Heating, dye absorption, and material properties of dental materials utilizing harmonic characteristics

Abstract

We advocate for an improved endodontic treatment system. [Solution] In endodontic treatment, the present invention relates to the application of photon energy to impart energy to dental materials to enhance, among other attributes, physical handling properties, efficacy, delivery ability, reactivity, polymerization, and / or mechanical properties after hardening.

Description

Technical Field

[0001] The present invention relates to the application of photon energy to dental materials to enhance, among other attributes, physical handling properties, effectiveness, delivery ability, reactivity, polymerization, and / or mechanical properties after curing.

Background Art

[0002] In many dental procedures, such as root canal and tooth restoration, it is necessary to clean and fill the internal space of the tooth in order to effectively repair and seal the space from the external environment. During endodontic treatment, dentists use chemo-mechanical methods to enlarge and clean the root canal lumen. Specifically, dentists use endodontic medicaments to remove debris, residual pulp tissue, and bacteria before filling. Despite advancements in endodontic instruments, the failure rate of endodontic treatment is approximately 30%. These failures are due to re-colonization of bacteria / infection of the root canal due to inappropriate cleaning or failure of the restoration. In many cases, restorative procedures fail for many of the same reasons as endodontic procedures, which are microleakage around the restoration that promotes poor adhesion of the material to the tooth structure and / or re-colonization / infection of bacteria. Therefore, the materials used during dental procedures need to conform to the complex shape of the space to which they are applied, effectively bond to the tooth or cavity structure, and seal the area where the material is placed. By improving the effectiveness of dental solutions (e.g., endodontic irrigants) and dental materials (e.g., gutta-percha, dental composite resins, i.e., composite materials, dental sealants, etc.), better cleaning and filling of these voids can be promoted and the success rate can be increased.

[0003] (Dental composite material) Dental composite resins offer dental professionals one of the most cost-effective ways to restore a patient's dentition in an aesthetically pleasing manner, defined as matching the patient's natural tooth color. To satisfy cosmetic reasons and consumer demand, composite resins are a preferred alternative to metal restorations, most specifically amalgam. Initially, composite resins faced doubt and skepticism due to their numerous drawbacks, including reduced wear resistance, micro-leakage, body fracture, peripheral fracture, recurrent collapse, postoperative sensitivity, improper interdental contact and contour, color degradation, and inability to maintain polish or shine. In addition to the physical and mechanical limitations of dental composite resins, their placement is technique-sensitive. The placement of composite resins requires meticulous attention to the procedure; otherwise, premature failure is possible. Furthermore, the teeth must be kept dry during resin placement; otherwise, adhesion to the teeth may be reduced, leading to restoration failure. The composite material is initially placed in a soft, fabric-like state, but when exposed to light of a specific blue wavelength, it polymerizes and hardens, becoming a solid filler.

[0004] Composite resins generally consist of acrylate monomers (such as triethylene glycol dimethacrylate, TEGDMA, urethane dimethacrylate, UDMA, bisphenol A glycidyl dimethacrylate, and bis-GMA), inorganic fillers (glass or ceramic), a photopolymerization system, and colorants and pigments that match the color and shade of teeth. Camphorquinone (CQ) is the most common photoinitiator used in photopolymerizable dental materials. CQ has a peak excitation of approximately 470 nm and is a type II photoinitiator, requiring the addition of a co-initiator to generate free radicals to initiate polymerization. Other photopolymerizable dental materials include type I photoinitiators such as diphenyl (2,4,6-trimethylbenzoyl)phosphine oxide (TPO) or 1-phenyl 1,2-propanedione (PPD), which do not require a co-initiator for polymerization. Regardless of the photoinitiators and / or co-initiators used in commercially available products, due to the light absorption and scattering properties of dental materials, it is not clinically practical to completely convert all free monomers into oligomers and polymers within the composite material, as they cannot penetrate beyond a few millimeters into the composite. If a composite is too thick inside a tooth... The deeper the composite, the softer it remains, and this soft, unpolymerized composite ultimately leads to restoration failure, leaching of potentially toxic free / unreacted monomers, and / or leakage of the bonded joints, resulting in recurrent tooth pathology. To overcome this problem, dentists are trained to place the composite in multiple increments, allowing each 2-3 mm section to fully cure before adding the next increment, maximizing polymerization throughout each composite increment and the complete restoration. Furthermore, clinicians must carefully construct the composite filling to match the patient's natural occlusion. If the filling is too deep, the patient's bite may become unnatural, potentially leading to chewing hypersensitivity and impaired recovery. Due to the aforementioned problems, improved composite compositions, curing light, delivery systems, placement methods, and improved post-curing properties of dental composites are desirable to assist clinicians and improve the success of restorations.

[0005] The main drawback of conventional dental composites (as documented in the literature) is the fact that the resin exhibits polymerization shrinkage. Polymerization of the resin initiates the conversion of monomer molecules into a polymer matrix, leading to shrinkage. This bulk shrinkage (polymerization shrinkage) is considered a volume reduction during the curing / polymerization process. The material deforms in stages from viscous to viscoelastic to elastic. In the viscous stage, no stress is present. However, in the viscoelastic stage, stress is generated in the material and at the interface between the material and the tooth. Due to the volume change of the composite material, shrinkage stress is transmitted to the cavity walls of the tooth. These stresses, and the resulting polymerization shrinkage, can be influenced by the choice of material, the content of the filler, the irradiance and duration of the polymerization light source used, the curing properties of the resin, water absorption, and cavity preparation configuration. Many options have been proposed to limit the internal stress on the tooth, including the use of liners and bases, changes in polymerization light, irradiance waveform, incremental layering, increasing the filler content, and changes in bonding techniques. Unfortunately, none of these can completely compensate for the effects of this phenomenon.

[0006] Lowering viscosity has been shown to improve the adaptability of composites and enhance ease of placement, which is a crucial effect. This is the main basis for the development of fluid resin composites and fluid liners. These fluid composites achieve lower viscosity primarily by reducing the content of reinforcing fillers and altering the chemical properties of the matrix. Various studies have shown that low viscosity composites can improve adaptability and reduce microleakage. The use of fluid composites is touted as a way to ensure closer contact with both the dentin adhesive and the inner surface of the prep, thereby enhancing the seal obtained by the composite. Depending on the type of restoration, achieving a complete interfacial seal between the tooth structure and the composite can be challenging.

[0007] One potential way to improve sealing is to use low-viscosity fluid composites; however, these fluid composites are generally not considered as durable as high-viscosity materials due to the lower level of reinforcing filler particles present. A second approach is to use fluid liners in combination with conventional composites. A third option is to use conventional / high-filler composites that have been heated to reduce viscosity. This last approach allows for the use of durable conventional composites, reducing viscosity to form a more complete interface with the tooth tissue and eliminating the need for fluid liners. Also, since fluid resins have a lower filler content than conventional composites, this third option is considered advantageous, and the reduced filler content results in a higher shrinkage rate. This can be a problem in restorative techniques when large amounts of fluid composites are used to improve the seal and limit fit of the composite.

[0008] As mentioned earlier, many polymer resins exhibit lower viscosity when heated. The theoretical basis for this behavior is that thermal vibrations force the composite monomers or oligomers to separate further, allowing them to slide more easily to one another. Studies have shown that heating common polymers and resin composites reduces their viscosity, thereby improving their adaptability. It has been shown that raising the temperature of dental composites reduces viscosity, as indicated by a decrease in film thickness. Deb et al. (Dent Mater. 2011 Apr; 27(4):e51-9.) showed that raising the temperature of dental composites reduces viscosity. Similar results were found by Bloom (Dent Adv. 2006 Jan; 4.). Thus, preheating improves the physical and mechanical properties of the resin, and preheated composites have become a focus of recent research. Preheating dental composites has been shown to reduce viscosity and potentially increase the microhardness of the composite resin after curing. The currently available devices used to assist clinicians in preheating composites rely primarily on conductive heat transfer and have many drawbacks, among other challenges and limitations, including long heating times, the fact that heating is not at the delivery point allowing the composite to cool to potentially room temperature depending on the time it takes to apply the procedure, the inability to rapidly heat multiple composites, and the inability to heat composites placed within restorations.

[0009] (Effect of high temperature on the properties of composite materials after curing) There are concerns about the effect of preheating on the properties of photopolymerizable dental materials. Several studies have investigated double bond conversion (a measure of how completely the polymerization reaction proceeds) and the hardness of composites after preheating. These studies are important in determining how quickly and completely composites polymerize. Preheating improves conversion rate and hardness, without negative changes. Generally, an increase in conversion rate corresponds to an improvement in the mechanical properties of the polymer material and composite. Therefore, preheating may result in more durable composite restorations. Furthermore, there have been concerns that higher temperatures in preheated composites lead to greater shrinkage during and after curing. Elhejazi (J Contemp Dent Pract. 2006 Jul 1; 7(3):12-21.) showed that increasing the temperature of resin composites increases shrinkage. In response to this concern, it has been proposed that preheated composites can be cooled for approximately 15 seconds after placement and before curing. Another concern expressed in the literature is that exposure to preheating cycles shortens the shelf life of unused composites. However, Daronch et al. (J Esthet Rest or Dent.2006; 18(6):340-51) showed that neither a preheating cycle nor a 24-hour extension of preheating caused significant changes in monomer conversion rates. While some studies have shown that preheating does not adversely affect dental materials, these studies are inconsistent and not comprehensive for all dental materials.

[0010] (Obstruction) The success of root canal treatment depends on many factors. It begins with removing all organic matrix from the canal. This includes the removal of coronal pulp tissue and root pulp tissue. By performing a complete access and identifying a direct access to the root pulp tissue, the coronal pulp tissue is removed. This allows the practitioner to remove the root pulp tissue with endodontic files and irrigation. Since approximately 30% of the root canal is left untouched with chemical and mechanical instruments alone, irrigation is undoubtedly the most important part of endodontics. Therefore, the importance of effective irrigation in root canal preparation cannot be overemphasized, and it is desirable to enhance the activity / effectiveness of endodontic irrigators. [Overview of the project] [Problems that the invention aims to solve]

[0011] Finally, the ultimate goal is to prevent reinfection by occluding the canal in three dimensions. To enhance the success of endodontic treatment, the canal system must be effectively sealed at the coronal and apical points. The apical seal is the primary barrier against leakage. There are many different occlusion techniques, and no single technique has been identified as clearly superior. Applying heat to the occlusion has been shown to increase success rates and enable occlusion of canal irregularities and anatomical structures that may not be sealable with conventional techniques. A successful occlusion is characterized and classified as a three-dimensional filling of the entire root canal system as close as possible to the cementum-dentin junction. That is, patent canal (patent Without excessive extension or insufficient filling in the presence of the canal. A minimal amount of root canal sealer is used in conjunction with the core filling material to establish a proper seal.

[0012] For many years, controversy has surrounded root canal occlusion. Clinicians and academics alike have researched, studied, applied, and compared numerous warm occlusion techniques, but no single technique has proven superior to the others, and clinicians can develop their preferences through experimentation and trial and error.

[0013] After endodontic closure, coronal restoration is completed to restore the tooth's shape and occlusal surface. There is reasonable evidence suggesting that coronary artery leakage from improperly placed restorations is a significant factor in endodontic failure. Therefore, there remains an unmet need for new methods, compositions, and apparatus to improve the application and hardening of dental materials and to perform the aforementioned dental procedures. [Means for solving the problem]

[0014] The advantage of the embodiments of the present invention described herein is that, by applying photon energy to a dental composite or a container for a dental composite, the material is rapidly and efficiently heated chairside above ambient temperature. The concept of this invention is also applicable to all dental materials. Compared with commercially available composite heaters, the disclosed invention is highly efficient, especially when there is a high conversion efficiency from photon energy to heat. Raising the temperature of dental materials such as dental composite resins improves the physical handling properties and delivery capabilities of the material, and dental composites can exhibit a viscosity similar to fluid composites but without the adverse effects (high shrinkage, low wear retention, low hardness, etc.), thus eliminating the need for fluid composites. Furthermore, the present invention enables the application of photon energy to the dental material once the dental material is in place, so improved handling properties can be achieved even after dispensing the material from a tool or wand. In addition, the improved fluidity and adaptability allow for filling small gaps in teeth, enabling minimally invasive restorations. Furthermore, by heating composite materials, manufacturers can develop and commercialize composite materials with higher filler capacities. This was previously impossible due to the constraints on extruding and handling highly filled materials. Normally, increasing the filler content makes the composite material too thick and difficult to handle, but by heating it using photon energy, the fluidity returns to that of a less filled composite material, while retaining the advantages of a highly filled composite material (i.e., reduced shrinkage stress, improved durability). Therefore, the disclosed invention further improves coronary artery repair and thereby improves clinical outcomes.

[0015] As described herein, dental materials are provided that, upon heating, increase the fluidity of the material, facilitating the application of the material and its conformation to the tooth surface to which it is applied. Furthermore, as a result of heating the material, the composite material, upon curing, exhibits increased hardness and durability without degradation of the cured dental material compared to dental materials placed without using the method described herein.

[0016] Furthermore, the disclosed invention utilizes photon energy to heat endodontic cleaning agents faster than ambient temperature, promoting the photochemical effect and thereby making the cleaning agent more effective during use. Moreover, a key advantage of the disclosed invention is that the use of photon energy does not have any particularly harmful effects on dental materials or dental composite resins. Furthermore, the invention described herein allows gutta-percha or similar occlusive materials to be delivered and applied into the root canal lumen, resulting in improved handling and lower viscosity than previously achieved. By reducing viscosity and improving delivery, the invention enables clinicians to more reliably achieve three-dimensional filling of complex root canal anatomy and significantly reduce endodontic failures. [Brief explanation of the drawing]

