to the low divergence of the LED beam.
  • a dental composition having a different formulation from the one in the Evidences may be employed. It is known from the literature that Axis and Thermoresin LC II dental compositions may be cured with both UV and visible radiation while another composition Dentacolor is cured substantially by visible light [J Oral Rehabil 1998 Oct, 25(10) 770-5] To confirm the effectiveness of the present invention, the depth of cure of a second commercially available dental composition known as Marathon V available from DenMat® was also evaluated using the LED-based cu ⁇ ng method of the present invention in the aforedescribed ISO DIS 4049 testing method.
  • FIG. 4 illustrates the depth of cure as a function of the distance of the LED from the dental composition with a blue-light Panasonic LED with a curing time of 60 sec.
  • Fig. 4 shows that using the present inventive method provides a relatively constant depth of cure as long as the LED is positioned within a distance of 8mm from the dental composition, a result of the low divergence of the LED beam in comparison to the highly divergent radiation generated within a conventional filtered light dental gun.
  • Optimum distance from the dental composition target is seen to be in the range of 1-8 mm for the LED curing apparatus 10.
  • a light emitting diode having other than "clear blue" wavelengths may be employed as long as the dental composition may be cured by the application of corresponding radiation. It is known from the literature that microfilled and hybrid composition materials designed for prosthetic veneer may be cured with different types of light, in particular both xenon light and metal halide light sources. Depending on the choice of light source and the choice of dental composition, an increased exposure duration increases the depth of cure for all combinations [J Oral Rehabil 1998 May; 25 (5):348-52]. Accordingly the present invention may be practiced using any LED having its wavelength selected to provide radiation energy in the effective curing range for the composition being employed.
  • the duration of radiation exposure with a LED as disclosed in the present application may be increased to accomplish a minimum acceptable depth of cure, depending on the selection of LED radiation wavelength and the selection of dental composition. Accordingly, the present invention is not limited to those embodiments precisely shown and described in the specification but only by the following claims.

Abstract

A dental composition curing method and device (10) for exposing a dental composition to a beam of radiation (26) emitted by a light-emitting-diode (LED) (14) positioned proximate the composition, LED radiation being more efficient than the conventional use of filtered white light. The device also includes a handle (12) and power supply (24).