[0017] [Figure 1] This is a graph of the near-infrared absorption bands of typical organic bonds and functional groups, showing the peak absorption bands of the organic and functional group structures, and details of their respective first, second, and third harmonic absorption bands. [Figure 2] An area cross diagram, where A1 = area under the curve (AUC) of the normalized additive spectrum, A2 = AUC of the normalized photon energy source spectrum, and A3 = area cross over between the additive spectrum and the emission spectrum of the photon energy source, wherein in some embodiments, A3 is at least 10% of A1 or A2, in some embodiments, A3 is at least 25% of A1 or A2, and in some embodiments, A3 is at least 50% of A1 or A2. [Figure 3]This graph compares the absorption of three commercially available dental composite resin materials (also known as dental composites) with that of poly(methyl methacrylate) (i.e., acrylic). The figure demonstrates the similarity between the near-infrared absorption characteristics of dental composites and acrylic, due to the presence of acrylate-based monomers within the composite resin composition. These absorption characteristics can be utilized for efficient heating using photon energy. For example, targeting higher absorption bands with higher photon energy can accelerate the heating of dental materials. [Figure 4] This graph shows the absorbance of gutta-percha and highly filled dental composite materials. These absorption properties can be utilized for heating using photon energy; in this case, higher absorptivity leads to improved photon energy conversion efficiency and faster heating rates. [Figure 5] This graph shows the absorption curves of polycarbonate plastics with different pigments added to the thermoplastic resin. This figure illustrates the dependence of near-infrared absorption not only on the material itself but also on the material's color. Therefore, the absorbance properties of a material container can be altered using thermoplastic colorants / pigments. These absorption properties can be utilized for heating using photon energy; in this case, higher absorptivity leads to improved photon energy conversion efficiency and faster heating. [Figure 6] This graph shows the internal temperature inside a composite compule using a commercially available composite heater. This figure illustrates how current composite heaters require a longer warm-up time to reach the ideal temperature compared to the present invention. [Figure 7] This graph shows the time taken to heat three different commercially available dental composite materials using various photon energy sources and spatial arrangements. The figure demonstrates that not only optical output is converted into thermal velocity, as thermal diffusion also plays a significant role in the distribution and transfer of heat within the composite material and the composite compar itself. Therefore, to implement the present invention, it is necessary to utilize appropriate optical output and spatial orientation of the photon energy source directed towards the dental material and / or dental material container in order to maintain optimal performance and input power (i.e., efficiency). [Figure 8]Graph of viscosity vs. shear rate of various composite materials at different temperatures. This figure shows that at all shear rates, the viscosity of commercially available dental composite materials decreases with increasing temperature, and the decreased viscosity improves handling characteristics and delivery to teeth and / or cavities. [Figure 9] Graph of the fluidity of highly filled composites versus temperature compared to a flowable composite at room temperature. This figure shows that heating a highly filled composite results in fluidity equal to or greater than that of a flowable composite, demonstrating that clinicians can eliminate the need to use heat to use a flowable composite as a liner for cavity restoration. [Figure 10] Graph of microhardness after curing when various commercially available dental composite materials are maintained and cured at various temperatures. This figure shows that at temperatures higher than ambient temperature, polymerization of the dental composite material during curing increases, and the microhardness of the upper and lower parts of a 2-mm pack becomes higher. [Figure 11] Graph of monomer and oligomer conversion after curing of highly filled composites exposed to various multi-spectral patterns of applied photon energy (850 nm) and curing light (405 nm and 470 nm simultaneously). Statistically significant differences (p<0.05) were observed between G3 top and G1 top, and between G4 top and G1 top. This figure shows that the addition of photon energy within the disclosed wavelength range enhances the degree of conversion to post-polymerization curing and increased microhardness values. [Figure 12] Graph of microhardness values after curing of highly filled composites exposed to various multi-spectral patterns of applied photon energy (850 nm) and curing light (405 nm and 470 nm simultaneously). Statistically significant differences (p<0.05) were observed between G3 top and G1 top, and between G4 top and G1 top. This figure shows that the addition of photon energy within the disclosed wavelength range enhances the degree of conversion to post-polymerization curing and increased microhardness values. [Figure 13]This graph shows the post-curing microhardness values ​​of various commercially available dental composites after application of photon energy or extended high temperatures from an oven, compared to room temperature. The data indicates that the application of photon energy or high temperatures (80°C) from an oven for one hour did not adversely affect the composites, as the microhardness values ​​did not change statistically significantly compared to the room-temperature (untreated) composites after curing. [Figure 14] This is an isometric view of a delivery device according to one exemplary embodiment of the present invention. [Figure 15] Figure 14 shows a partial broken bottom view of the distribution tip and composite of the apparatus, illustrating the retention of the compound and spatial orientation of the photon energy source directed towards a dental container containing a photopolymerizable dental material. [Figure 16] This is an isometric view of a delivery device according to another exemplary embodiment of the present invention. [Figure 17] This is an exemplary embodiment of a package consisting of at least three photon energy emitters (i.e., LEDs) for use in a multispectral apparatus, emitting at least two separate emission spectra to cure dental composite materials and applying photon energy for heating. The image on the left is a top view of the package showing the orientation of the three photon energy emitters (i.e., LEDs) on a cloverleaf PCB. The image on the right is a cross-section of the package showing the centrally positioned photon energy emitter 32c (i.e., LED) on a plane parallel to the cloverleaf PCB, where two of the three LEDs on the cloverleaf PCB are shown. [Figure 18] This is an exemplary embodiment of a photon emitter package for use in a multispectral apparatus that emits at least two distinct emission spectra for the application of photon energy for curing and heating of dental composite materials. [Figure 19] This is an exemplary embodiment of a photon emitter package for use in a multispectral apparatus that emits at least two distinct emission spectra for the application of photon energy for curing and heating dental composite materials. [Figure 20]This graph shows NIR reflectance values ​​compared to the internal temperature of dental materials exposed to a specific photon energy band for 15 seconds from a VishayVCNL4010 sensor (a fully integrated proximity and ambient light sensor with an infrared emitter, I2C interface, and interrupt functionality) obtained from various colored commercially available dental containers. The figure shows the measured NIR reflectance and the temperature change of the object after 15 seconds of exposure to an NIR LED at a constant distance from the sensor (showing a strong correlation between wavelength, power, time, and time (R2=0.97), with all distances between objects kept constant). Therefore, the sensor can be used to determine the amount of photon energy required to heat a given dental material or material container to a desired temperature and, if necessary, maintain that desired temperature over a certain period. Furthermore, the sensor's measurements could serve as a "fingerprint" for identifying the object into which the "platform" system is inserted (i.e., the device will only work with specific materials or material containers). [Figure 21] This graph shows the post-curing microhardness values ​​of the Filtek Supreme Composite when exposed to multispectral light by simultaneously applying photon energy within the disclosed wavelength band and 470 nm light for curing. Asterisks indicate statistically significant differences compared to the "470 nm" group. This figure demonstrates that the addition of photon energy within the disclosed wavelength range enhances the conversion of post-polymerization curing degree and microhardness values. [Figure 22]This graph shows the absorption coefficients of biological tissues at various wavelengths, with oxyhemoglobin, protein, water, and hydroxyapatite being particularly important for teeth. Hydroxyapatite and water exhibit low absorption coefficients relative to commercially available curing light spectra, i.e., peak emission at 470 nm. However, the absorption coefficient of oxyhemoglobin is 1,000 to 10,000 times the absorbance of the disclosed photon energy spectrum, which is why commercially available curing lights raise concerns about temperature rise within the dental pulp and safety. Therefore, the disclosed invention can utilize photon energies from 520 nm to 2,500 nm to increase composite microhardness (Figure 21), reduce oxyhemoglobin and dental pulp absorption, and improve clinical efficacy and safety. [Figure 23] This graph shows the temperature increase of dental composite materials (Grandio SO, VOCO) when photon energy absorbers / dyes are added at various concentrations. When the concentration of LUNIR1 dye was 0.1% or higher, a statistically significant improvement in heating was observed. This figure clearly shows that adding a photon energy absorber to a composite material significantly improves the energy conversion efficiency of photon energy to heat, as evidenced by the substantial temperature increase after approximately 15 seconds of exposure to photon energy. [Figure 24] This graph shows the increase in absorption of a dental composite material (Filtek Supreme) when a photon energy absorber / dye (ICG) is added at various concentrations. Statistically significantly higher absorbance was observed at ICG dye concentrations exceeding 1 ppm. The figure demonstrates that adding a photon energy absorbent dye to a composite material significantly improves the absorption properties of the dental material. This increased absorbance can be targeted to increase the heating rate of the material using photon energy. [Figure 25]The graph shows the heating profiles obtained from polymethyl methacrylate (PMMA) resin, exposed to a constant 940 nm photon energy source for approximately 30 seconds, with and without different absorption dyes incorporated. Temperature measurements were recorded for a total of approximately 60 seconds. The graph shows that by incorporating dyes with higher absorbance values ​​commensurate with the applied photon energy source, the heating rate and overall temperature gain can be significantly increased compared to resins without dyes or resins with low dye / pigment absorption. Furthermore, once the photon energy stops, the material temperature drops easily, as is evident from the rapid decrease in the NIR dye temperature measurement of PMMA between 30 and 60 seconds. This is an additional advantage of the present invention, as the material can cool more quickly once the photon energy stops. Therefore, if a hot material is heated in the apparatus of the disclosed present invention, the power to the apparatus can be turned off, and the material will cool rapidly before being touched. Conversely, commercially available heating units typically heat a metal block, thus maintaining heat for a significantly longer period. The metal block transfers heat to the material primarily by conduction. [Figure 26] This graph shows the microhardness values ​​after curing of a commercially available composite (Ivoclar Evo-Ceram A2 shade) with and without additional photoinitiators (660HNu) and co-initiators (Borate V) at various concentrations, when exposed to curing emission of equivalent total light power. Improvements in microhardness values ​​were observed in Ivoclar Evo-Ceram with the addition of 0.005% 660HNu and 0.05% Borate V, both simultaneously exposed to 470nm and 660nm. This figure demonstrates that polymerization and improvement in microhardness values ​​depend on the concentrations of the additionally incorporated photoinitiators and co-initiators. Furthermore, as shown in Figure 27, a visible color change from green / blue to the standard A2 shade was visualized after photopolymerization of various compositions. In particular, the green / blue color was not noticeable after curing at 660HNu concentrations of 0.05% or less. Therefore, these concentrations can be used to provide clinicians with a visible indicator of complete / successful treatment. Conversely, the 0.1% 660HNu sample after hardening shows residual green / blue coloration, making it unsuitable for aesthetic dental applications. [Figure 27] This figure demonstrates that the color introduced by the incorporated additives is lost during curing, indicating successful / complete curing to the clinician. [Figure 28] This is an isometric view of a delivery device according to another exemplary embodiment of the present invention. [Figure 29] This is an isometric view of a delivery device according to another exemplary embodiment of the present invention. The insert image shows a compal / material container in the receptacle of the device for receiving compal / material containers. [Figure 30] This is a cross-sectional view of a part of the device. The insert image shows the compal / material container in the device's receptacle for receiving the compal / material container, and how the device's plunger contacts the dental material container to push out the dental material. [Figure 31] This is a cross-sectional view of the isometric lateral profile image in Figure 25. [Figure 32] Figure 24 is an exploded view of the device, showing various components of the device. [Figure 33] This is an isometric cross-sectional view of a multispectral curing light apparatus according to one exemplary embodiment of the present invention. [Figure 34] A bottom view of a multispectral curing light apparatus according to an exemplary embodiment of the present invention. [Figure 35] This is an exemplary embodiment of a package comprising at least three photon emitters (i.e., LEDs) for use in a multispectral device that emits at least two distinct emission spectra for the application of photon energy for curing and heating dental composite materials. [Figure 36]This graph shows the absorbance versus wavelength characteristics of an exemplary embodiment of the present invention for a dental material container, in which a photon energy absorbing dye (Epolite 7657) with high absorbance from approximately 800 nm to approximately 1100 nm and less than 550 nm is incorporated into the thermoplastic resin (polycarbonate) (sample thickness is 2 mm). Since this dye / additive simultaneously provides high absorbance within the photon energy range, it is possible to increase the heating rate of the container and / or material using a photon energy emitter, and to target in the blue light range (400-500 nm), effectively blocking polymerization light from photopolymerizing the dental material inside the container. [Figure 37] This block diagram shows a generalized functional component of one exemplary apparatus used for heating, controlling, and identifying dental materials and / or dental material containers. The temperature of the dental materials and / or dental material containers can be controlled and maintained using a sensor feedback loop. Furthermore, sensors can be used to ensure that a photon energy source emits photon energy only when the material or container is present. Finally, sensors can be used to specifically identify different materials and / or containers based on feedback. [Modes for carrying out the invention]

[0018] The following paragraphs further define embodiments of the invention as described herein. The following embodiments are not intended to limit or narrow the scope of the invention, as will be readily apparent to those skilled in the art, that appropriate modifications and adaptations can be made without departing from the specific aspects, embodiments, or scope of the invention described herein. All patents and publications referenced herein are incorporated herein by reference in their entirety.

[0019] For the purposes of interpreting this specification, the following terms and definitions apply, and where appropriate, a singular term also includes a plural form, and vice versa. In the event of any conflict between the following definitions and any documents incorporated herein by reference, the following definitions shall prevail.

[0020] As used herein, the terms “room temperature” or “ambient temperature” refer to typical ambient temperatures ranging from approximately 20°C to approximately 27°C.

[0021] The term "to treat" refers to administering treatment in an amount, method, or manner that is effective in improving a condition, symptom, or parameter associated with a disorder. In some aspects, treatment refers to the treatment of dental diseases such as tooth decay.

[0022] The term "prevention" refers to preventing or reducing the progression of a disability to a statistically significant extent or to an extent detectable by a person skilled in the art.

[0023] As used herein, the term “substantially” means to the majority or a considerable extent, but not entirely.

[0024] As used herein, "a" or "an" means one or more unless otherwise specified.

[0025] Terms such as "to include," "to consist of," "to have," and "to possess" all mean "to include." The terms "patient" or "subject" refer to mammals and humans. Therefore, in one aspect, the subject is a mammal, or a mammal that needs it. In one aspect, the subject is a human, or a human that needs it. In one aspect, a human, or a human that needs it, is a medical patient. Subjects range in age from 0 to 99 years or older.

[0026] This specification describes methods for applying photon energy to heat dental materials and housings or containers for dental materials. This specification also describes dental material compositions and dental material containers or housings having enhanced heating and photopolymerization properties based on the inclusion of heating additives and photopolymerization accelerator systems. Further described herein are apparatuses capable of applying specific wavelengths of photon energy to heat, deliver, and cure dental compositions (e.g., dental compositions disclosed herein). This specification also describes methods for treating patients using the methods and apparatus disclosed herein. While examples or embodiments may discuss or specifically relate to particular uses or aspects of the invention, it is understood that examples or embodiments may further relate to and be conceivable to other detailed aspects of the invention. For example, a particular apparatus or method may be discussed in relation to dental composite materials, but the same apparatus or method may generally be applicable to other dental materials.

[0027] The inventors report that using photon energies of 0.49 eV to 2.38 eV (i.e., 2500 nm to 520 nm), 0.49 eV to 1.90 eV (i.e., 2500 nm to 650 nm), or 1.23 eV to 2.06 eV (i.e., 1000 nm to 600 nm) can enhance the handling, mechanical, and performance properties of dental materials with high conversion efficiency. Dental materials include, but are not limited to, composite materials, resins, glass ionomer resins, cements, cavity liners, endodontic lining agents, endodontic closure materials, gutta-percha, anesthetics, and sealants. Accordingly, the inventions described herein include methods for heating dental materials, methods for improving the polymerization of photopolymerizable dental materials, dental material heating and delivery devices, dental material heating and curing devices, and dental material compositions.

[0028] Photon energies outside the specified range of 0.49 eV to 2.38 eV (i.e., 2500 nm to 520 nm) are still envisioned by the present invention to enhance the handling, mechanical, and performance characteristics of dental materials with high conversion efficiency. In particular, ultraviolet wavelengths have high photon energies (specifically, ultraviolet A wavelengths: 315 nm to 400 nm, 3.93 eV to 3.09 eV), and the use of ultraviolet is available because many materials exhibit inherently high absorbance below 400 nm. Other wavelengths are also possible, as wavelengths below 400 nm may have adverse effects on dental materials, especially photopolymerizable dental materials, and there are potential safety concerns due to ionization, but some specific embodiments described further here utilize photon energies within the specified range of 0.49 eV to 2.38 eV (i.e., 2500 nm to 520 nm). Of particular concern is the photopolymerization of dental materials, which can occur when ultraviolet light is directly applied to the material itself. However, in some embodiments, ultraviolet light can be used to heat the container of the dental material if the container has an optical density value of at least 2 for wavelengths below 400 nm. That is, the container of the dental material transmits less than 1% of light below 400 nm. Conversely, in some other embodiments, ultraviolet light can be used on other non-photopolymerizable dental materials, particularly endodontic cleaning agents, to improve their performance properties through photochemical effects.

[0029] (A method of applying photon energy to heat dental materials) Several embodiments described herein are methods for heating dental materials to temperatures above ambient temperature using photon energy without adversely affecting the dental materials. One embodiment is a method for rapidly heating dental materials to temperatures above ambient temperature by heating them with photon energy in the range of 0.49 eV to 2.38 eV (i.e., 2500 nm to 520 nm). In some embodiments, the dental material is heated to a temperature of about 50°C to about 250°C. In some embodiments, the dental material is heated to a temperature of about 50°C to about 100°C. In some other embodiments, the dental material is heated to a temperature of 60°C to about 80°C. In some embodiments, the applied photon energy is 1.23 eV to 2.06 eV (1000 nm to 600 nm). In some embodiments, the photon energy for heating the dental material is applied before the application of the dental material. Other photon energy wavelengths can be utilized by adjusting the photon energy applied to the fundamental absorption frequency / wavelength and / or harmonic vibration band of the dental material or the container of the dental material. In particular, resonant frequencies exceeding the fundamental frequency are called harmonics. In the electromagnetic spectrum, the harmonic bands are multiples of the fundamental absorption frequency. Since energy is proportional to the absorbed frequency, and that frequency is proportional to the wave number, the first harmonic appearing in the spectrum will have a wave number approximately twice that of the fundamental wave. In other words, the first harmonic v=1→2 has approximately twice the energy of the fundamental wave, and v=0→1. For example, a vibrating diatomic molecule such as hydrochloric acid (HCl), which has a fundamental absorption at 3465 nm, will have its first harmonic absorption band at 1733 nm (actually observed at 1764 nm), its second at 1155 nm (actually observed at 1198 nm), its third at 866 nm (actually observed at 915 nm), and its fourth at 693 nm (actually observed at 746 nm). Therefore, to obtain equivalent vibrational motion, a much larger amount of energy is required in the first harmonic compared to the energy required at the fundamental absorption frequency / wavelength. As molecular vibrations increase, heat is generated, so objects and materials can be heated by targeting the basic absorption and / or harmonic ranges.

[0030] With regard to dental materials, the basic absorption band is typically outside the specified photon energy range (0.49 eV to 2.38 eV, i.e., 2500 nm to 520 nm). Therefore, the harmonic band of dental materials is targeted by several embodiments described herein. Specifically, when photopolymerizable dental materials (i.e., composites, resins, cements, sealants, etc.) are applied before or during use (i.e., in vivo), the material heats up faster than ambient temperature, but does not prematurely cure or adversely affect the photopolymerizable material before or after curing, which may occur if the applied photon energy activates a photoinitiator incorporated into the material.

[0031] Clinically, heated photopolymerizable materials are advantageous because their improved fluidity facilitates the application and adhesion of the photopolymerizable material to the tooth surface. This same concept generally applies to all dental materials. Furthermore, it has been shown that the mechanical properties of photopolymerizable materials can be improved by adding photon energy during or immediately before curing to increase the temperature, resulting in improved post-curing properties (conversion degree and microhardness) compared to standard curing. Therefore, in some embodiments described herein, the applied photon energy is at a wavelength different from the absorption peak used to activate the photoinitiator of the photopolymerizable material.

[0032] The type and amount of photon energy applied to dental materials for desired heating can be determined based on the absorption harmonic regions of various components (such as molecules and bonds). For example, various components and their respective harmonic regions are shown in Figure 1. Since most components have absorption in multiple harmonic regions, some embodiments relate to applying photon energy to these composite materials by utilizing the combined harmonic band region, the primary absorption band wavelength, which falls within the range of 0.49 eV to 2.38 eV (i.e., 2500 nm to 520 nm). In some embodiments, the photon energy utilized is 1.23 eV to 2.06 eV (i.e., 10 (00nm to 650nm).

[0033] In some embodiments, the applied photon energy lies in a third harmonic region, or a higher harmonic, or in other component absorption characteristics within a specific photon energy range / wavelength, providing specific advantages with respect to the degree and rate of heating that can be achieved without excessively high energy requirements. The disclosed embodiments are highly efficient in converting energy from a power source into heat using photon energy tuned for dental materials and / or dental material containers.

[0034] While current existing LED technology can achieve photon emission in the third harmonic band, emission of photons in the first or second harmonic band requires diode lasers and is far more expensive for much lower light energy output. Essentially, shorter wavelengths of light have higher frequencies and higher photon energies. Considering the relationship between wavelength and frequency, higher frequencies correspond to shorter wavelengths. Therefore, shorter wavelengths have higher energy than longer wavelengths. Thus, in certain cases, absorbance may be lower, but the third harmonic possesses high energy, allowing for the utilization of wavelengths that exhibit more effective and efficient heating characteristics. Furthermore, by using information about the components used in the composite material, specific wavelengths within a selected region can be directed onto the composite material to efficiently influence heating at the wavelengths where molecular and bond absorption is highest.

[0035] In some embodiments, photon energy is applied to dental materials including anesthetics (to reduce pain during injection), gutta-percha (for endodontic root canal occlusion), dental composites, sealants, cements, cavity liners, and glass ionomer resins (e.g., reduced viscosity, improved handling properties, reduced voids, and improved mechanical properties after curing), and endodontic irrigators (increased efficacy and reactivity).

[0036] Therefore, in some embodiments, the photon energy specified herein is applied using an apparatus specifically configured for the efficient heating of dental material samples.

[0037] (A method of improving the performance or reactivity of a material by applying photon energy.) One embodiment is a method of applying photon energy to dental materials to enhance the material's properties or reactivity through the photochemical effect. This method is distinctly different from photodynamic therapy or the use of photosensitizers. One aspect involves using a specific range of photon energy on photopolymerizable dental materials, thereby further improving the mechanical properties of the dental materials. Without being bound by theory, this can be done using the two-photon effect if the appropriate wavelength or electron volt is suitable for the photoinitiator. For example, to polymerize a material containing camphoroquinone via the two-photon effect, photon energy is applied in the 880 nm to 960 nm band.

[0038] Another embodiment involves the use of photon energy to stimulate photochemical effects, including photodegradation of dental materials (i.e., changes in materials by light that may include oxidation and free radical generation), photofading (i.e., reduction or removal of the visible color or fluorescent properties of a pigment due to photochemical changes in the pigment), or photocatalysis (i.e., acceleration of chemical reactions by light). Clinically, this may help to enhance disinfectant properties, aesthetic properties, and safety. With respect to endodontic irrigators, the application of photon energy can be used to enhance the disinfectant properties of commonly used irrigators such as sodium hypochlorite and chlorhexidine, where reactivity or free radical generation is increased by photon energy of specific wavelengths. The above methods can be further enhanced by incorporating additives into dental materials, which are further described herein.

[0039] (Additives for improving heating by increasing energy conversion efficiency and heat transfer) Another embodiment involves adding one or more heating additives to a dental material or a dental material container. This includes methods for improving the heating of dental materials. In some embodiments, the heating additive is a photon energy absorption enhancer or a thermal conductivity enhancer. As described herein, heating additives containing specific photon energy absorption enhancers (such as absorption dyes) and thermal conductivity enhancers are added to dental materials and / or containers of dental materials to increase the absorption of photon energy, the energy conversion efficiency from photon energy to heat, and / or the heating rate of the material. In some embodiments, the methods described herein include adding one or more heating photon energy absorption enhancers, one or more thermal conductivity enhancers, or any combination thereof to dental materials or containers of dental materials.

[0040] A suitable photon energy absorption enhancer exhibits one or more of the following properties: high absorbance between 0.49 eV and 2.38 eV (i.e., 2500 nm to 520 nm), high UV-A absorption between 3.93 eV and 3.09 eV (315 nm to 400 nm), biocompatibility, no unnatural tooth coloration of the material, compatibility with the material and / or container, stability, thermal stability (e.g., when used in injection molding), solubility and dispersibility within the material and / or container, no adverse effect on the material's performance, and high efficiency in converting photon energy to heat, or a combination of these properties. UV-absorbing additives are advantageous to use because many UV-absorbing dyes are colorless; however, other dyes absorbing 0.49 eV to 2.38 eV are also colorless or may impart an acceptable color to dental materials. For example, additives that impart a slightly yellow or yellowish-brown color may be acceptable in the range of slightly yellow or yellowish-brown shades of dental materials. Exemplary and non-limiting photon energy absorption enhancers that meet some of the above characteristics include the following dye classifications: cyanines, polycyanines, fluorones, amminium, trisaminonium, metal dithiolene complexes, antroquinones, perialylenes (i.e., cesterylene and ceterylenetetracarboxylate bisimide), squaline, phthalocyanines, phthalocyanine metal complexes, polymethine cyanines, porophilin, chlorine, benzochlorine, thiadin, quantum dots, and single-walled carbon nanotubes. Suitable commercially available dyes that meet one or more of the aforementioned criteria include, but are not limited to, Cy3, Cy5, fluorescein, indocyanine green, methylene blue, toluidine blue, Luminochem absorption dyes (e.g., LUNIR8 / 1; Budapest, Hungary), and absorption dyes from eporin. Specifically, Epolite 4113, 4831, 4019, 7809, 4105, 3130, 3169, 3036, 4019, 4129, 4113, 5262, 5839, 6661, 6158, 5636, 6084 (Newark, New Jersey), and QCR Solutions' absorbent dyes (NIR806F, NIR856A, NIR886A, NIR848A, NIR949A, NIR728A, NIR700A, NIR739B, Port St. Lucie, Florida is preferred). Below are the structures of Cy3 and Cy5, and higher wavelength cyanine dyes share similar structures, which is advantageous because cyanine dyes have been shown to be biocompatible. [ka] Absorbing cyanine pigments (Cy3 and Cy5)

[0041] In another embodiment, the photon energy absorption enhancer is added to the dental material or a container for the dental material at a concentration that yields an absorbance / optical density value of 1 or more, and at a photon energy within the disclosed photon energy range.

[0042] The selected photon energy absorption enhancer, the spectrum of the photon energy absorption enhancer, and the spectrum of the photon energy source represent important aspects for achieving the desired overall heating performance. Referring to Figure 2, the area intersection (A3) of the normalized absorbance (A1) spectrum of the photon energy absorption enhancer and the normalized emission spectrum (A2) of the photon energy source must have at least some overlap to achieve improved photon energy absorption and subsequent heating. In one embodiment, the area intersection of the normalized absorbance spectrum of the photon energy absorption enhancer and the normalized emission spectrum of the photon energy source must be at least 10% of the area under the curve of the additive or photon energy source. In another embodiment, this area intersection is at least 25%. In yet another embodiment, this area intersection (A3) is at least 50%.

[0043] In another embodiment, one or more photon energy absorption enhancers are added to the dental material at a concentration of approximately 0.001% to 10% (weight%) in order to enhance the photon energy absorption of the dental material. In another embodiment, one or more photon energy absorption enhancers are added to the dental material at a concentration of approximately 0.005% to 7% (weight%). In another embodiment, one or more photon energy absorption enhancers are added to the dental material at a concentration of approximately 0.01% to 3% (weight%). In yet another embodiment, one or more photon energy absorption enhancers are added to the dental material at a concentration of approximately 0.01% to 1% (weight%). In another embodiment, one or more photon energy absorption enhancers are added to the dental material at concentrations of approximately 0.001%, approximately 0.005%, approximately 0.01%, approximately 0.05%, approximately 0.1%, approximately 0.2%, approximately 0.4%, approximately 0.8%, approximately 1%, approximately 2%, approximately 3%, approximately 4%, approximately 5%, approximately 6%, approximately 7%, approximately 8%, approximately 9%, or approximately 10% (by weight).

[0044] In another embodiment, one or more photon energy absorption enhancers are added to the dental material container at a concentration of approximately 0.1% to 25% (weight%) in order to enhance the photon energy absorption of the dental material container. In another embodiment, one or more photon energy absorption enhancers are added to the dental material container at a concentration of approximately 0.1% to 20% (weight%). In another embodiment, one or more photon energy absorption enhancers are added to the dental material container at a concentration of approximately 0.1% to 15% (weight%). In another embodiment, one or more photon energy absorption enhancers are added to the dental material container at a concentration of approximately 0.1% to 10% (weight%). In another embodiment, one or more photon energy absorption enhancers are added at a concentration of approximately 0 In another embodiment, one or more photon energy absorption enhancers are added to the dental material container at a concentration of 0.1% to 5% (by weight). In yet another embodiment, one or more photon energy absorption enhancers are added to the dental material container at a concentration of approximately 0.1% to 1% (by weight).

[0045] In another embodiment, one or more thermal conductivity enhancers are added to the dental material. A suitable thermal conductivity enhancer improves the thermal conductivity of the material and / or the material container. This allows heat to disperse more quickly throughout the material and / or the material container, or improves the thermal conductivity between the material and the container. Exemplary and non-limiting additives that improve thermal conductivity include graphite particles, graphene particles, ceramic particles (such as metal nitrides, boron nitride, silicon carbide, silicon nitride, etc.), metal oxide particles (such as aluminum oxide), metal particles, carbon, and carbon nanotubes. In another embodiment, one or more thermal additives are added to the dental material at a concentration of about 0.01% to 80% (weight %). In another embodiment, one or more thermal additives are added to the dental material at a concentration of about 0.01% to 50% (weight %). In another embodiment, one or more thermal additives are added to the dental material at a concentration of about 0.01% to 30% (weight %). In another embodiment, one or more heat-heating additives are added to the dental material at a concentration of approximately 0.01% to 10% (by weight). In yet another embodiment, one or more heat-heating additives are added to the dental material at a concentration of approximately 0.01% to 1% (by weight).

[0046] In another embodiment, one or more thermal conductivity enhancers are added to the dental material container. A suitable thermal conductivity enhancer improves the thermal conductivity of the material and / or the material container. This allows heat to disperse more quickly throughout the material and / or material container, or improves thermal conductivity between the material and the container. Exemplary and non-limiting additives that improve thermal conductivity include graphite particles, graphene particles, ceramic particles (such as metal nitrides, boron nitride, silicon carbide, silicon nitride, etc.), metal oxide particles (such as aluminum oxide), metal particles, carbon, and carbon nanotubes. In another embodiment, one or more thermal additives are added to the dental material container at a concentration of about 0.01% to 80% (weight %). In another embodiment, one or more thermal additives are added to the dental material container at a concentration of about 0.01% to 50% (weight %). In another embodiment, one or more thermal additives are added to the dental material container at a concentration of about 0.01% to 30% (weight %). In another embodiment, one or more heat-heating additives are added to the dental material container at a concentration of approximately 0.01% to 10% (by weight). In yet another embodiment, one or more heat-heating additives are added to the dental material container at a concentration of approximately 0.01% to 1% (by weight).

[0047] (Additives for improving the polymerization of materials (photoinitiators and co-initiators)) In another embodiment, the photopolymerization enhancer system is incorporated into a photopolymerizable dental material composition. Including such a system allows for the use of photon energy to enhance polymerization, curing depth, and conversion degree. Because the photopolymerization enhancer system described herein includes a type I photoinitiator and a type II photoinitiator containing a co-initiator, or two type II photoinitiators containing co-initiators, the photopolymerization enhancer system described herein is distinctly different from other known photopolymerization systems in that at least one type I or type II photoinitiator is activated within a suitable range of photon energies. In some embodiments, the range of photon energies in which at least one of the photoinitiators is activated is approximately 0.49 eV to 2.38 eV (2500 nm to 520 nm), which is referred to herein as a “specific photoinitiator”.

[0048] In one embodiment, the photopolymerization accelerator system comprises a type I photoinitiator and a type II photoinitiator, each containing at least one co-initiator, wherein at least one or all of the photoinitiators are specific photoinitiators. In another embodiment, the photopolymerization accelerator system comprises two type II photoinitiators, each containing at least one co-initiator, wherein one or all of the photoinitiators are specific photoinitiators. In yet another embodiment, the co-initiators are present at a concentration equal to or greater than that of the specific photoinitiator. In one embodiment, the co-initiator and other unspecified photoinitiators are present at a concentration equal to or greater than that of the specified photoinitiator. In another embodiment, the combination of the co-initiator and other unspecified photoinitiators is present at a concentration equal to or greater than that of the specified photoinitiator. In another embodiment, at least one of the co-initiators is borate V. In another embodiment, the specified photoinitiator is incorporated at a concentration of about 0.0001% to 2% by weight of the entire photopolymerizable dental material. In another embodiment, the specified photoinitiator is incorporated at a concentration of about 0.0001% to 1% by weight of the entire photopolymerizable dental material. In another embodiment, the specified photoinitiator is incorporated at a concentration of about 0.0001% to 0.5% by weight of the entire photopolymerizable dental material.

[0049] In another embodiment, the photopolymerization accelerator system comprises a type I photoinitiator and a type II photoinitiator, or two type II photoinitiators, each containing at least one co-initiator, wherein the particular photoinitiator is incorporated at a concentration of 0.0001% to 0.5% by weight of the entire photopolymerizable dental material, the co-initiators and other photoinitiators are present at concentrations equal to or greater than the concentration of the particular photoinitiator, and at least one of the co-initiators is borate V. In another embodiment, the photopolymerization accelerator system comprises a type I photoinitiator and a type II photoinitiator, each containing at least one co-initiator, or two type II photoinitiators, each containing at least one co-initiator, wherein the particular photoinitiator is incorporated at a concentration of 0.001% to 0.1% by weight of the entire photopolymerizable dental material, at least one of the co-initiators contains borate V at a concentration equal to or greater than that of the particular photoinitiator, and the other photoinitiators are present at concentrations equal to or greater than that of the particular photoinitiator.