Description

METHOD FOR CURING A DENTAL COMPOSITION USING A LIGHT EMITTING DIODE
Field of the Invention
The present invention relates to curing photo-curable dental compositions In particular, the present invention provides a method to cure dental compositions using a light-emitting diode (LED) as a source of curing radiation placed proximate to the composition to be cured
Description of the Related Art
Certain polymeric materials useful in the field of dentistry for adhesion, sealing and restoration may be cured or hardened upon exposure to a source of radiation Such photoactive materials are known as "photo-curable dental compositions" and generally harden when exposed to radiation having wavelengths in the visible range Photo-cured dental compositions are convenient for use by a dentist because the curing process can be initiated when the dental composition has been accurately placed in its proper position A source of radiation energy positioned proximate to the material to be hardened, for example an appropriate amount of composition placed inside a tooth cavity, is activated to initiate polymerization and subsequent curing of the composition to secure the repair
Photo-cured dental compositions were initially hardened by the application of concentrated beams of ultraviolet (UN) radiation In order to provide such UN radiation, dental guns and other apparatuses for producing concentrated beams of UV radiation were developed See U S Patent Νos 4,112,335 and 4,229,658, for example Later, visible light curable dental compositions were used and dental radiation guns for producing concentrated visible light were provided like that disclosed in U S Pat No 4,385,344 However, a relatively high divergence about 25 degrees of the light beam from such visible light sources reduces penetration into the tooth structure, leading to their relative inefficiency and unreliability for photo-curing dental composition that are thicker than about two millimeters
Photo-curable dental materials have also been developed that are hardened by exposure to radiant energy in a preselected spectral range Typically, a photo-activated chemical reaction in many photo-curable dental materials is initiated by application of a high intensity blue light having a wavelength of 400-500 nanometers Since the light sources employed typically produce the entire visible light spectrum as well as some non-visible radiation, a reflector is coated to reflect only visible light, and the filters are selected to substantially block non-visible radiation and visible light other than blue light in the range of 400-500 nanometers, in order to produce the desired range of radiation, as shown for example in U.S. Pat. No. 5,147,204. Laser-based radiation sources have also been employed, using for example, a Nd YAG laser producing radiation at a wavelength of about 1060 nanometers, in combination with a frequency doubling material as disclosed for example in U.S. Pat. No. 5,885,082. In the instance that a laser source is used, the beam must be de-focused to cover the area being cured and this is done by varying by hand the distance between the dental composition and the laser dental gun.
There are several disadvantages in using light curing apparatuses of the prior art like those discussed above. Commercially available dental light guns often include an elongated, slender light guide such as a bundle of optical fibers having a free end that can be positioned close to the photo- curable material in order to direct light to the material from a light source located outside the oral cavity. Thus, because of the relatively large size of the dental gun within a patient's mouth, a degree of physical discomfort is introduced to the patient as well as to the dentist who must hold the gun steady for about one minute.
Second, the area illuminated by conventional blue-filtered metal-halide radiation is usually in the range of about a 1/2 -inch diameter circle and over a typical curing cycle of about 60 seconds. The relatively high energy output and beam divergence of such dental guns leads to the possibility of increased heating of the pulp tissue which is sensitive to small changes in temperature.
In addition, when dental compositions are cured in place within a cavity for instance, after curing an amount of shrinkage of about 2.5% occurs leaving a gap within the area being treated; such shrinkage is so deleterious that any small reduction in shrinkage is desirable.
Furthermore, in tests of cure depth uniformity of standardized compositions, it was found that a high percentage (46%) of curing lights used in private dental offices are unsuitable for use when tested against manufacturer's recommendations using a curing radiometer or a heat radiometer, due in part to the loss of output of the light source in use [J Dent 1999 Mar;27(3):235- 41]. Finally, due to the expenses of combining a laser or metal-halide radiation source, focusing elements, power sources, etc., significant expenses are involved in purchasing and using dental guns. Conventional dental curing devices are therefore seen to have shortcomings including uncomfortable use, unreliable curing and relatively high expense.
United States Patent 4,385,344 discloses a dental gun device for production of light in the low visible range for photo-curing dental compositions, the device comprising a tungsten halogen lamp with a concentrating reflector which reflects visible light and passes middle and far infrared wavelengths. A dichroic heat reflecting filter which passes light from 400 to 700 nm and reflects energy in the visible red and near infrared wavelengths back to the lamp envelope, enhances lamp halogen cycle efficiency. The dichroic heat reflecting filter is followed by a dielectric filter which provides a high efficiency bandpass at the desired visible range. A fiber optic light guide is positioned to receive the focused and filtered light and to transmit it to a reduced surface light applying tip at the end of the handpiece. The fiber light guide is encased in a specially designed sheathing which provides protection to the optical fibers and carries two electrical conductors which are connected between a control switch on the handpiece and the power supply for the lamp.
United States Patent 5, 147,204 is representative of conventional blue-light filtered dental guns. This patent discloses a blue light emitting apparatus for curing photo-curable dental material including a handpick having a housing, a depending handle and a detachable light guide. The light guide is received in a head connected to the housing. A source of tungsten-halogen light is coupled to the housing, and a light guide is detachably connected to the head for communication with the source of light. Since the tungsten-halogen light produces the entire visible light spectrum as well as some non-visible radiation, a reflector is coated to generally reflect only visible light, and a blue-pass filter and a heat filter are selected to substantially block non-visible radiation and visible light other than blue light in the range of 400-500 nanometers.
United States Patent 5,885,082 is representative of the use of pulsed laser radiation having a selected wavelength for performing a variety of dental procedures, including curing and hardening of a dental composition containing hydroxyapatite and phosphoric acid. The use of laser radiation for curing employs a housing provided with an optical fiber coupled to a source of monochromatic light, such as an Nd YAG laser operating at a wavelength of 1060 nanometers. The optical fiber directs light radiation onto a curved mirror which deflects the radiation onto the receiving end of a further optical fiber. A frequency doubling material influences the laser radiation so that such a laser-based dental gun has the capability of applying either 1060 nanometers or 532 nanometers radiation to the area to be treated. It is significant that cooling water is disclosed as being sprayed onto the tooth in the vicinity of the spot which is being irradiated, especially when radiation at 532 nanometers is applied. A further disadvantage of the use of laser radiation is de-focusing the laser beam to be coextensive with the surface of filling composition by varying by hand the spacing between the laser dental gun and the tooth surface. Accordingly, from a study of the different approaches taken in the prior art to the problems presented by the necessity for reliably providing a minimum essential amount of curing radiation without undue heating or other discomfort to a patient or dentists, there remains a need for an improved approach to dental polymer curing that is compatible with existing polymeric compositions and which involves smaller, easier to use and less expensive devices that operate with a smaller amount of applied radiation energy, yielding lower temperatures, and less composition shrinkage. A further need is the availability of a light source that has insignificant loss of output during use.
BRIEF SUMMARY OF THE INVENTION