[0050] In another embodiment, certain photoinitiators or co-initiators added to photopolymerizable dental materials may lose their visible color (i.e., become bleached or colorless) as a result of applying photon energies of 0.49 eV to 1.90 eV (2500 nm to 650 nm) or 1.23 eV to 2.06 eV (1000 nm to 600 nm) and / or are consumed during the photopolymerization process that occurs after the application of photon energies of 0.49 eV to 1.90 eV (2500 nm to 650 nm) or 1.23 eV to 2.06 eV (1000 nm to 600 nm). During clinical application, photopolymerizable dental materials (e.g., dental composites) start as a distinct color and change to the desired tooth shade upon curing. This property allows clinicians to visually confirm that the material has fully cured.

[0051] In another embodiment, a particular photoinitiator absorbs photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm) and is photobleached or becomes colorless. In yet another embodiment, a particular photoinitiator promotes the curing of the material by increasing radical formation, and simultaneously bleaches as the formed radicals are depleted. Thus, in some embodiments, a particular photoinitiator participates in the curing process and provides a visible change indicating complete curing. In these embodiments, the particular photoinitiator is used in combination with another photoinitiator and / or coinitiator at concentrations disclosed herein.

[0052] Exemplary and non-limiting Type I photoinitiators that can be used in combination with specific photoinitiators include TPO (diphenyl(2,4,6-trimethylbenzoyl)phosphine oxide), 2-benzyl-2-(N,N-dimethylamino)-1-(4-morpholinophenyl)-butan-1-one (BDMB), 2,2-dimethoxy-2-phenylacetophenone (DMPA), bisacylphosphine oxide (BAPO), acylgermane derivatives, benzoin ethers, benzyl ketals, α-dialkoxyacetophenone, α-hydroxyalkylphenone, α-aminoalkylphenone, acylphosphine oxides, and fluoro dyes. Exemplary and non-limiting Type II photoinitiators that can be used in combination with specific photoinitiators include 1-phenyl-1,2-propanedione (PPD), camphoroquinone (CQ), ethyl-4-(dimethylamino)benzoate (EDB), benzyl (BZ), and cyanine dyes. Additional suitable photoinitiators that can be used in combination with specific photoinitiators include: This includes cetophenone, titanocene, Germanine compounds, benzophenone derivatives, dibenzoylferrocene, iridium complexes, pyrene derivatives, thiobarbituric acid derivatives, benzyl and benzoin compounds, benzophenone, thioxanthone, sulfonium, iodonium, perialylene (especially sexterylene, especially sectorylenetetracarboxylate bisimide), squaline, phthalocyanine and phthalocyanine metal complexes, polymethine cyanine, porophilin, chlorine, benzochlorine, thiadin, and cyanine-based photoinitiators shown as structure S1. Commercially available photoinitiators include those from Spectra Group Limited, Inc. (H-Nu 660, H-Nu 780, H-Nu This includes, but is not limited to, 815). [ka]

[0053] An exemplary and non-limiting class of co-initiators that can be used with Type I and certain photoinitiators, or with Type II and certain photoinitiators, includes amine-based co-initiators (e.g., ethyl-4-dimethylaminobenzoate (DMABE), 4-dimethylaminobenzonitrile (DMABN), 2-N,N-dimethylaminoethyl methacrylate (DMAEMA), or other pyridinium-based compounds), borate-based co-initiators (e.g., butyltriphenylborate, called borate V, tetrabutylammonium tetrafluoroborate), and iodonium salts. Commercially available co-initiators include, but are not limited to, those of Spectra Group Limited, Inc. (e.g., borate V, iodonium salt H-Nu 254).

[0054] (Additives to improve the reactivity of materials (photocatalysts)) Another embodiment includes a method for improving the reactivity of dental materials by incorporating one or more photocatalysts. The incorporation of photocatalysts is thought to absorb the applied photon energy and function as a photocatalyst that enhances other dental material properties. Exemplary and non-limiting photocatalysts include metal oxides, etc. A potential application of this photocatalyst is to place the metal oxide in an endodontic lining or mouthwash and expose it to photon energy to improve disinfection.

[0055] (Methods of treating patients with dental materials) Another embodiment described herein is a method for treating a patient with a dental material, comprising the steps of: heating the dental material above ambient temperature using a device that uses photon energy from a photon energy emission source; and applying the heated dental material to the surface of a tooth or a dental cavity before the material hardens (if applied, i.e., before the dental photopolymerization material hardens).

[0056] As described in this book, photon energies include energies of approximately 0.49 eV to 2.38 eV (2500 nm to 520 nm) or approximately 1.23 eV to 2.06 eV (1000 nm to 600 nm). In one embodiment, the dental material is a dental photopolymerizable material. In another embodiment, the emitted photon energy for heating the dental material is at an appropriate absorption wavelength of the dental material, dental material container, or heating additive described herein, without prematurely curing or polymerizing the material.

[0057] Dental light-curing materials include composite resins, high-filler composite resins, glass ionomer resins, and sieves. This includes rants, cements, cavity liners, or combinations thereof. A method of treating a patient, following the step of applying a heated dental material, further includes a step of curing the dental material. In one embodiment, the curing step further includes a step of applying a second photon energy source having the absorption spectrum of a photopolymerizable material present in the dental material to initiate polymerization. Thus, in this embodiment, during the treatment of the patient, the photon energy applied to heat the dental photopolymerizable material does not overlap with the absorption of the photoinitiator present in the dental photopolymerizable material.

[0058] (Device for heating and dispensing dental materials) The apparatus of the present invention described herein enables the creation of dental composite materials with higher filler content. Higher filler content results in less shrinkage during curing, greater hardness, higher wear resistance, and longer-lasting restorations. However, highly filled composite materials have limited use due to their low fluidity, high dispensing force, low moldability, and poor limit fit. Preheating photopolymerizable materials reduces viscosity, rearranges the molecular structures of fillers and monomers, and reduces internal stress and heterogeneity, thereby improving the clinical use of highly filled composite materials. Furthermore, preheating photopolymerizable materials and curing them at high temperatures increases the volume expansion (i.e., thermal expansion) of the composite material, which can offset the volume reduction due to polymerization. This significantly reduces shrinkage, leakage, stress, and postoperative pain of the composite material.

[0059] Therefore, another embodiment is a device capable of emitting photon energy in the range of 0.49 eV to 2.38 eV (i.e., 2500 nm to 520 nm) and can be used to heat and / or distribute dental materials. In one embodiment, the photon energy utilized is between 1.23 eV to 2.06 eV (1000 nm to 600 nm) or 1.23 eV to 1.77 eV (i.e., 1000 nm to 700 nm) for heating and distributing dental materials, and the applied photon energy is invisible to the human eye and therefore safer. The photon energy source is limited to an electroluminescent source such as a light-emitting diode (LED) or laser diode, providing 0.5 W to 20 W or 1 W to 8 W of optical power.

[0060] Suitable devices described herein are cordless and may further incorporate a rechargeable energy source such as a lithium-ion battery, supercapacitor, lithium polymer battery, nickel-cadmium battery, or nickel-metal hydride battery. In another embodiment, the device includes a computer or container containing dental material. After application of the dental material, the compal can be removed from the device and replaced with another compal or container for subsequent applications in the same procedure or subsequent procedures.

[0061] In another embodiment, the photon energy source is positioned close to the compar or container to ensure efficient energy transfer. In another embodiment, the distance between the photon energy source and the compar or container is less than 1 cm. Alternatively, in another embodiment, the photon energy source is collimated via a lens or optical fiber to ensure the transfer of higher energy to the compar or container and / or to allow the photon energy source to be positioned at a greater distance from the compar or container.

[0062] In another aspect, the tool or wand effectively manages the thermal properties of the photon energy source to prevent degradation of dental materials or to avoid dangerous high temperatures for the operator or patient being treated with the device. This can be achieved by placing the photon energy source in a primary heatsink such as a printed circuit board or a metal-clad printed circuit board, the primary heatsink being contained within the device housing or further coupled to secondary or tertiary heatsinks that make up the device housing. Furthermore, the use of heat pipes facilitates thermal management. With proper thermal management, surfaces that can come into contact with the device body are generally kept cool in the case of medical devices. It will not reach dangerously high temperatures, which are defined as temperatures exceeding approximately 50°C.

[0063] In another embodiment, to minimize the adverse effects of excessive or undesirable temperatures on the dental material, the device includes a sensor that controls the applied photon energy. As detailed in the block diagram shown in Figure 37, a temperature sensor is used to monitor the temperature of the dental material in the tool / wand during the application of photon energy, determine when the object reaches the desired temperature, and feed this information back to the applied photon energy source to reduce or disconnect the emitter output. Exemplary and non-limiting temperature sensors include thermistors, IR temperature sensors, thermopiles, thermocouples, or resistance temperature detectors (RTDs). The temperature sensor is not only part of the device, but also part of the object being heated. This can be done by embedding a thermistor in the object, or by creating the object from a material that changes its electrical properties (resistance, capacitance, or inductance) in relation to temperature changes, and then electrically connecting it to the device. Suitable temperature sensors are available from Vishay Dale (TFPT), Panasonic (AMG88), Texas Instruments (TMP007), Digilent, Inc. (240-080), and TE Connectivity (Ni1000SOT).

[0064] Furthermore, once the object reaches the desired temperature, the device is expected to maintain that temperature without reaching undesirable temperatures that could adversely affect the dental material, using pulse-width modulation (PWM), proportional-integral-derivative controllers (PID), or another control-loop feedback system approach. Additionally, to account for the difference between the absorbance of the dental material and the required power, and the time to reach the desired temperature, another sensor can be used, either in place of or in addition to the temperature sensor, to determine the object's absorptivity and adjust the power to the photon energy source accordingly. This can be achieved by directly or indirectly determining the object's absorption or color for a particular wavelength of photon energy by measuring reflectivity or transmittance using a thermopile, RGB sensor, proximity sensor, phototransistor, photodiode, ambient light sensor, CMOS sensor, or CCD sensor. Suitable sensors are available from Vishay Semiconductor (VCNL4020X01, VEML6040), Rohm Semiconductor (BH1680FVC), Texas Instruments (TMP007), Everlight Electronics Co Ltd (PD15-22C / TR8), Kingbright (APA3010P3BT), OmniVision Technologies Inc. (OV09740-A46A), and Toshiba (TCD1103GFG).

[0065] Furthermore, the sensor's measurements can function as a "fingerprint," identifying the inserted object, container, or material for implementing a closed-platform system. Therefore, the same sensor used for absorption measurement, or a separate implementation of one of the aforementioned sensors, can be configured so that the sensor's measurements only work with the manufacturer's specific object, container, or material. This allows manufacturers to use the device to heat only their own products. Additionally, as a safety feature, the device can be incorporated to use one of the aforementioned sensors to determine the presence of an object before or during heating, and to emit photon energy only if an object is present.

[0066] In another embodiment, the apparatus used for heating and distribution comprises a curing light source of 365 nm to 500 nm and additional photon energy sources of 0.49 eV to 2.38 eV (i.e., 2500 nm to 520 nm), 1.23 eV to 2.06 eV (i.e., 1000 nm to 600 nm), or 1.24 eV to 1.77 eV (i.e., 1000 nm to 700 nm) that can be activated and directed toward the composite after the composite has been applied, in order to heat and / or cure the coated composite. Both the curing light source and the photon energy sources are 50 each. The light emits a light power of 0mW to 3W or 700mW to 1.5W. In another embodiment, the photon energy is applied before, simultaneously with, or after a short delay of about a few seconds compared to the curing light source, and the properties of the resulting dental composite material can be tuned. The photon energy is absorbed directly by the composite material (i.e., components within the composite material such as monomers and fillers, or incorporated additives), or by any of the aforementioned additives which can also be used for heating before curing, to heat the dental material during curing.

[0067] In another embodiment, the curing light and photon energy source are positioned distally to the device to facilitate access within the oral cavity. Alternatively, in another embodiment, the curing light and / or photon energy source are collimated via a lens or optical fiber to ensure higher energy transfer to the placed material and / or to allow the curing light and photon energy source to be positioned non-distal to the device. The device effectively thermally manages the curing light and photon energy source to prevent them from becoming excessively hot, which would degrade dental composite materials and be dangerous to the operator of the device or the patient being treated with the device. This can be achieved by placing the photon energy source on a primary heatsink (printed circuit board or metal-clad printed circuit board), which may be included in the device housing or further coupled to a secondary or tertiary heatsink comprising the device housing / body. Furthermore, the use of heat pipes facilitates thermal management. Clinically, the disclosed use and method of use of the photon energy device can improve surface hardness, degree of conversion, depth of curing, reduce shrinkage and leakage, improve the stepwise layering and curing of restorative materials, and improve the efficiency of the procedure. In another embodiment, this can also be achieved with a separate device that does not distribute dental materials and is limited to curing photopolymerizable materials, i.e., multispectral curing light.

[0068] One embodiment described herein is the apparatus shown in any one of Figures 14-16 or 28-32. In one embodiment, the apparatus has a photon emitter package shown in any one of Figures 17-19 or 35.

[0069] (A device that accelerates the hardening of photopolymerizable dental materials) According to another embodiment of the present invention, a tool or wand can use photon energy to heat a photopolymerizable dental material above ambient temperature, thereby curing the photopolymerizable dental material. This results in high-temperature curing of the photopolymerizable dental material in situ and / or in vivo, which provides significant benefits to the mechanical properties of the photopolymerizable dental material. In one embodiment, the device has a thermally conductive body, and in another embodiment, the device is elongated to facilitate easy access in the mouth. In addition, the device includes at least four individual distally mounted photon energy emission sources that produce at least two individual emission spectra. In one embodiment, these photon energy emission sources consist of light-emitting diodes (LEDs). At least one LED emission spectrum is used to cure the photopolymerizable dental material, and at least one LED emission spectrum is used to raise the temperature of the photopolymerizable dental material above ambient temperature before or during curing. In one embodiment, the emission source for curing the photopolymerizable dental material emits light in the 365 nm to 500 nm range with a light power of 500 mW to 3 W. In another embodiment, the light source for curing the photopolymerizable dental material emits light in the 420nm to 490nm range with a light power of 700mW to 1.5W. In yet another embodiment, the light source for raising the temperature of the photopolymerizable dental material above the ambient temperature during curing emits light in the 520nm to 2500nm range with a light power of 500mW to 3W. In yet another embodiment, the light source for raising the temperature of the photopolymerizable dental material above the ambient temperature during curing emits light in the 600nm to 1000nm range with a light power of 700mW to 2W.

[0070] The spatial orientation of these at least four LEDs ensures a nearly uniform beam profile, and it was found that the light power does not vary significantly across the illumination field. In one embodiment, one LED is positioned in the center of the distal head of the device, and at least three The LEDs are arranged radially around a centrally located LED. These at least four LEDs can be located on the same PCB or on separate parallel PCBs (see Figures 17-19 and 35), and on the same plane or on separate parallel planes. However, in another embodiment, the at least four LEDs radiate beam profiles in approximately the same direction, so the beam profiles can be collimated to provide a uniform illumination field. Furthermore, when incorporating three or more LEDs radially, the spacing between the LEDs (i.e., angular separation) must be equal to obtain a uniform beam profile. For example, three LEDs should be separated by an angle of approximately 120° (see Figures 17 and 35), four LEDs by an angle of approximately 90°, and five LEDs by an angle of approximately 72°. In another embodiment, one centrally located LED is contained on its own PCB surrounded by three LEDs contained on another PCB, and the three LEDs are located 120° apart on the same plane.