The disadvantages discussed above within the prior art may be fully or at least partially overcome by using the apparatus and methods of this invention. A dental composition curing method has been developed that consists of exposing the dental composition to be hardened to radiation from a light emitting diode having output wavelengths selected to photo-activate a hardening chemical reaction within the target composition. The inventors have surprisingly discovered that the radiation beam from a LED provides the same depth of cure as achieved by a conventional blue-light filtered dental gun, even though the LED irradiation intensity is between about 50% to 80% lower for the same exposure time. In particular, to achieve a 1.5 mm depth of cure, an energy density of about 25 mW/cm2 at the target composition is required for a LED-based dental gun vs. an energy density of about 53 mW/cm2 required for a conventional blue-light dental gun. Remarkably, in the instance of a 2 mm depth of cure, an energy density of about only 38 mW/cm2 at the target composition is required for a LED-based dental gun vs. about 200 mW/cm2 required for a conventional blue-light dental gun.
Even more unexpectedly, it has been discovered that the amount of shrinkage that occurs during the curing process is about 7% lower when a LED-based dental gun of the present invention is employed instead of a conventional blue light dental gun. In addition, the smaller size of a LED permits a smaller dental gun to be employed so that the level of thermal discomfort experienced by a patient is decreased. Even further, for irradiation intensities yielding a 1.5 mm depth of cure, the degree of heating has been measured and found to be about 8% less when the LED-based dental gun of the present invention is employed instead of a conventional blue light dental gun. Even furthermore, the failure mode of operation with a LED is catastrophic in nature so that energy output remains essentially constant during use. Thus, the present dental composition curing method using a low-cost LED radiation source is more efficient for affecting dental composition curing than the conventional use of filtered white light or laser radiation, thereby providing significant benefits to both dentist and patient alike.
BRIEF DESCRIPTION OF THE DRAWINGS
The invention will be more fully understood from the following detailed description thereof taken in connection with the accompanying drawings which form a part of this application and in which:
FIG. 1 is a schematic view of an apparatus suitable for performing the dental composition curing method of the present invention using a LED radiation source;
FIG. 2 is a schematic view of a mercury dilatometer testing method suitable for evaluation of shrinkage rate and heating using the LED radiation dental composition curing method of the present invention;
FIG. 3 is a graphical representation of temperature measurements obtained with the dental composition curing method of the present invention using a LED radiation source; and,
FIG. 4 is a graphical representation of depth of cure measurements obtained with the dental composition curing method of the present invention using a LED radiation source.
DETAILED DESCRIPTION OF THE INVENTION
FIG. 1 shows schematically the elements of a dental curing apparatus 10 suitable for performing the dental composition curing method of the present invention using a LED radiation source. The curing apparatus 10 comprises an elongated handle 12 shaped for operator convenience in positioning a light emitting diode (LED) 14 proximate a target dental composition 16 so that curing radiation emitted from the LED 14 is directly incident upon the dental composition target 16. LED 14 may be attached to handle 12 by any of several methods, including clamping, receiving in a recess, gluing and the like. LED 14 is activated by means of a pair of low voltage power wires 18 illustrated for convenience as being contained within handle 12. Wires 18 are joined by means of a suitable connector 20 and power cord 22 to a programmable power supply 24 selected to provide the desired power parameters. When activated, LED 14 irradiates radiation energy, illustrated by arrow 26 onto the target material 16. If desired, a conventional radiation radiometer, not illustrated, may be used to ensure that power output from the LED 14 is within normal operating ranges.
Exemplary LEDs 14 useful in practicing the present invention include Panasonic's "LED Blue Clear" 1500 millicandela T 1-3/4, LNG992CFBW and similar devices commercially available from Hewlett Packard and Toshiba Such LEDs emit radiation in the range from about 440 to about 500 nanometers with a power output of about 1500 millicandela A programmable power supply 24 employed in conjunction with the above identified Panasonic LED is well known in the industry, specifically a model PS 281 produced by Tektronix was to obtain the results described below
Dental compositions 16 suitable as a filling material for cavities in teeth are well known in the art and may be obtained by mixing liquid phosphoric acid, water and a paste composed of a ceramic and hydroxyapatite, in a proportion to form a suitably workable composition A typical dental composition has a liquid component of about 40% phosphoric acid in water and a paste component of about 80% ceramic and 20% hydroxyapatite Increased amounts of hydroxyapatite demand more energy to cure the composition The ceramic component may be composed of corderite, silica or silicium oxide, or aluminum oxide, for example The powder components will have the grain sizes normally used for dental filling materials
The following examples are given to help a complete understanding of this invention and are provided herein for purposes of illustration only and are not intended to be limiting in any manner
EXEMPLARY EVIDENCES
In order to demonstrate the improved dental curing obtained using LED radiation in accordance with the present invention, comparative tests were completed using the dental curing apparatus 10 as described above and a conventional dental radiation curing unit like that available from Denstsply International Inc , Caulk Division, Milford, Delaware, specifically the Spectrum™ Curing Unit, Model 200R This unit is typical of other commercially available conventional curing units and employs a quartz halogen lamp filtered with a blue filter and includes an on-board radiometer to assure minimum levels of output power The Model 200R provides a minimum operating intensity of about 450 mW/cm in the 400-500 nanometer wavelength range at the output of its light guide This intensity decreases as distance to the target from the output end is increased
Tests described herein were completed using commercially available dental compositions, in particular, two different products, the DenMat® Marathon V #5474 and the Caulk TPH Spectrum Shade A 3 5 compositions were used to obtain comparative performance data between the LED curing method of the present invention and prior art conventional methods In all the following exemplary tests, the dental curing apparatus 10 was operated at an energy output level of about 25 mW/cm2 and was stationed at a distance of about 7mm ± 2mm above the dental composition target 16 for a peπod of 60 seconds The conventional Spectrum™ 200R Cuπng Unit was operated at an energy output level of about 300 mW/cm2 at the target 16 for a peπod of 60 seconds
( 1 ) Measurement of Depth of Cure
Depth of cure was measured in accordance with the established industry standard depth of cure measurement technique defined by the International Organization for Standardization as ISO DIS 4049, 1998 This technique employs a 7 mm thick stainless steel mold having a 4 0 mm diameter cylinder that extends through the mold The thickness of the mold is 2mm greater than twice the maximum depth of cure claimed The dental composition to be cured, in this instance, the Caulk TPH Spectrum Shade A 3 5 composition, is tightly filled into the cylinder and the open ends of the cylinder are covered with a polyester film One end of the cylinder is irradiated with curing radiation under test conditions and then the uncured mateπal is removed from the cylinder The cured cylinder is removed from the mold and the cured height is measured with a micrometer The depth of cure is recorded as half the height of the cured cylinder and the test is repeated twice As described above, both radiation sources, the dental cuπng apparatus 10 and the Spectrum™ 200R Cuπng Unit were used to cure the cylinder of dental composition
Depth of cure for a 4 mm diameter cylinder mold was then measured and determined to be 1 5 ± 0 1 mm for the LED radiation curing apparatus 10 at 25 mW/cm2 In contrast, to obtain a similar depth of cure using conventional blue-light radiation like that emitted from the conventional Spectrum™ 200R Cuπng Unit, it was necessary to operate at a power level of 53 mW/cm2 In the instance of obtaining a 2mm depth of cure, the LED radiation cuπng apparatus 10 was operated at 38 mW/cm2 and the conventional blue-light radiation cuπng gun was operated at about 200mW/cm2 Thus, the LED curing apparatus 10 may be operated at a much lower irradiation intensity than conventional dental guns to obtain an essentially equivalent or greater depth of cure
(2) Measurement of Shrinkage
The degree of shrinkage associated with polymerization with a polymer dental composition was measured in accordance with an established ADAHF industry standard technique using a dilatometer 30 like that illustrated in FIG 2 A dab of dental composition 14 with approximately 0 1 gram mass is placed on a standard microscope slide 32 that has been tared on a 4-dιgιt balance The composition 14 is spread on the slide 32 with a spatula, keeping the composition less than 1 5 mm thick and less than 5 mm in diameter to assure complete curing The weight of the composition is recorded to 4 decimals An open glass measurement tube 34 having a cup-shaped end section 36 is positioned with the cup-shaped end section 36 facing upwards and the microscope slide 32 with dental composition 14 is inverted over the cup so that the composition is centered in the cup.