[0071] Depending on the clinical procedure, different LEDs may have different light output and duration, either individually or in relation to each other. For example, the output of a centrally located LED may precede, delay, or be used simultaneously with the output of at least three radially arranged LEDs. If a clinician wishes to soften and / or manipulate a photopolymerizable dental material in situ and / or biocompatible, the device may incorporate a setting that illuminates only the photopolymerizable dental material to raise its temperature, thereby reducing the material's viscosity. At this point, the material can be manipulated into the desired shape / structure before hardening. Alternatively, the temperature of the photopolymerizable dental material can be raised in situ and / or biocompatible without physical manipulation, which is advantageous in reducing its viscosity and improving its fit to the tooth surface. The heated photopolymerizable dental material can then be hardened in situ and / or biocompatible at high temperatures while maintaining the best fit to the tooth surface. In an example setup to achieve this situation, the photopolymerizable dental material is irradiated with a 365nm-500nm spectrum for approximately 3 to 30 seconds, and immediately before curing, the photopolymerizable dental material is irradiated with a 520nm-2500nm spectrum, raising its temperature for approximately 5 to 30 seconds. In one embodiment, the device has 2 to 5 pre-programmed settings for various clinical procedures / priorities, each mode having different power, duration, and overlap characteristics of at least two emission spectra, with at least one emission spectrum within a specified photon energy range.

[0072] In another embodiment, to ensure proper thermal management of the photon energy emitter (e.g., an LED), the photon energy emitter is coupled to a primary heatsink located within the device. In another embodiment, these primary heatsinks are coupled to a thermal conductor. Alternatively, in another embodiment, primary heatsinks for at least three radially arranged LEDs are coupled to a primary heatsink for a centrally located LED, and then coupled to a thermal conductor. Finally, in another embodiment, these photon energy emitters are electrically connected to a DC power supply. In another embodiment, this DC power supply is a removable and rechargeable power supply such as a lithium-ion battery.

[0073] Optionally, other dental devices can be integrated into this multispectral curing unit. This includes, but is not limited to, transilluminators.

[0074] Another embodiment is the apparatus shown in any one of Figures 33-34. In one embodiment, the apparatus has a photon emitter package as shown in any one of Figures 17-19 and 35.

[0075] (Composition of dental materials and containers) Another embodiment is a dental material composition. In some embodiments, the dental material is a photopolymerizable dental material composition. The dental material compositions described herein have improved energy conversion efficiency, heat transfer, and / or polymerization properties.

[0076] In some embodiments, the photopolymerizable dental material compositions described herein include: acrylate monomers (e.g., triethylene glycol dimethacrylate, TEGDMA, urethane dimethacrylate, UDMA, and bisphenol-A-glycidyl dimethacrylate, bis-GMA, etc.), inorganic fillers (e.g., glass or ceramic, i.e., silicon dioxide, crystalline silica, borosilicate glass, zirconium oxide, zirconia-silica, etc.), photopolymerization systems (e.g., camphoroquinone with an amine co-initiator), optionally one or more pigments or colorants to match tooth color, optionally one or more heating additives, optionally a polymerization accelerator system, and optionally one or more thermal conductivity accelerators. As described herein, heating additives, polymerization accelerator systems, and thermal conductivity accelerators improve the energy conversion efficiency, heat transfer properties, and / or degree of polymerization of the material.

[0077] In one embodiment, the dental material composition contains about 1% to about 40% by weight of acrylate monomer. In another embodiment, the dental material composition contains about 5% to about 30% by weight of acrylate monomer. In another embodiment, the dental material composition contains about 5% to about 20% by weight of acrylate monomer. In another embodiment, the dental material composition contains about 5% to about 15% by weight of acrylate monomer. In another embodiment, the dental material composition contains about 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, or 40% by weight of acrylate monomer.

[0078] In another embodiment, the dental material composition comprises about 30% to about 95% by weight of an inorganic filler. In another embodiment, the dental material composition comprises about 60% to about 95% by weight of an inorganic filler. In another embodiment, the dental material composition comprises about 5% to about 20% by weight of an inorganic filler. In another embodiment, the dental material composition comprises about 5% to about 15% by weight of an inorganic filler. In another embodiment, the dental material composition comprises about 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, or 40% by weight of an inorganic filler monomer.

[0079] In some embodiments, heating additives, polymerization accelerators, and thermal conductivity enhancers are provided to the dental material compositions described herein in the concentrations described by the methods embodied above.

[0080] Tables 1 and 2 show exemplary embodiments of photopolymerizable dental materials. These exemplary dental material compositions include an absorbent dye (e.g., LUNIR1) as a photon energy absorption enhancer to significantly increase the heating of the material. As described herein, additional heating additives and / or polymerization accelerators may be added to the disclosed compositions to further enhance the energy conversion efficiency, heat transfer properties, and / or polymerization properties of the material. Alternatively, other additives may be incorporated to adjust the absorption properties of the material to any photon energy within the disclosed photon energy range. [Table 1] [Table 2]

[0081] Further exemplary embodiments are shown in Table 3. This exemplary dental material composition contains two type II photoinitiators (camphoroquinone and H-Nu 660; H-Nu 660 is a photoinitiator). The present invention includes a photopolymerization accelerator system having a specific photoinitiator (as described in the substantiation) and another co-initiator (borate V) that significantly increases polymerization. The composition also yields a formulation that changes color from "blue / green" to "tooth shade," allowing clinicians to confirm that the composite has fully cured (see Figure 27). Additional heating additives and / or polymerization accelerators may be added to the disclosed composition as described herein to further enhance the energy conversion efficiency, heat transfer properties, and / or polymerization properties of the material. Alternatively, other additives may be incorporated to adjust the absorption properties of the material to any photon energy within the disclosed photon energy range. [Table 3]

[0082] Another exemplary configuration is shown in Table 4. This exemplary dental material composition comprises a dental composite having two Type II photoinitiators (camphoroquinone and H-Nu 660; H-Nu 660 is a specific photoinitiator as described herein) and a copolymerization initiator (borate V). This composition also results in a formulation that changes color from “blue” to “tooth shade,” thereby allowing a clinician to confirm that the composite has fully cured. Additional heating additives and / or polymerization accelerators may be added to further enhance the energy conversion efficiency, heat transfer properties, and / or polymerization properties of the material, as described herein. Alternatively, other additives may be incorporated to adjust the absorption properties of the material to any photon energy within the disclosed photon energy range. [Table 4]

[0083] Further examples of photopolymerizable compositions utilizing the photoinitiator systems described herein are shown in Tables 5-6, which are formulations for dental sealants. [Table 5] [Table 6]

[0084] (Endodontic filling material) Another embodiment is a composition for dental materials, particularly endodontic filling materials such as gutta-percha, which exhibits improved energy conversion efficiency and / or heat transfer characteristics.

[0085] In one embodiment, a disclosed composition for gutta-percha endodontic filling comprises the following components: gutta-percha or other polyisoprene derivatives, inorganic fillers (glass or ceramic, e.g., zinc oxide, titanium oxide, silicon dioxide, crystalline silica, borosilicate glass, zirconium oxide, zirconia-silica, etc.), radiopaque agents (e.g., barium sulfate, bismuth sulfate, tungsten), stabilizers (antioxidants, butylated hydroxytoluene, etc.), waxes or resins (e.g., metal stearate complex, zinc stearate, por (e.g., ethylene glycol, paraffin wax, palmitate, carnauba wax), and at least one heating additive to improve the energy conversion efficiency and / or heat transfer properties of the material. These heating additives are incorporated into the dental material (e.g., gutta-percha) at the concentrations described herein.

[0086] Another exemplary configuration is shown in Tables 7-8. This exemplary gutta-percha endodontic filling dental material composition includes an absorbing dye (i.e., indocyanine green) as a photon energy absorption enhancer that significantly increases the heating of the material. Additional additives may be added to the disclosed composition to further enhance the energy conversion efficiency and / or heat transfer properties of the material. Alternatively, other additives may be incorporated to adjust the absorption properties of the material to any photon energy within the disclosed photon energy range. [Table 7] [Table 8]

[0087] (Dental material container) Another embodiment is a dental material container that exhibits improved energy conversion efficiency and / or heat transfer when irradiated with the disclosed photon energy.

[0088] The disclosed composition for dental material containers comprises the following components: a thermoplastic resin (e.g., polycarbonate, polyamide, polypropylene, polyethylene, etc.), and at least one additive for improving the energy conversion efficiency and / or heat transfer properties of the material. The material may also contain colorants or other pigments, plasticizers, or other fillers (e.g., glass fibers, carbon black, etc.). With respect to photopolymerizable dental materials such as dental composites, the additives, colorants, pigments, or other fillers must adequately block the polymerization light that cures the photopolymerizable material in the container from passing through the container and reaching the composite material.

[0089] Examples of dental material container compositions are shown in Tables 9-14. The following tables detail the formulations of containers incorporating heating additives, showing the heating rate of the materials inside and the overall temperature change. To significantly increase the amount of color. [Table 9] [Table 10]

[0090] Additional additives can be added to the above composition to further enhance the energy conversion efficiency and / or heat transfer properties of the material container. These additives are incorporated at the concentrations disclosed below. For example, boron nitride can be added to the composition to improve the heat transfer properties of the container. [Table 11] [Table 12]

[0091] Alternatively, other additives can be used to adjust the absorption properties of the container to any photon energy within the disclosed photon energy range. Furthermore, other fillers can be added to enhance the properties of the material container. For example, glass fiber can be added to increase the strength of the container. [Table 13] [Table 14]

[0092] Another embodiment is a method for manufacturing a dental container according to this specification, comprising a thermoplastic resin and a heating additive. In one embodiment, the method comprises a step of heating the thermoplastic resin to at least its softening point. In another embodiment, the method further comprises a step of maintaining and controlling the resin temperature at at least its softening point. In another embodiment, the method further comprises a step of adding an additive in an amount of about 0.1 to 5%. Suitable additives include those having a high photon energy absorption of 520 nm to 2500 nm. In another embodiment, the method comprises a step of maintaining the temperature of the resin at its softening point while adding the additive and optionally a dispersant. In another embodiment, the method comprises a step of mixing and homogenizing a mixture comprising the resin, the additive and optional dispersant while maintaining the temperature at at least the softening point of the resin. In another embodiment, the method comprises a step of extruding the homogenized mixture comprising the resin, the additive and optional dispersant into a mold cavity comprising the shape of a dental material container and cooling it before removing it from the cavity. Alternatively, in another embodiment, a homogenized and heated mixture containing a resin, additives, and an optional dispersant is formed into pellets for later use in injection molding of dental material containers.

[0093] Another embodiment is a dental material container manufactured by the process described above. The formed dental material container is suitable for being filled with dental material. Furthermore, the molded dental material container manufactured by the process described above and containing dental material is suitable for being heated with photon energy to rapidly heat the dental material described herein.

[0094] (Examples) (Example 1: Application of photon energy to anesthetics, gutta-percha, dental composites, and dental / endodontic cleaning agents - absorption and performance) The advantages of the disclosed embodiments can be derived from the application of photon energy to dental materials, including but not limited to: anesthetics (reducing pain during injection), gutta-percha (for endodontic root canal occlusion), dental composites, sealants, cements, cavity liners, glass ionomer resins (e.g., reduced viscosity, improved handling properties, reduced voids, improved mechanical properties after curing), and endodontic irrigators (increased efficacy and reactivity). For example, in Figure 3, the absorbances of three composite materials, namely Filtek Supreme Ultra, Spectrum TPH3, and Eshet.X HA, are compared to the absorbance of acrylic, showing that the three major composite materials exhibit similar absorption to acrylic material. This demonstrates the effectiveness of dental composites. The main composition is acrylic monomer, which is shown to be the primary structure responsible for absorption, and this indicates that a specific wavelength band corresponding to the harmonic band can be selected to heat the acrylic monomer and oligomer within the complex.

[0095] Furthermore, dental materials containing gutta-percha have the following structure: [ka]

[0096] The target bindings for absorption and heating of gutta-percha using near-infrared (IR) photons are terpene molecules, which possess both CC single and CC double bonds. This is clearly shown in Figure 4, which displays the various binding and molecular peaks of gutta-percha and highly packed composite materials, such as Eshet.X HA, that can be targeted for near-infrared application and heating. Furthermore, apart from the materials forming the composite, the composite / dental material container, or compal, can be designed with a color that exhibits either low absorption, passing all photon energy to the composite or the dental material within it, or high absorption, heating the compal / material container itself. Different absorption properties can be obtained for the same plastic material (polycarbonate) with different colors / opacities, as shown in Figure 5. Any of these provided absorption / harmonic bands can be targeted for heating of dental materials and / or dental material containers using photon energy.

[0097] Next, referring to Figures 6 and 7, the composite and / or comparable photons The ability to target photons also provides a significant reduction in the time required to heat the composite to the desired temperature. In other words, using photon energy greatly increases the heating rate without harmful effects. For comparison, as shown in Figure 6, heating a composite with a commercially available composite heater is slow, reaching approximately 60°C in 10 minutes. In contrast, as shown in Figure 7, using photon energy, the same composite material can be heated to the same temperature (60°C) in less than 20 seconds, which is highly advantageous for clinicians as it significantly reduces procedure time and increases office efficiency. Different composite materials (and other dental materials) heat up faster based on the composition of the composite material itself, the composition of the material container, and / or the heat transfer characteristics of the composite material or container. These same concepts apply to all dental materials. Heating time and heating rate are also related to the amount and spatial orientation of the photon energy source. That is, a single emitter with 4W output is effective, but not as efficient as four emitters with 1W output each directed around the composite container. In a preferred embodiment of the present invention, a device is created that uses 1 to about 6 light-emitting diodes to heat dental materials to about 60°C to 80°C in about 10 to 60 seconds.

[0098] (Example 2: Determining the viscosity of dental materials at high temperatures) One additional consideration is the desired target temperature for heating the composite and / or dental material. This determines the type and amount of photon energy required to achieve the desired handling and / or performance characteristics. Furthermore, in the case of photopolymerizable dental materials, the photon energy should not be excessive, as this may cause the photopolymerizable dental material to harden prematurely before application. In one exemplary embodiment, the composite may be heated to a temperature of about 50°C to about 100°C, more preferably about 60°C to about 80°C.

[0099] To determine this more concretely, the following evaluation (Figure 8) was conducted.

[0100] (method) Four preheated resin-based nanocomposite materials: Herculite Ultra (Kerr, Orange, CA), Tetric EvoCeram (Ivoclar). The rheological properties of stainless steel (Vivadent, Schaan, Liechtenstein), Filtek Supreme Ultra (3M, St. Paul, MN), and Grandio (Voco, Cuxhaven, Germany) are as follows: The procedure was performed using a shear rheometer with environmental control (Kinexus, Malvern, UK) with a row plate setup (20 mm diameter). A composite sample (0.2 g) was placed on the lower plate of the rheometer, and the upper plate was gently lowered until it touched the surface of the sample with a gap distance of 0.5 mm. The rheometer was set to various temperatures (25°C, 37°C, and 60°C), and a 5-minute delay was adopted before measurement to ensure the composite material was at the specified temperature. The shear rate was 0.1 to 10 s in ramp mode. -1 It increased linearly.

[0101] (result) The results indicate that viscosity decreases as the shear rate increases. Furthermore, for all shear rates tested, viscosity changes as a function of heating temperature in the following order: 60°C < 37°C < 25°C.

[0102] (Conclusion) Regardless of the resin composite material used, preheating dental nanocomposite materials significantly improved fluidity, mechanical bonding, and sealing strength. Consequently, increasing the shear rate and temperature resulted in a significant decrease in shear viscosity.

[0103] In addition, similar evaluations were performed on two additional composites, as shown in Figure 8. The results of these evaluations show that the advantage of heating highly filled composites is that they behave like fluid composites at a certain temperature. This temperature varies depending on the specific composite brand, but highly filled composites need to be heated to about 60°C or higher to achieve the desired fluidity. For even more highly filled composites, this target temperature is expected to be even higher, perhaps around 70°C or 80°C. Regardless of the product, photon energy can be used to enhance performance and handling properties, such as fluidity. Fluidity aids in placement on teeth, and highly filled composites are more durable than fluid composites.

[0104] (Example 3: The effect of temperature on dental materials) In some embodiments, it is undesirable to heat a composite material to a temperature that causes it to harden or solidify. For example, above 140°C, some dental composites begin to harden (due to self-hardening / polymerization or evaporation of components) and become clinically unusable. This temperature varies depending on the composition of the dental composite, with some composites maintaining their integrity at 200°C. An overview of this experiment is provided below.

[0105] (method) Three samples each of dental composite materials from three manufacturers and gutta-percha from one manufacturer were placed on a hot plate and heated to 60°C. Thermocouples were placed on the composite materials to monitor the temperature. The temperature increased by 5°C every 3 minutes up to 150°C. After 150°C, the temperature increased by 10°C every 3 minutes. The samples were examined using a metal spatula, and the observations were recorded.

[0106] (result) At 60°C, the viscosity of the composite material decreased significantly in all three brands, compared to previous data. Support was provided. The gutta-percha was very soft but still viscous. Up to 115°C, the gutta-percha became similar to the composite at 60°C, easily manipulated with a spatula, but still exhibited stringy behavior. At 130°C, the gutta-percha lost its stringiness, its viscosity decreased significantly, and it became easily malleable. By 140°C, two of the three composite brands began to harden. Upon removal from the hot plate, the two hardened composites crumbled easily with slight pressure. The third brand of composite did not harden or crumble until 200°C. It appeared unaffected and could still harden at this temperature. The gutta-percha appeared unaffected up to 200°C. Between 200°C and 250°C, visible, foul-smelling smoke began to be produced, but there was no discoloration or significant change in material properties.

[0107] (Conclusion) The composite material needs to be kept below 140°C to prevent performance degradation, and temperatures above 100°C are clinically unnecessary as it already achieves the desired fluidity below 100°C. Gutta-percha should not be heated above 200°C, and the desired fluidity is achieved below this temperature range of approximately 115°C to approximately 200°C. These temperature boundaries are considered in the present invention. In some embodiments, the use of photon energy does not raise the temperature of the dental material above approximately 200°C. In some embodiments, the use of photon energy does not raise the temperature of the dental material above approximately 140°C.

[0108] In another benchtop test (data not provided), the heat block and oven were set to high temperatures of 120°C and 150°C to determine whether primary conductive heating from very hot elements could shorten the warm-up time of dental composites and compal. The composites reached 80°C over 30 seconds, but then rapidly exceeded 100°C and hardened, rendering the material unusable. This data supports the idea that conductive heating, like commercially available composite heating units, cannot rapidly heat composites in a safe and controlled manner without causing harmful effects on the composites.

[0109] Dental cleaning agents containing sodium hypochlorite perform better at high temperatures (up to 60°C), but degrade rapidly at higher temperatures and should not be heated above their boiling point (100°C). Therefore, in one embodiment, photon energy is used to heat the dental liquid / cleaning agent to approximately 30°C to 100°C.

[0110] In summary, the specific temperature at which certain dental materials should be heated to strengthen them without causing adverse effects largely depends on the composition of the dental material.

[0111] Figure 13 shows an overview of data collected to test the adverse effects of prolonged exposure to high temperatures and near-infrared (NIR) photon energy on the curing properties of dental composite materials.

[0112] (method) Three different commercially available composite material brands were tested under three conditions: room temperature 20°C (control), 80°C in an oven, and 80°C by photon energy. In the high-temperature group, the oven was set to 80°C and the composite material was left inside for 1 hour. For NIR exposure, an NIR LED (940nm) was used with a thermocouple and microcontroller. The thermocouple was inserted into the composite material for feedback, and the LED was turned on at 100% to raise the composite material temperature to 80°C. This took less than a minute. At this point, the microcontroller switched to a modulated pulse to maintain a constant temperature for 1 hour. The composite material was distributed and molded into packs using 2mm pack molds (Paradigm Curing Discs, 3M Company SKU: 76965), and cured using a commercially available curing light. Curing time was 0 seconds. In the high-temperature group, dispensing occurred immediately after removal from the oven or NIR LED fixture.

[0113] (result) As is evident from the data, prolonged exposure to high temperatures from a convection oven or absorption of near-infrared photon energy did not statistically affect the microhardness values ​​after curing compared to dental composites stored at room temperature. Furthermore, there was no observed change in the aesthetics of the tested dental composite materials.

[0114] (Conclusion) Maintaining the composite material at 80°C using photon energy did not adversely affect the material.

[0115] (Example 4: Absorbance measurement experiment using proximity sensor) A proximity sensor (Vishay VCNL4010 sensor - infrared emitter, I) incorporating both an 890nm infrared (IR) LED and an IR phototransistor to measure reflected IR photon energy. 2The tests were performed using a fully integrated proximity and ambient light sensor with a C interface and interrupt functionality. While this sensor is typically used to measure the distance to an object, the test results shown in Figure 20 show a strong correlation (R) between the measured IR reflectance and the temperature change of the object after 15 seconds of exposure to an IR LED at a constant distance from the sensor. 2 The sensor indicates that (wavelength, power, time, and distance were all kept constant between objects) there exists a value of 0.97. All objects tested were commercially available dental composite materials of various colors. Therefore, the sensor can be used to determine the amount of photon energy required to heat a particular dental material or material container to a desired temperature and, if necessary, to maintain that desired temperature over a certain period of time. Furthermore, the sensor's measurements can function as a "fingerprint" to identify the inserted object and implement a closed-platform system (i.e., the device works only with a specific material or material container).

[0116] (Example 5: Microhardness and temperature of dental composite materials) In addition to improving the fluidity of the composite material, it has been confirmed that heating the composite material improves its hardness or durability after curing following application. To explain this, the following evaluation was conducted, and the results are shown in Figure 10.

[0117] (method) Using a custom heating setup, 2mm x 3mm composite material packs (height x diameter) were heated to specified temperatures (25, 40, 60, and 80°C). The composite material packs were cured at various temperatures (Paradigm Curing Light, 3M, St. Paul, Minnesota) and stored in a dark container at 37°C for 24 hours. Microhardness was measured on the top and bottom surfaces of the samples using an HMV-G microhardness tester (Shimadzu Corporation, Kyoto) under the following experimental conditions: Force setting - HV0.2 (1.961N), Hold time - 10 seconds. Before the microhardness measurements, the composite samples were smoothed using 180, 500, and 1500 grit sandpaper, leveled, and polished for analysis. Four resin-based nanocomposite materials were tested (n=9 each): Herculite Ultra (Kerr), Tetric EvoCeram (Ivoclar Vivadent), Filtek Supreme Ultra (3M), Grandio (Voco). Statistical significance between temperature results was compared using an independent Student's t-test (a=0.05).

[0118] (result) The microhardness results are summarized in Figure 10. Preheating the Grandio and Filtek composite materials above 60°C resulted in statistically significant microhardness changes on both the top and bottom surfaces of the samples. The microhardness increased (p<0.02). Preheating the Tetric composite to 60°C resulted in a statistically significant increase in the microhardness of the top surface of the sample (p=0.047). Preheating the Herculite composite to 80°C resulted in a statistically significant increase in the microhardness of the top surface of the sample (p<0.05).

[0119] (Conclusion) To increase the microhardness of dental composite materials, it is desirable to cure the composite materials at high temperatures. In particular, 60°C to 80°C is the target range for increasing the microhardness of tested composite materials. Therefore, additives that raise the temperature of photopolymerizable dental materials before or during curing function as polymerization accelerators, as increasing the temperature increases polymerization and thus increases microhardness. Accordingly, in some embodiments, photon energy is used to heat dental materials, especially photopolymerizable dental materials, to a temperature of about 60°C to about 80°C.

[0120] (Example 6: Conversion rate and temperature of dental composite materials) As another measure of improved durability resulting from heating or preheating of dental composite materials before application and curing, the degree of transformation of the composite material at high temperatures was also evaluated according to the following evaluation procedure, and the results are shown in Figure 11.

[0121] (measurement) A custom heating setup was used to heat 2mm x 3mm composite packs (height x diameter) to specified temperatures (25°C, 40°C, 60°C, and 80°C). The composite material packs were cured at various temperatures and stored in a dark container at 37°C for 24 hours. DoC was measured on the top surface of the sample by micro-attenuation total reflection Fourier transform infrared spectroscopy (micro-ATR FTIR) using a Nicolet iS5 spectrometer (ThermoFisher Scientific, Waltham, Massachusetts) equipped with an iD5ATR accessory, with the following specifications: wavenumber range = 4000–650 cm⁻¹ -1 32 scans / second, and 2cm -1 Resolution. Four resin-based nanocomposite materials (n=5 each) were tested: Herculite Ultra (Kerr), Tetric EvoCeram (Ivoclar Vivadent), Filtek Supreme Ultra (3M), and Grandio (Voco). Statistical significance between temperature results was compared using independent Student's t-tests (a=0.05).

[0122] (result) The conversion degree results are shown in Figure 11. All four composite brands showed a statistically significant increase in conversion degree (DoC) of the composite material when heated to 60°C compared to 25°C (p<0.05). All composite material brands except Herculite (p=0.11) showed a statistically significant increase in DoC of the composite material when heated to 80°C compared to 25°C (p<0.03). Only Grandio showed a statistically significant increase in DoC when heated to 40°C compared to 25°C (p=0.02).

[0123] (Conclusion) Curing dental composite materials at high temperatures results in higher DoC. In particular, the target range for maximizing DoC is 60°C to 80°C. Therefore, in some embodiments, photon energy is used to heat dental materials, especially dental photopolymerizable materials, to a temperature of about 60°C to about 80°C.

[0124] (Example 7: Polywave / Multispectral curing) Preheating of photopolymerizable dental materials enhances their curing process, and the advantages of a combination of blue light in the 440-500 nm range and a second wavelength above 520 nm were evaluated. The effect of the combination of photon energy and curing light emission on composite microhardness will be investigated in the next experiment. Therefore, we conducted an investigation, and the results are shown in a graph in Figure 12.

[0125] (method) A custom setup was used to simultaneously investigate the near-infrared photon energy and curing of Filtek Supreme composite materials. In short, the setup consisted of a 2mm pack mold (Paradigm Curing Discs, 3M Company SKU: 76965) placed on a fixed near-infrared LED die package (four die 850nm LEDs 5mm apart, LEDEngin, San Jose, California, operating at 1A) and positioned under a fixed dental curing light (2mm apart; Valiant Curing Light, Vista Dental Products, Racine, WI). Five different groups were tested, with n=3 in each group: G1) Valiant's standard 20-second treatment mode (no NIR), G2) Valiant's boosted 3-second treatment mode (no NIR), G3) Valiant's standard 20-second treatment + 20-second NIR (0-second delay, i.e., simultaneous), G4) NIR (0-25 seconds) + Valiant's standard 20-second treatment (from 5-25 seconds), i.e., 5-second NIR preceded, and G5) NIR (0-13 seconds) + Valiant's boosted 3-second treatment (10-13 seconds), i.e., 10-second NIR preceded. Composite material samples underwent microhardness evaluation as described in Example 5. Statistical significance between experimental groups was compared using independent Student's t-tests (a=0.05).

[0126] (result) The composite hardness results are shown in Figure 12. G3 and G4 showed statistically significant increases in microhardness on the upper surface of the composite sample compared to G1 (p=0.03 and 0.02, respectively). No statistical significance was observed when comparing the results of G2 and G5 (p=0.11). However, in the intergroup comparison, the results for G5 showed higher average results on both sides of the sample. This became clear. Therefore, a larger sample set may help to uncover the true trends between these groups.

[0127] (Conclusion) This method does not adversely affect the curing process, and it appears that using wavelengths of 520 nm or higher simultaneously or consecutively with curing light improves the microhardness of the cured composite material. Furthermore, the effect of other wavelengths within the specified wavelength range (520 nm to 2500 nm) on the microhardness of the composite material was evaluated according to the following experiment, and the results are shown in Figure 21 as a graph.

[0128] (method) A custom setup was used to investigate the simultaneous application of photon energies at various wavelengths and the curing of Grandio SO composite materials. The setup consisted of a ring of three blue LEDs (475nm Cree XLamp XP-E2) 5mm away from the sample, with a fourth replaceable LED in the center. The output of the blue LEDs was adjusted so that the composite material sample was exposed to the same light energy levels used in commercially available curing lights (Valiant Curing Light, Vista Dental Products, Racine, WI). All replaceable LEDs were adjusted to emit the same light output, and the light output from the three blue LEDs was kept constant. Light power measurements were performed using a light power meter (S310C sensor, PM100D console, Thor Labs, Newton, New Jersey). The wavelengths tested with the replaceable LEDs were 523nm, 590nm, 623nm, 660nm, 740nm, 850nm, and 940nm (LedEngin LZ1). A 10-second exposure of the replaceable LED preceded a 20-second exposure of the combined output of the replaceable LED and the blue LED. In other words, while the replaceable LED emitted light for 30 seconds, the three blue LEDs emitted light during the last 20 seconds, meaning that the photon energy within the specified wavelength led the polymerized light for 10 seconds. As described in the section "Microhardness and Temperature of Composite Materials," the microhardness of composite material samples was evaluated. Statistical significance between experimental groups was compared using an independent Student's t-test (a=0.05).

[0129] (result) The microhardness data for the tested wavelengths is shown in Figure 21. The upper hardness was significantly increased when using 523nm, 590nm, 623nm, 660nm, 850nm, and 940nm. The lower microhardness was also significantly improved when using 523nm, 623nm, 660nm, 850nm, and 940nm.

[0130] (Conclusion) Multiple wavelengths, when combined with standard blue polymerization light at 470 nm, showed improved post-curing microhardness in the upper and lower parts of the pack. These wavelengths are advantageous for clinical use because the harder composite material exhibits longer life and reduced wear. Furthermore, while hydroxyapatite and water exhibit low absorption coefficients compared to the commercially available curing light spectrum, i.e., peak emission at 470 nm, the oxyhemoglobin absorption coefficient is 1,000 to 10,000 times higher absorbance than the disclosed photon energy spectrum (see Figure 22). This is why commercially available curing lights raise concerns about temperature rise in the dental pulp and safety. Therefore, the disclosed invention can utilize photon energies between 520 nm and 2,500 nm to increase composite microhardness (Figure 21), reduce oxyhemoglobin and dental pulp absorption, and improve clinical efficacy and safety.

[0131] Furthermore, the described “lead” of photon energy emission before curing the light emission demonstrates a successful exemplary embodiment of the present invention. No adverse effects were observed when using two separate emission spectra during testing. One emission spectrum is within the disclosed photon energy range (520 nm to 2500 nm).

[0132] (Example 8: Improvement of heating by incorporating heating additives into dental composite materials or gutta-percha) Near-infrared dyes (i.e., photon energy absorption enhancers) were added to enhance the absorption of dental materials at near-infrared wavelengths and, therefore, to improve the conversion of applied photon energy into a temperature rise in the dental materials. In the initial evaluation, two different NIR dyes were used as additives to gutta-percha and composite materials, and heating was evaluated according to the following experiment.

[0133] (method) Two near-infrared dyes were investigated (nickel(II)5,9,14,18,23,27,32,36-octabtoxic-2,3-naphthalocyanine, Sigma Aldrich, Milwaukee, Wisconsin; and QCR#NIR848A (QCR Solutions, Port St. Lucie, Florida)). The dyes were dissolved at varying concentrations in ~0.3 mL of chloroform (Sigma Aldrich, Milwaukee, WI) to produce dyes for gutta-percha or 2 w / w% or 5 w / w% dental composite material (Filtek Supreme) at 1 w / w% or 2.5 w / w%. Once the dyes were dissolved, the powdered gutta-percha or dental composite material was added to the mixture and blended by hand with an additional approximately 0.5 mL of chloroform until smooth. The newly formed gutta-percha / composite material was left in a fume hood for approximately 30 minutes to allow the chloroform to evaporate. The gutta-percha sample was softened by placing it on a watch glass on a 120°C hot plate for 5 minutes. The gutta-percha pack was created using a custom mold measuring 2mm high x 3.4mm in diameter. A thermistor was placed in the gutta-percha pack, and the sample was heated at a distance of 3mm using an 850mm 4-die LED package. The composite material sample was formed in a similar manner, except that heat was not required to create the pack.