The slide 32 is clamped secured to the measurement tube with a clamp 38, rotated 180-degrees to the orientation shown in FIG. 2 and filled with mercury 40. A prescribed linear displacement transducer 42, a Lucas Shaevitz LVDT, assembly is slowly lowered into the tube 34 until it rests on top of the glass measurement tube 34 with its plunger 44 floating on the mercury 40. A prescribed thermistor 46, an Omega 44133 thermistor is built into the cup-shaped section 36 of the measurement tube 34 and positioned to be in contact with the mercury 40 surrounding the composition 14 being tested. The LVDT assembly 42 and the Omega 44133 thermistor 46 are connected to a control box (not shown) and interfaced to a computer (not shown). Both radiation sources, the dental curing apparatus 10 and the conventional Spectrum™200R Curing Unit were used to irradiate the dental composition as illustrated in FIG. 2 for 60 seconds at output power levels of 25mw/cm2 and 300 mw/cm2, respectively.
A software program developed by the ADAHF residing within the computer is used to acquire and analyze data related to an expansion of the mercury from the LVDT and mercury temperature changes registered by the thermistor. The change in mercury level results from two sources: (1) shrinkage in dental composition due to polymerization, and (2) expansion in mercury due to irradiation induced heating. The software program calculates the expansion in mercury from the thermistor temperature data. The overall volume change is calculated based on LVDT data. From the combination of these data, the shrinkage within the dental composition may be calculated once the final density of cured polymer is provided. Final density of the polymer is measured using a Mettler Toledo AT 261 balance in combination with a Mettler Toledo 210485 density determination kit.
(3) Measurement of Heat
The increase in temperature associated with a 60-second exposure for achieving a depth of cure of 1.5 mm was measured using the ADAHF dilatometer described above. Again, both radiation sources, the dental curing apparatus 10 and the conventional Spectrum™ 200R Curing Unit were used to expose dental composition target 16 for 60 seconds at output power levels measured to be 25 mW/cm2 for the LED curing apparatus 10 and 450 mw/cm2 at the output end of the conventional blue-light dental gun. Due to the relatively high divergence of the conventional dental gun, its 300 mW/cm2 output irradiation corresponds to an energy density of about 53 mW/cm2 at the dental target 16. In contrast, the energy density of the LED curing apparatus 10 remains about 25 mW/cm2 due to the low divergence of the LED beam.
Temperature measurements beginning after the 60-second irradiation period are illustrated in FIG. 3. The dental curing apparatus 10 using an LED 14 illustrated with a solid line produced an initial temperature increase of about 0.78° C whereas in contrast the conventional light Spectrum™ 200R Curing Unit illustrated with a dashed line produced an initial temperature increase of about 0.85° C. Thus the dental curing apparatus 10 produced lower overall heating of the composition in contrast to the higher overall heating from the conventional blue light curing unit. Thereby, when treated with the dental curing method of the present invention, a patient will experience a significantly lower degree of discomfort as a result of the about 8% lower temperatures during curing of an embedded dental composition.
Shrinkage measurements made using these same irradiation intensities as in FIG. 3, which yield a 1.5 mm depth of cure, showed that the dental curing apparatus 10 of the present invention operating at 25 mw/cm2 produced a shrinkage of 2.758% whereas in contrast the conventional Spectrum™ 200R Curing Unit operating at 53 mW/cm2 produced a shrinkage of about 2.960%. This is a net shrinkage reduction of about 7% when using the inventive dental curing method and apparatus 10, a strongly desirable advantage of the present invention.
(4) Failure Mode
Although actual results were not experimentally determined, it is well known within the industry that dental curing guns employing conventional radiation sources gradually lose power output during the life of the dental gun. For example, a negative correlation between the depth of cure and the age of light-curing guns has been reported, with older Heliotests (Ivoclar-Vivadent) units tending to cure a Z100 Composite (3M) dental composition to less depth than newer units [Prim Dent Care 1997 Sep;4 (3):91-4j. Because of this time loss of power output, curing lights are considered as unsuitable for use with a reading of less than 200 mW/cm2 using a curing radiometer and greater than 50 mW/cm2 using a heat radiometer [J Dent 1999 Mar;27 (3):235-41] underscoring the necessity of monitoring the output of conventional dental curing guns as they age in use. In contrast, an inherent characteristic of LED radiation sources like those used in the present invention is a stable level of output radiation during the operating life of a LED, with a catastrophic failure that is readily noticeable by an operator whenever the output declines.
(5) Relative Costs The expenses associated with conventional radiation dental curing guns comes about as a result of the need to provide relatively high output power with appropriate filteπng and cooling means Such guns and the associated power supply cost in the $600-1,000 range In contrast, the LED-based dental cuπng method of the present invention employs low power LEDs costing in the $2 range and not requiπng the high output power, filteπng and cooling means of conventional dental cuπng guns
In the way of summary, the following Table contains the results of the Examples in a condensed form The advantages of using the present invention are evident and furthermore are totally unexpected in view of the absence within prior art of the use of LEDs for effective curing of dental compositions
Table 1
Figure imgf000011_0001
It is to be understood that the embodiments of the invention disclosed herein are illustrative of the pπnciples of the invention and that other modifications may be employed which are still within the scope of the invention For example, in one alternate exemplary embodiment, a dental composition having a different formulation from the one in the Evidences may be employed It is known from the literature that Axis and Thermoresin LC II dental compositions may be cured with both UV and visible radiation while another composition Dentacolor is cured substantially by visible light [J Oral Rehabil 1998 Oct, 25(10) 770-5] To confirm the effectiveness of the present invention, the depth of cure of a second commercially available dental composition known as Marathon V available from DenMat® was also evaluated using the LED-based cuπng method of the present invention in the aforedescribed ISO DIS 4049 testing method. The test results were essentially a duplicate of those reported in the above Evidences, part (1), and are shown in FIG. 4 thereby confirming the broad applicability of the present invention in curing dental compositions that are known to be curable by the application of radiation. FIG. 4 illustrates the depth of cure as a function of the distance of the LED from the dental composition with a blue-light Panasonic LED with a curing time of 60 sec. Fig. 4 shows that using the present inventive method provides a relatively constant depth of cure as long as the LED is positioned within a distance of 8mm from the dental composition, a result of the low divergence of the LED beam in comparison to the highly divergent radiation generated within a conventional filtered light dental gun. Optimum distance from the dental composition target is seen to be in the range of 1-8 mm for the LED curing apparatus 10.
In another alternate exemplary embodiment, it is obvious that a light emitting diode having other than "clear blue" wavelengths may be employed as long as the dental composition may be cured by the application of corresponding radiation. It is known from the literature that microfilled and hybrid composition materials designed for prosthetic veneer may be cured with different types of light, in particular both xenon light and metal halide light sources. Depending on the choice of light source and the choice of dental composition, an increased exposure duration increases the depth of cure for all combinations [J Oral Rehabil 1998 May; 25 (5):348-52]. Accordingly the present invention may be practiced using any LED having its wavelength selected to provide radiation energy in the effective curing range for the composition being employed. In this alternate exemplary embodiment, the duration of radiation exposure with a LED as disclosed in the present application may be increased to accomplish a minimum acceptable depth of cure, depending on the selection of LED radiation wavelength and the selection of dental composition. Accordingly, the present invention is not limited to those embodiments precisely shown and described in the specification but only by the following claims.

Claims

What is claimed is
1 A method for curing a dental composition suitable for repairing a dental cavity or a dental surface comprising
applying the dental composition to the cavity or surface, and, exposing the composition to radiation from a light emitting diode having output wavelengths selected to photo-activate a hardening chemical reaction within the composition
2 The method of claim 1 wherein the light emitting diode is selected from the group comprising blue, red, and green light emitting diodes
3 The method of claim 1 wherein the light emitting diode comprises a blue light emitting diode
4. The method of claim 1 wherein the dental composition comprises a combination of a ceramic and hydroxyapatite
5 The method of claim 3 wherein the dental composition comprises a combination of a ceramic and hydroxyapatite
6 The method of claim 1 wherein the light emitting diode has a radiation wavelength in the range from about 440 nanometers to about 500 nanometers.
7 The method of claim 1 wherein the light emitting diode is operated at a power output in the range of about 25 mW/cm to about 38 mW/cm
8 The method of claim 1 wherein the light emitting diode is positioned a distance of less than about 8 mm from the dental composition being cured
9 The method of claim 7 wherein the light emitting diode is activated for a period about 60 seconds
10 A device for curing a dental composition suitable for repairing dental cavities or dental surfaces, the device comprising
a light emitting diode having output wavelengths selected to photo-activate a hardening chemical reaction within the composition;
a holder for positioning the light emitting diode proximate said dental composition; and,
a power supply connected to the light emitting diode and adapted to cause the diode to emit radiation energy suitable for hardening the dental composition.
11. The device of claim 10 wherein the light emitting diode is selected from the group comprising blue, red, and green light emitting diodes.
12. The device of claim 10 wherein the light emitting diode comprises a blue light emitting diode.
13. The device of claim 10 wherein the light emitting diode has a radiation wavelength in the range from about 440 nanometers to about 500 nanometers.
14. The device of claim 10 wherein the light emitting diode is operated at a power output in the range of about 25 mW/cm2 to about 38 mW/cm2.
15. The device of claim 10 wherein the light emitting diode is positioned a distance of less than about 8 mm from the dental composition being cured.
16. The device of claim 14 wherein the light emitting diode is activated for a period about
60 seconds.
PCT/US2000/027609 1999-10-05 2000-10-05 Method for curing a dental composition using a light emitting diode WO2001024724A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU10740/01A AU1074001A (en) 1999-10-05 2000-10-05 Method for curing a dental composition using a light emitting diode