[0134] (result) The heating results are described in Tables 15-16 below. Table 15 shows the results after adding near-infrared dye #1 to gutta-percha (GP). Near-infrared dye #1 is nickel(II) 5,9,14,18,23,27,32,36-octabtoxic-2,3-naphthalocyanine, which has an absorbance of 845-851 nm and an extinction coefficient of 111 L / g*cm. The test compositions contained 2% or 5% dye #1 in powdered gutta-percha. [Table 15]

[0135] Table 16 shows the results after adding near-infrared dye #2 to gutta-percha. Table 17 shows the results after adding various concentrations of near-infrared dye #2 to the commercially available dental composite material Filtek. Near-infrared dye #2 was QCR#NIR848A (lot #0519-16A-8484) with an extinction coefficient of 330 L / g*cm. The test compositions contained 2% or 5% Ni IR dye in powdered gutta-percha. [Table 16] [Table 17]

[0136] (Conclusion) Adding near-infrared dyes significantly improves the efficiency of deposited NIR photon energy relative to the temperature rise of dental materials, accelerating the heating of dental materials such as composites and gutta-percha. In one embodiment, an additive at a concentration of at least 10 ppm (0.001%) that absorbs photon energy in the 520 nm to 2500 nm range is added to the dental material composition to promote rapid heating of the dental material. Furthermore, this additive can be added to the dental material container.

[0137] In another test, we considered adding NIR dyes to the composite material. The heating rate / properties were evaluated according to the following experiment. The results are shown graphically in Figure 23.

[0138] (method) One near-infrared dye (LUNIR1) was investigated. This dye was weighed and placed in a cuvette. Precise amounts of dental composite material (Grandio SO, VOCO GmBH) were added to create 0.1 mg of the composite material at dye concentrations of 0.10 wt%, 0.50 wt%, 1.0 wt%, and 2.0 wt%. These were tested only against the control of the dental material. Next, this composite material was exposed to a near-infrared LED (940 nm LedEngin LZ1) for 15 minutes. The samples were exposed for a certain number of seconds. The start and end temperatures of the composite material were measured using thermocouples placed within the composite material. Statistical significance between experimental groups was compared using an independent Student's t-test (a=0.05).

[0139] (result) Figure 23 shows the temperature-dependent data for the composite materials with the tested pigment concentrations. Statistically significant differences were observed between the baseline and each of the four pigment concentrations. No statistical significance was found when comparing temperatures between different pigment concentration percentages. Regardless of the LUNIR1 concentration, the color of the composite material did not change significantly from the original tooth resin color.

[0140] (Conclusion) Adding photon energy absorbing dyes to composite materials significantly improves the efficiency of temperature increase in dental materials, as the deposited photon energy is converted into heat. Although there is no statistical difference, a positive trend has been observed where the temperature increase increases with increasing dye concentration. Therefore, in one embodiment, to promote rapid heating of dental materials, photon energy absorbing dyes in the 520nm to 2500nm range are used. An additive containing at least 0.1% of energy-absorbing material is added to the dental composite material. Furthermore, the additive must not cause an unnatural change in tooth color in the dental material.

[0141] In another test, we considered adding different dyes to the composite material. The absorbance properties of the composite material blends were evaluated according to the following experiment. The results are shown graphically in Figure 24.

[0142] (method) Indocyanine green (ICG) is a well-known biocompatible dye approved by the FDA for in vivo use and has a peak absorbance at 800 nm. ICG was dissolved in ~0.3 ml of chloroform (Sigma-Aldrich, Milwaukee, Wisconsin) and added in various amounts to create dyes at concentrations of 1 ppm, 10 ppm, 100 ppm, and 1000 ppm in a dental composite material (Filtek Supreme, shade A2). The mixtures were then hand-mixed until smooth and left in a light-protected fume hood for ~10 minutes to evaporate the chloroform (photoprotection was necessary to prevent the composite from hardening under room light). The samples were then subjected to Fourier transform spectroscopy to measure the absorbance at 800 nm.

[0143] (result) As shown in Figure 24, 10 ppm ICG resulted in a significant increase in the absorbance of the dental composite material at 800 nm. Further increases in ICG concentration led to increased absorbance. The absorbance of 1 ppm ICG was almost the same as that of 0 ppm ICG. ICG concentrations of 1 ppm and 10 ppm did not significantly alter the color of the composite material from the original composite material tooth shade. However, 100 ppm and 1000 ppm ICG resulted in a green composite material blend / mixture, which constitutes an unnatural tooth color.

[0144] (Conclusion) Adding photon energy absorbing dye ICG at concentrations exceeding 1 ppm significantly increased material absorption at 800 nm. Adding 10 ppm ICG did not significantly alter the color of the composite material from its original shade, indicating that 10 ppm ICG is applicable to dental composite materials. Due to aesthetic concerns, 100 ppm and 1000 ppm cannot be used in dental composite materials. However, 100 ppm and 1000 ppm can be used in non-aesthetic procedures or dental materials where aesthetics are not a concern (e.g., gutta-percha filled inside teeth and not aesthetically visible).

[0145] (Example 9: Far-red or near-infrared dye additives + composite materials as photoinitiators to improve curing) The characteristics of far-red dyes, which are combinations of photoinitiators and co-initiators for dental composite materials, and their curing properties were evaluated according to the following criteria, and the results are shown in Figure 26.

[0146] (method) Dental composite material (Ivoclar Evo-Ceram) was used with far-red photoinitiator (H-Nu 660, Spectra Group Limited) at various concentrations ranging from 0.005% to 0.1% by weight, and with co-initiator (borate V) used at 10x higher concentrations. For comparison, the unprocessed composite material and 1% by weight co-initiator were also used. Composite materials including the co-initiator were also tested. The composite material packs were fabricated with a depth of 2.35 mm and a width of 3.45 mm. Curing was performed for all variations using a combination of far-infrared (660 nm LedEngin LZ1) and blue (475 nm Cree XLamp XP-E2) LEDs. The red LED was activated first for 10 seconds, followed by the red and blue LEDs being activated simultaneously for 20 seconds. Additionally, raw composite materials and co-initiator-only composites were tested with an additional blue LED instead of red as a baseline. After curing... The surface microhardness of the top and bottom of the composite pack was measured. Statistical significance between experimental groups was compared using an independent Student's t-test (a=0.05).

[0147] (result) Microhardness data for the test conditions are shown in Figure 26. A significant increase was observed at the top for 0.005% 660nm initiator + 0.05% borate V. The hardness of 0.1% 660nm initiator + 1.0% borate V, 0.05% 660nm initiator + 0.5% borate V, and 0% 660nm initiator + 1.0% borate V was found to be remarkably low. Furthermore, as shown in Figure 27, a visible color change from green / blue to the standard A2 tone was visualized after photopolymerization of various composite materials. In particular, the green / blue color was not noticeable after curing at 660HNu concentrations of 0.05% or less. Therefore, these concentrations can be used to provide clinicians with a visible indicator of complete / successful treatment. Conversely, the green / blue color remained in the 0.1% 660HNu sample after curing.

[0148] (Conclusion) The use of additional initiators and co-initiators with far-red wavelengths affects the microhardness of the cured composite material. Higher concentrations can actually negatively impact the basal hardness, potentially because energy is absorbed by the initiator before reaching this depth. However, concentrations can be selected to improve microhardness compared to using blue light alone. In particular, adding 0.005% 660H-Nu and 0.05% borate V to commercially available dental composite materials and curing them using 660nm and blue (such as 470nm) light results in a harder composite material after curing.

[0149] (Example 10: Far-red or near-infrared dye additive + container material) To enhance the absorption of dental material housings at far-red or near-infrared wavelengths, and therefore improve the conversion of applied photon energy into a temperature rise in the dental material, plastics containing NIR dyes were evaluated according to the following criteria. The results are shown graphically in Figure 25.

[0150] (method) Various plastic materials of similar thickness were heated using an NIR LED (940nm LZ1 LedEngin operating at 1A). A thermocouple was attached to the plastic on the opposite side of the LED radiation exposure, at the center of the LED radiation. The LED was active for 30 seconds, and temperature data was recorded for another 30 seconds after the LED was turned off. The materials tested were poly(methyl methacrylate) (PMMA) (clear, orange, black, and white), polycarbonate (PC) embedded with NIR absorbing dye (clear orange in appearance), and two commercially available composite materials, Compal (black and blue).

[0151] (result) The heating curves of the materials are shown in Figure 25. In PC using NIR dyes, both the rate of change and the peak temperature change are large. Among the other materials, the black composite material Compal was optimal for heating, but its peak temperature was 60% lower than that of PC using NIR dyes.

[0152] (Conclusion) Adding NIR dyes to plastic materials improves the efficiency of converting deposited NIR photon energy into a temperature increase.

[0153] (Example 11: Apparatus for heating dental composite materials and applying dental composite materials, and apparatus for heating dental composite materials and curing dental photopolymerizable composite materials) This specification describes a method for performing the application of dental materials, such as dental composite materials. This is an exemplary embodiment of the device. An exemplary embodiment of a dispensing or delivery device is shown in Figures 14-15. The device comprises a body including a handle and an actuator or trigger that operates to dispense composite material from the device. The actuator may be additionally formed as a spring-forced grip, as shown in Figure 16. As shown in Figure 15, the body may also include an emitter that emits near-infrared light / photon energy, and further, a compal is removably mounted to the body adjacent to the emitter so that light from the emitter strikes the compal and / or the dental material contained therein. The light / photons from the emitter strike the compal and / or the dental material, affecting the dental material by heating the material to a desired temperature, and subsequently the trigger is activated to dispense the dental material from the compal. When depleted, the compal is removed from the body and a new compal is attached thereto so that the device can be used to heat and dispense additional dental material. The body may further include an internal power source (not shown), such as a battery, so that the device is cordless. Alternatively, the device may be connected to a suitable external power supply (not shown) via a plug (not shown) that is operably connected to the device and detachably engaged with a power supply.

[0154] The apparatus may further include or be formed a curing light source (not shown) that can operate in succession or simultaneously with a near-infrared emitter, and the infrared emitter may be part of the curing apparatus. The apparatus also includes appropriate actuators or buttons for operating the emitter and / or light source. In addition, the apparatus may include or be formed a curing light source (not shown) that can operate in succession or simultaneously with a near-infrared emitter, and the infrared emitter may be part of the curing apparatus.

[0155] Referring to Figure 28, an exemplary embodiment of a distribution or delivery device is shown. The device 1 has a main outer body including an outer housing 2, a handheld grip 3 for holding the device, a base 4, an actuator 5, an upper housing 6, and a removable autoclavable sleeve 7 covering a removable compal 8 which may contain dental materials as described herein. The grip 3 further includes a removable rechargeable energy source door 9 having a retaining clip 11. The upper housing 6 further covers one or more LED indicators 12, and the device further includes an on / off button or switch 13.

[0156] Referring to Figure 29, this shows another side perspective view of the apparatus 1 described above and the distal tip portion 14 of the apparatus. As shown, the distal tip portion 14 includes a compal 8 covered by an autoclavable sleeve 7. The compal 8 is mounted distal to the plunger 16, and the plunger 16 extends into the compal, pushing down the actuator 5, which releases dental material from the orifice 15.

[0157] Referring here to Figures 30 and 31, a sagittal side view of the apparatus 1 with the outer housing 2 and autoclavable sleeve 7 removed is shown. As shown, the apparatus includes a main printed circuit board (PCB) 24 connected to a rechargeable energy source 25. The PCB 24 is further connected to wires or wire ribbons 23 connected to a secondary PCB 18 on which one or more control sensors 20 and one or more photon energy emitters 21 are mounted. The photon energy emitters 21 are covered by lenses 17 and are in very close proximity (e.g., less than 1 cm) to the compal 8. As described herein, one or more photon energy emitters 21 emit photon energy that is absorbed and heated by one or more components of the dental material contained in the compal 8. Furthermore, as described herein, one or more photon energy emitters 21 emit photon energy that is absorbed by one or more components of the dental material container, such as the compal 8, heating the dental material container and thereby heating the dental material contained therein. The secondary PCB18 also has one or more attached to it It can function as a primary heatsink for the photon energy emitter 21. Furthermore, a secondary heatsink 19 covers the secondary PCB 18, which may include a portion of the upper housing 6 or nose cone bottom 18 of the above-mentioned device. The lower image of Figure 30 shows a lateral sagittal perspective view of the distal tip 14 of the device as described above.

[0158] Referring here to Figure 32, an exploded view of the device is shown. Shown are the outer housings 2L (left housing) and 2R (right housing), the upper housing 6, the nose cone bottom 22, the handheld grip 3 for holding the device, the base 4, the rechargeable energy source door 9 with retaining clips 11 on the left and right, the actuator 5, the removable autoclavable sleeve 7, and the LED indicator 12. Also shown is a plunger 16 hinged to the actuator 5, extending distally to the compal 8. Furthermore, a main PCB 24 is shown having at least one photon energy emitter 21 connected to a rechargeable energy source 25 via connected wires or wire ribbons 23. A secondary PCB 18 is shown, with multiple photon energy emitters 21 mounted and disconnected from the wires or wire ribbons 23. A lens 17 covering one or more photon emitters 21 is shown in close proximity to the compal 8 (e.g., less than 1 cm).

[0159] Figures 17-19 and 35 show embodiments of a photon emitter (i.e., LED) package that can be incorporated into a disclosed multispectral apparatus described herein, emitting at least two distinct emission spectra for the application of photon energy for curing and heating of dental composite materials. In one embodiment, the LEDs are located on two distinct PCBs, and the same They are located on one plane or on different planes. Although not shown in these figures, two different radiation sources can be placed on the same PCB and on the same plane, or a single LED package can be created incorporating multiple dies for different spectral emission. In one embodiment, the various photon energy sources (i.e., LEDs) are located on separate PCBs on separate planes, as shown in Figures 17-19 and 35. This configuration offers improved collimation and illumination of light / photon energy compared to multiple dies on the same LED package. Specifically, in one embodiment, three LEDs are required arranged in a cloverleaf configuration (i.e., 120 degrees apart) on a PCB that is higher than another PCB containing one LED (see Figures 17 and 35). This configuration allows for closer spacing between the LEDs, making it easier to collimate the spectral emission patterns of the LEDs using smaller optical components (reflectors, collimators, etc.) and a uniform illumination field.

[0160] Further detailing the realized LED configuration, referring to Figures 17-19, the light or photon emitting portion of the multispectral device 38 can include different sets of photon emitters 21a located thereon, which can be arranged on the same printed circuit board (PCB) and exist on the same plane, or they can exist on two separate PCBs and exist on either the same or different planes, or lastly, a single LED package can be created by incorporating multiple dies to emit light of different wavelengths or photons of different energies.

[0161] In Figure 17, the multispectral apparatus 38 further includes a collimator body or apparatus housing 30 for emitters 21a surrounding LEDs 32a, 32b, and 32c, where LEDs 32a, 32b, and 32c are mounted on the same or different PCBs 27a and 27b, which can be arranged in different planes. LEDs 32a, 32b, and 32c must emit at least two different emission spectra, with at least one emission spectrum within a specified photon energy range. LEDs 32a, 32b, and 32c are located within the collimator body or apparatus housing 30 and aligned with the collimator surface 29a to guide light and / or photons from the collimator body or apparatus housing 30 through the lens 29b. In Figures 17 and 18, LED 32c is collimated The LED 32a is positioned around the outside of the meter body or device housing 30, while the LED 32a is positioned inside the collimator body or device housing 30, as shown in the embodiment of Figure 17.

[0162] Another materialized apparatus is shown in Figures 33 and 34, which is a multispectral apparatus 38 for curing and / or heating dental materials. The apparatus 38 includes a central photon energy emitter (i.e., LED) 35 with three radially arranged photon energy emitters (i.e., LEDs) 34. The central photon energy emitter 35 is located on a primary heatsink coupled to a thermally conductive body 41. The three radially arranged photon energy emitters 34 are located on separate primary heatsinks parallel to the primary heatsink of the central photon energy emitter 35 and also coupled to the thermally conductive body 41. The apparatus 38 may optionally include an optical transilluminator 39. The apparatus 38 includes a PCB 43, a button 42, a removable and rechargeable battery pack 44, and a rotary knob 40 for selecting the operating mode.

[0163] Referring here to Figure 35, a setup 33 for inclusion within a multispectral apparatus 38 is shown. Setup 33 includes three photon energy emitters (i.e., LEDs) 34 arranged radially on a heatsink / PCB 36, around a central LED 35 mounted on another heatsink / PCB 37 parallel to the heatsink / PCB 36. Both heatsinks are coupled to a thermally conductive body 41. In this example, the four LEDs 34 and 35 emit at least two distinctly different spectra. At least one spectrum is used to raise the photopolymerizable material above ambient temperature, and at least one spectrum is used to cure the photopolymerizable material.