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US09/412,683 US6318996B1 (en) 1999-10-05 1999-10-05 Method for curing a dental composition using a light emitting diode
US09/412,683 1999-10-05

Publications (1)

Publication Number Publication Date
WO2001024724A1 true WO2001024724A1 (en) 2001-04-12

Family

ID=23634010

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2000/027609 WO2001024724A1 (en) 1999-10-05 2000-10-05 Method for curing a dental composition using a light emitting diode

Country Status (3)

Country Link
US (1) US6318996B1 (en)
AU (1) AU1074001A (en)
WO (1) WO2001024724A1 (en)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9066777B2 (en) 2009-04-02 2015-06-30 Kerr Corporation Curing light device
US9072572B2 (en) 2009-04-02 2015-07-07 Kerr Corporation Dental light device
US9572643B2 (en) 1998-01-20 2017-02-21 Kerr Corporation Apparatus and method for curing materials with radiation
US9726435B2 (en) 2002-07-25 2017-08-08 Jonathan S. Dahm Method and apparatus for using light emitting diodes for curing
RU2745537C2 (en) * 2018-07-27 2021-03-26 Федеральное Государственное Бюджетное Образовательное Учреждение Высшего Образования "Дагестанский Государственный Технический Университет" (Дгту) Automated thermoelectric system for liquid-cooled thermo-odontometry
RU2751286C2 (en) * 2018-07-23 2021-07-12 Федеральное Государственное Бюджетное Образовательное Учреждение Высшего Образования "Дагестанский Государственный Технический Университет" (Дгту) Automated thermoelectric system for thermo-odontometry with evaporation cooling

Families Citing this family (61)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6423818B1 (en) * 1999-07-30 2002-07-23 Takehisa Matsuda Coumarin endcapped absorbable polymers
US6719559B2 (en) 1999-09-24 2004-04-13 Densen Cao Curing light
US6783362B2 (en) 1999-09-24 2004-08-31 Cao Group, Inc. Dental curing light using primary and secondary heat sink combination
US6755649B2 (en) 1999-09-24 2004-06-29 Cao Group, Inc. Curing light
US6910886B2 (en) 1999-09-24 2005-06-28 Cao Group, Inc. Curing light
US6932600B2 (en) * 1999-09-24 2005-08-23 Cao Group, Inc. Curing light
US7077648B2 (en) * 1999-09-24 2006-07-18 Cao Group, Inc. Curing light
US6780010B2 (en) 1999-09-24 2004-08-24 Cao Group, Inc. Curing light
US6988891B2 (en) * 1999-09-24 2006-01-24 Cao Group, Inc. Curing light
US6926524B2 (en) * 1999-09-24 2005-08-09 Cao Group, Inc. Curing light
US6929472B2 (en) 1999-09-24 2005-08-16 Cao Group, Inc. Curing light
US6971876B2 (en) 1999-09-24 2005-12-06 Cao Group, Inc. Curing light
US6988890B2 (en) 1999-09-24 2006-01-24 Cao Group, Inc. Curing light
US6971875B2 (en) 1999-09-24 2005-12-06 Cao Group, Inc. Dental curing light
US6719558B2 (en) 1999-09-24 2004-04-13 Densen Cao Curing light
US6981867B2 (en) 1999-09-24 2006-01-03 Cao Group, Inc. Curing light
US7094054B2 (en) 1999-09-24 2006-08-22 Cao Group, Inc. Dental curing light
US7294364B2 (en) * 1999-09-24 2007-11-13 Cao Group, Inc. Method for curing composite materials
US7086858B2 (en) 1999-09-24 2006-08-08 Cao Group, Inc. Semiconductor curing light system useful for curing light activated composite materials
US6979193B2 (en) 1999-09-24 2005-12-27 Cao Group, Inc. Curing light
US7066732B2 (en) * 1999-09-24 2006-06-27 Cao Group, Inc. Method for curing light-curable materials
US6974319B2 (en) * 1999-09-24 2005-12-13 Cao Group, Inc. Curing light
US6709128B2 (en) * 2001-03-26 2004-03-23 Ocumed, Inc. Curing system
US20020151941A1 (en) * 2001-04-16 2002-10-17 Shinichi Okawa Medical illuminator, and medical apparatus having the medical illuminator
US6767109B2 (en) 2001-06-06 2004-07-27 Ivoclar Vivadent Ag Light hardening device and a light source suitable for use in a light hardening device
US6835064B2 (en) * 2001-11-09 2004-12-28 Ivoclar Vivadent Ag Light hardening device and method for hardening a polymerizable mass for dental applications
US6702576B2 (en) 2002-02-22 2004-03-09 Ultradent Products, Inc. Light-curing device with detachably interconnecting light applicator
US7186108B2 (en) * 2002-04-11 2007-03-06 Pentron Laboratory Technologies, Llc Curing unit for dental materials
KR20050044865A (en) 2002-05-08 2005-05-13 포세온 테크날러지 인코퍼레이티드 High efficiency solid-state light source and methods of use and manufacture
DE10222828B4 (en) 2002-05-21 2008-05-15 3M Espe Ag irradiator
US6893258B1 (en) 2002-06-11 2005-05-17 Cms-Dental Aps Dental material curing apparatus
US6902397B2 (en) * 2002-08-01 2005-06-07 Sunstar Americas, Inc. Enhanced dental hygiene system with direct UVA photoexcitation
US20050288387A1 (en) * 2002-08-21 2005-12-29 Li Feng Acrylate dental compositions with improved viscosity and storage odor
US20040124370A1 (en) * 2002-12-13 2004-07-01 John Gerlock Process and system for curing clearcoats
US20070020578A1 (en) * 2005-07-19 2007-01-25 Scott Robert R Dental curing light having a short wavelength LED and a fluorescing lens for converting wavelength light to curing wavelengths and related method
US6957907B2 (en) * 2003-04-11 2005-10-25 Ultradent Products, Inc. Illumination apparatus having a light-converting lens for increasing visual contrast between different oral tissues
US20050170316A1 (en) * 2004-01-29 2005-08-04 Russell Bruce M. Toothbrush for detecting the presence of plaque
US20050175956A1 (en) * 2004-02-11 2005-08-11 Russell Bruce M. Toothbrush for whitening teeth
US20070111167A1 (en) * 2004-02-11 2007-05-17 Colgate-Palmolive Company Light-based toothbrush
US20050205882A1 (en) * 2004-03-16 2005-09-22 John Condon LED-photo-curing device
US7074040B2 (en) 2004-03-30 2006-07-11 Ultradent Products, Inc. Ball lens for use with a dental curing light
JP5280051B2 (en) * 2004-07-02 2013-09-04 ディスカス デンタル,エルエルシー Dental light device with improved heat sink
US20060018123A1 (en) * 2004-07-02 2006-01-26 Rose Eric P Curing light having a reflector
WO2006014309A2 (en) * 2004-07-02 2006-02-09 Discus Dental Impressions, Inc. Curing light capable of multiple wavelengths
US20060057537A1 (en) * 2004-09-15 2006-03-16 Welch Allyn, Inc. Combination dental instrument
US7371066B2 (en) * 2004-09-15 2008-05-13 Miltex, Inc. Illuminated dental examination instrument
US20060057535A1 (en) * 2004-09-15 2006-03-16 Welch Allyn, Inc. Cordless intraoral dental examination instrument having non-plano mirror
JP4800324B2 (en) 2004-12-30 2011-10-26 フォーセン テクノロジー インク Exposure equipment
US8109981B2 (en) 2005-01-25 2012-02-07 Valam Corporation Optical therapies and devices
US7321004B2 (en) * 2005-02-11 2008-01-22 New Photonics, Llc Method for photo-curing polymerizable compositions
US7407616B2 (en) * 2005-02-11 2008-08-05 New Photonics, Llc Method for photo-curing polymerizable compositions with pulsed light
US20060252005A1 (en) * 2005-05-06 2006-11-09 Feinbloom Richard E Apparatus for providing radiation at multiple wavelengths and method of operating same
US20080101073A1 (en) * 2006-11-01 2008-05-01 Discus Dental, Llc Dental Light Devices Having an Improved Heat Sink
GB0720165D0 (en) 2007-10-16 2007-11-28 3M Innovative Properties Co Light-emitting device
US20090208894A1 (en) * 2008-02-18 2009-08-20 Discus Dental, Llc Curing Light
US9642687B2 (en) 2010-06-15 2017-05-09 The Procter & Gamble Company Methods for whitening teeth
JP5713945B2 (en) * 2012-03-26 2015-05-07 三菱電機株式会社 Curing shrinkage measuring apparatus and curing shrinkage measuring method
BR112017005431A2 (en) 2014-09-17 2019-05-14 Garrison Dental Solutions Llc dental curing light
US10307940B2 (en) 2016-05-13 2019-06-04 MSI Coatings Inc. System and method for using a VOC free low radiant flux LED UV curable composition
USD810293S1 (en) 2017-01-20 2018-02-13 Garrison Dental Solutions, Llc Dental instrument
US11338320B1 (en) 2018-02-03 2022-05-24 MSI Coatings Inc. Composition for aerosol cans, method of making and using the same

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5147204A (en) * 1991-08-08 1992-09-15 Minnesota Mining And Manufacturing Co. Dental material curing apparatus
US5420768A (en) * 1993-09-13 1995-05-30 Kennedy; John Portable led photocuring device
US5711665A (en) * 1995-12-19 1998-01-27 Minnesota Mining & Manufacturing Method and apparatus for bonding orthodontic brackets to teeth
US5885082A (en) * 1988-12-21 1999-03-23 Endo Technic International Corporation Dental and medical procedures employing laser radiation

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AR207269A1 (en) 1975-03-20 1976-09-22 Dentsply Int Inc LIGHT SOURCE APPARATUS TO SUPPLY ULTRAVIOLET RADIATION TO A RESTRICTED SURFACE AREA
US4229658A (en) 1978-08-18 1980-10-21 Dentsply Research & Development Corp. Xenon light apparatus for supplying ultraviolet and visible spectra
US4385344A (en) 1980-08-29 1983-05-24 Dentsply Research & Development Corp. Visible light apparatus for curing photo-curable compositions
US6102696A (en) 1999-04-30 2000-08-15 Osterwalder; J. Martin Apparatus for curing resin in dentistry

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5885082A (en) * 1988-12-21 1999-03-23 Endo Technic International Corporation Dental and medical procedures employing laser radiation
US5147204A (en) * 1991-08-08 1992-09-15 Minnesota Mining And Manufacturing Co. Dental material curing apparatus
US5420768A (en) * 1993-09-13 1995-05-30 Kennedy; John Portable led photocuring device
US5634711A (en) * 1993-09-13 1997-06-03 Kennedy; John Portable light emitting apparatus with a semiconductor emitter array
US5711665A (en) * 1995-12-19 1998-01-27 Minnesota Mining & Manufacturing Method and apparatus for bonding orthodontic brackets to teeth

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9572643B2 (en) 1998-01-20 2017-02-21 Kerr Corporation Apparatus and method for curing materials with radiation
US9622839B2 (en) 1998-01-20 2017-04-18 Kerr Corporation Apparatus and method for curing materials with radiation
US9726435B2 (en) 2002-07-25 2017-08-08 Jonathan S. Dahm Method and apparatus for using light emitting diodes for curing
US9066777B2 (en) 2009-04-02 2015-06-30 Kerr Corporation Curing light device
US9072572B2 (en) 2009-04-02 2015-07-07 Kerr Corporation Dental light device
US9693846B2 (en) 2009-04-02 2017-07-04 Kerr Corporation Dental light device
US9730778B2 (en) 2009-04-02 2017-08-15 Kerr Corporation Curing light device
US9987110B2 (en) 2009-04-02 2018-06-05 Kerr Corporation Dental light device
RU2751286C2 (en) * 2018-07-23 2021-07-12 Федеральное Государственное Бюджетное Образовательное Учреждение Высшего Образования "Дагестанский Государственный Технический Университет" (Дгту) Automated thermoelectric system for thermo-odontometry with evaporation cooling
RU2745537C2 (en) * 2018-07-27 2021-03-26 Федеральное Государственное Бюджетное Образовательное Учреждение Высшего Образования "Дагестанский Государственный Технический Университет" (Дгту) Automated thermoelectric system for liquid-cooled thermo-odontometry

Also Published As

Publication number Publication date
US6318996B1 (en) 2001-11-20
AU1074001A (en) 2001-05-10

Similar Documents

Publication Publication Date Title
US6318996B1 (en) Method for curing a dental composition using a light emitting diode
US6755647B2 (en) Photocuring device with axial array of light emitting diodes and method of curing
US6468077B1 (en) Compact device for curing dental compositions and method of curing
US20020187455A1 (en) Device for curing photosensitive dental compositions with off-axis lens and method of curing
Malhotra et al. Light-curing considerations for resin-based composite materials: a review. Part I
US7407616B2 (en) Method for photo-curing polymerizable compositions with pulsed light
US5616141A (en) Laser system for use in dental procedures
Santini Current status of visible light activation units and the curing of light-activated resin-based composite materials
Rueggeberg State-of-the-art: dental photocuring—a review
Kramer et al. Light curing of resin-based composites in the LED era.
US6171105B1 (en) Dental-restoration light-curing system
US20090046476A1 (en) Dental Light Guide
JP2001522635A (en) Strobe light curing apparatus and method
US20120301842A1 (en) Method and apparatus for hard tissue treatment and modification
US20050227205A1 (en) Apparatus and method for root canal obturation
US20060183810A1 (en) Method for photo-curing polymerizable compositions
JPH07255751A (en) Dental impression tray for photosetting impression material
Jiménez-Planas et al. Developments in polymerization lamps.
WO2006074525A1 (en) Dental illumination device and method
EP2698125B1 (en) Scanning polymerization of dental material
US20020093833A1 (en) Optically enhanced halogen curing light
JP2004321801A (en) Spot curing lens used to spot cure dental appliance adhesive, and system and method employing such lens
US20030152885A1 (en) Dental curing device with blue light emitting diodes
Dogan et al. Temperature rise induced by various light curing units through human dentin
Mahn Light polymerization

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AE AG AL AM AT AU AZ BA BB BG BR BY BZ CA CH CN CR CU CZ DE DK DM DZ EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX MZ NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG UZ VN YU ZA ZW

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG

121 Ep: the epo has been informed by wipo that ep was designated in this application
DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
REG Reference to national code

Ref country code: DE

Ref legal event code: 8642

122 Ep: pct application non-entry in european phase
NENP Non-entry into the national phase

Ref country code: JP