[0164] The following descriptions are illustrative and within the scope of embodiments of the present invention as described herein: Description 1. A method of treating the tooth that needs treatment, A step of heating a dental photopolymerizable material above ambient temperature using a device equipped with a photon energy emission source that emits photon energy, The procedure comprises the step of applying the heated dental photopolymerizable material to cavities on the tooth surface, A method characterized in that photon energy is absorbed by the dental photopolymerizable material, the dental photopolymerizable material container, or the heating additive without photopolymerizing the material, thereby increasing one or more properties, including the energy conversion efficiency from photon energy to heat, or the heating rate of the dental photopolymerizable material; Description 2. The method according to Description 1, characterized in that the photon energy increases the heating rate of the dental photopolymerizable material compared to heating the dental photopolymerizable material without photon energy; Description 3. The method according to any one of descriptions 1 to 2, characterized in that the apparatus emits photon energy in the range of approximately 0.49 eV to 2.38 eV (2500 nm to 520 nm); Description 4. The apparatus is characterized by emitting a photon energy of approximately 1.23 eV to 2.06 eV (1000 nm to 600 nm) according to any one of descriptions 1 to 3; Description 5. The method according to any one of descriptions 1 to 4, characterized in that the dental photopolymerizable material is heated to a temperature of approximately 50°C to approximately 250°C; Description 6. The dental photopolymerizable material is heated to a temperature of approximately 60°C to approximately 80°C, as described in any one of descriptions 1 to 5; Description 7. The method according to any one of descriptions 1 to 6, further comprising the step of curing the dental photopolymerizable material; Description 8. The dental photopolymerizable material is characterized by comprising a composite resin, a high-filler composite resin, a glass ionomer resin, a sealant, a cement, a cavity liner, or a combination thereof, as described in any one of descriptions 1 to 7; Description 9. The method according to any one of descriptions 1 to 8, further comprising the step of curing the dental photopolymerizable material by applying a second source of photon energy emitting a wavelength suitable for absorption by the photopolymerizable material to initiate polymerization; Description 10. The method according to any one of descriptions 1 to 9, characterized in that the photon energy applied to heat the dental photopolymerizable material does not overlap with the absorption of the photoinitiator present in the dental photopolymerizable material; Description 11. The method according to any one of descriptions 1 to 10, characterized in that the dental photopolymerizable material or the dental photopolymerizable material container further comprises a heating additive, a thermal conductivity accelerator, or a polymerization accelerator, or a combination thereof; Description 12. The method according to any one of descriptions 1 to 11, characterized in that the heating additive is a dye having an absorption spectrum that overlaps with the emission spectrum of photon energy emitted from a photon energy source; Description 13. The method according to any one of descriptions 11 to 12, characterized in that the thermal conductivity enhancer is an additive that improves the thermal conductivity of the dental photopolymerizable material or the dental photopolymerizable material container; Description 14. The method according to any one of descriptions 11 to 13, characterized in that the thermal conductivity enhancer is selected from graphite fibers, graphene flakes, ceramic particles, metal oxides, metal particles, carbon nanotubes, and combinations thereof; Description 15. The method according to descriptions 1 to 14, characterized in that the photon energy at the absorption wavelength of the dental photopolymerizable material or the container for the dental photopolymerizable material is emitted during or immediately before the curing step of the dental photopolymerizable material; Description 16. The method according to any one of descriptions 1 to 15, characterized in that, by applying photon energy at the absorption wavelength of the dental photopolymerizable material or the dental photopolymerizable material container, one or more post-curing properties of the dental photopolymerizable material, selected from conversion degree and hardness, are increased compared to the dental photopolymerizable material that has not been heated with photon energy at the absorption wavelength of the dental photopolymerizable material container; Description 17. The method according to any one of descriptions 1 to 16, characterized in that the application of photon energy at the absorption wavelength of the dental photopolymerizable material or the container of the dental photopolymerizable material stimulates one or more photochemical effects selected from photodegradation, photofading, or photocatalysis of the dental photopolymerizable material; Description 18. A photopolymerizable dental composition, Unreacted monomers and Filler and, At least one photoinitiator, A heating additive that increases one or more properties, including the energy conversion efficiency from photon energy to heat, or the heating rate of dental photopolymerizable materials, The heating additive is characterized in that it does not impart an unnatural tooth color to the photopolymerizable dental composition after photopolymerization; Description 19. The composition according to description 18, characterized in that the heating additive and at least one of the photoinitiators are activated by distinctly different photon energy spectra; Description 20. The aforementioned heating additive is High absorbance between 0.49 eV and 2.38 eV (2500 nm to 520 nm), Compatibility with the aforementioned dental photopolymerizable material, Stability at temperatures higher than room temperature, Soluble and dispersible properties within the aforementioned dental photopolymerizable material, It shall not adversely affect the performance of the aforementioned dental photopolymerizable material. High conversion efficiency from photon energy to heat, or, The combination of those characteristics, A composition according to any one of descriptions 18 to 19, characterized by possessing one or more of the following properties; Description 21. The aforementioned heating additive is characterized by comprising a photon energy absorption enhancer, a heat conduction enhancer, or a combination thereof, as described in any one of descriptions 18 to 20; Description 22. The composition according to description 21, characterized in that the photon energy absorption enhancer is present in the dental photopolymerizable material at a concentration of up to approximately 10% by weight of the dental photopolymerizable material; Description 23. The composition according to any one of descriptions 21 to 22, characterized in that the photon energy absorption enhancer is present in the dental photopolymerizable material at a concentration of about 0.001% to about 0.5%; Description 24. The composition according to any one of descriptions 21 to 23, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancer and the normalized emission spectrum of the photon energy source is at least 10% of the area under the curve of either spectrum; Description 25. The composition according to description 24, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancer and the normalized emission spectrum of the photon energy source is at least 25% of the area under the curve of either spectrum; Description 26. The composition according to any one of descriptions 24 to 25, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancer and the normalized emission spectrum of the photon energy source is at least 50% of the area under the curve of either spectrum; Description 27. The composition according to any one of descriptions 21 to 26, characterized in that the heat conduction enhancer is an additive that improves the thermal conductivity of the dental photopolymerizable material; Description 28. The heat conduction enhancer is selected from graphite particles, graphene particles, ceramic particles, metal oxide particles, metal particles, carbon nanotubes, and combinations thereof, as described in any one of descriptions 21 to 27; Description 29. The heat conduction enhancer is concentrated in the dental photopolymerizable material in an amount of approximately 0.01% to approximately 90% by weight. A composition according to any one of descriptions 21 to 28, characterized in that it is present in the dental photopolymerizable material at a certain degree; Description 30. The composition according to any one of descriptions 21 to 29, characterized in that the heat conduction enhancer is present in the dental photopolymerizable material at a concentration of about 1% to about 10% by weight of the dental photopolymerizable material; Description 31. The composition according to any one of descriptions 18 to 30, further comprising a polymerization accelerator comprising a photoinitiator, a coinitiator, or a combination thereof; Description 32. The composition according to description 31, characterized in that the polymerization accelerator increases the photopolymerization of photopolymerizable monomers present in the dental photopolymerizable material; Description 33. The polymerization accelerator is characterized by increasing one or more properties, consisting of improved polymerization, improved curing depth, improved conversion degree using photon energy, and a combination thereof, as described in any one of descriptions 31 to 32; Description 34. The composition according to any one of descriptions 18 to 33, characterized in that the heating additive contains a dye exhibiting an absorbance of 0.49 eV to 2.38 eV (2500 nm to 520 nm); description 35. The composition according to any one of descriptions 18 to 34, characterized in that the dye is present in an amount of about 0.001% to about 10% by weight of the composition; Description 36. The aforementioned composition, a. Unreacted acrylate monomer containing approximately 5-30% by weight, b. An inorganic filler containing approximately 60-95% by weight, c. A photoinitiator containing approximately 0.001 to 0.5% by weight, d. A co-initiator containing approximately 0.001 to 1% by weight, e. A dye containing approximately 0.001 to 10% by weight that exhibits an absorbance of 0.49 eV to 2.38 eV (2500 nm to 520 nm), A composition according to any one of descriptions 18 to 35, characterized by comprising: Description 37. The aforementioned composition, a. Unreacted acrylate monomers containing approximately 40-90% by weight, b. An inorganic filler containing approximately 1-20% by weight, c. A photoinitiator containing approximately 0.001 to 0.5% by weight, d. A co-initiator containing approximately 0.001 to 0.5% by weight, e. A dye containing approximately 0.001 to 10% by weight that exhibits an absorbance of 0.49 eV to 2.38 eV (2500 nm to 520 nm), A composition according to any one of descriptions 18 to 36, characterized by comprising: Description 38. A method of treating the tooth that needs treatment, A step of heating the composition according to any one of paragraphs 18 to 37 with a photon energy emission source that emits photon energy at the absorption wavelength of the composition or the heating additive present in the composition; A step of applying the heated composition to the surface of the tooth; A method characterized by comprising; Paragraph 39. A dental composition, Polyisoprene, An inorganic filler, A radiopaque agent, Wax or resin, and A heating additive that increases one or more properties including the energy conversion efficiency from photon energy to heat or the heating rate of the dental composition; A composition characterized by comprising; Paragraph 40. The composition according to paragraph 39, wherein the polyisoprene contains natural or synthetic gutta-percha; Paragraph 41. The composition according to any one of paragraphs 39 to 40, wherein the polyisoprene is contained in about 10 to 30% by weight of the composition; Paragraph 42. The composition according to any one of paragraphs 39 to 41, wherein the filler is contained in about 50 to 85% by weight of the composition; Paragraph 43. The composition according to any one of paragraphs 39 to 42, wherein the radiopaque agent is contained in about 1 to 35% by weight of the composition; Paragraph 44. The composition according to any one of paragraphs 39 to 43, wherein the wax or resin is contained in about 1 to 10% by weight of the composition; Paragraph 45. The composition according to any one of paragraphs 39 to 44, wherein the heating additive is contained in about 0.001 to 10% by weight of the composition; Paragraph 46. The composition, a. Natural gutta-percha or synthetic gutta-percha comprising about 10 to 30% by weight of the composition, b. An inorganic filler comprising about 50 to 85% by weight of the above composition, c. A radiopaque agent comprising about 1 to 35% by weight of the above composition, d. A wax or resin comprising about 0 to 10% by weight of the composition, e. A heating additive comprising approximately 0.001 to 10% by weight of the composition and exhibiting an absorbance of 0.49 eV to 2.38 eV (2500 nm to 520 nm), A composition according to any one of descriptions 39 to 45, characterized by comprising: Description 47. A method of treating the tooth that needs treatment, A device having a photon energy emission source that emits photon energy at the absorption wavelength of the composition or a heating additive present in the composition, comprising the step of heating one of the compositions described in 39 to 46, The steps include applying the heated composition to the surface of the tooth, A method characterized by comprising; Description 48. A photopolymerizable dental composition, Unreacted monomers and Filler and, At least one photoinitiator is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), and at least one other photoinitiator is activated by an external photon energy, comprising at least two photoinitiators. A co-initiator comprising at least one borate derivative, The photoinitiator does not impart an unnatural tooth color to the photopolymerizable dental composition after photopolymerization. A composition characterized by; Description 49. The composition according to description 48, characterized in that the two photoinitiators comprise a type I or type II photoinitiator or a combination thereof; Description 50. The photopolymerizable material is characterized by comprising two type II photoinitiators, as described in any one of descriptions 48 to 49; Description 51. The composition according to any one of descriptions 48 to 50, characterized in that the photoinitiator, which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), promotes photopolymerization; Description 52. The composition according to any one of descriptions 48 to 51, characterized in that the photoinitiator, which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), is present in a concentration of about 0.0001 to 0.5% by weight of the composition; Description 53. The composition according to any one of descriptions 48 to 52, characterized in that the photoinitiator, which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), is present in a concentration of about 0.001 to 0.1% by weight of the composition; Description 54. The composition according to any one of descriptions 48 to 53, characterized in that the borate derivative is borate V; Description 55. The composition according to any one of descriptions 48 to 54, characterized in that the borate derivative is at least 10 times more concentrated than at least one of the photoinitiators which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm); Description 56. The photoinitiator, activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), is characterized by photofading and / or consumption during a photopolymerization process occurring at 0.49 eV to 1.90 eV (2500 nm to 650 nm), thereby reducing the visible color, as described in any one of descriptions 48 to 55; Description 57. The photoinitiator, activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), increases radical formation while simultaneously promoting the curing of the material, and provides a visible change indicating complete curing as the formed radicals are depleted and bleached; the composition according to any one of descriptions 48 to 56; Description 58. The aforementioned composition, a. Unreacted acrylate monomer containing approximately 5-30% by weight, b. An inorganic filler containing approximately 60-95% by weight, c. A first photoinitiator containing approximately 0.001 to 0.5% by weight, d. A second photoinitiator containing approximately 0.001 to 0.5% by weight and exhibiting an absorbance of 0.49 eV to 1.90 eV (2500 nm to 650 nm), e. A borate derivative co-initiator containing approximately 0.01-5% by weight, A composition according to any one of descriptions 48 to 57, characterized by comprising: Description 59. The aforementioned composition, a. Unreacted acrylate monomers containing approximately 40-90% by weight, b. An inorganic filler containing approximately 1-20% by weight, c. A first photoinitiator containing approximately 0.001 to 0.5% by weight, d. A second photoinitiator containing approximately 0.001 to 0.5% by weight and exhibiting an absorbance of 0.49 eV to 1.90 eV (2500 nm to 650 nm), e. A borate derivative co-initiator containing approximately 0.01-5% by weight, A composition according to any one of descriptions 48 to 58, characterized by comprising: Description 60. A method of treating the tooth that needs treatment, A device having a photon energy emission source that emits photon energy at the absorption wavelength of the composition or a photoinitiator present in the composition, comprising the step of heating one of the compositions described in 48 to 59, The steps include applying the heated composition to the surface of the tooth, A method characterized by comprising; Description 61. A material container, Comprising a thermoplastic resin and at least one photon energy absorption promoting additive for forming the container, Comprising, The additive increases one or more properties including an improvement in the energy conversion efficiency from photon energy to heat or an increase in the heating rate of the material contained therein, The additive has an optical density value greater than 1 with respect to photon energy of 0.49 eV to 2.38 eV (2500 nm to 520 nm) after thermoplastic injection molding, and is characterized as a container; Description 62. The container according to Description 61, further comprising a pigment, a colorant, a plasticizer, or a filler, or a combination thereof; Description 63. The container according to any one of Descriptions 61 to 62, characterized in that the container integrally includes an additional photon energy absorption promoting additive, or at least one heat conduction promoting additive, or a combination thereof; Description 64. The container according to Description 63, characterized in that the photon energy absorption promoting additive is present in the container at a concentration of about 0.01 to 20% by weight of the dental photopolymerizable material container; Description 65. The container according to any one of Descriptions 63 to 64, characterized in that the photon energy absorption promoting additive is present in the container at a concentration of about 0.1 to 5% by weight of the dental photopolymerizable material container; Description = 66. The container according to any one of Descriptions 61 to 65, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption promoting additive and the normalized emission spectrum of the photon energy source is at least 10% of the area under the curve of either spectrum; Description 67. The container according to description 66, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancing additive and the normalized emission spectrum of the photon energy source is at least 25% of the area under the curve of either spectrum; Description 68. The container according to any one of descriptions 66 to 67, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancer additive and the normalized emission spectrum of the photon energy source is at least 50% of the area under the curve of either spectrum; Description 69. The aforementioned heat conduction enhancer is characterized by being an additive that improves the thermal conductivity of dental material containers. A container as described in any one of descriptions 63 to 68; Description 70. The container according to any one of descriptions 63 to 69, characterized in that the heat conduction enhancer is selected from graphite particles, graphene particles, ceramic particles, metal oxide particles, metal particles, carbon nanotubes, and combinations thereof; Description 71. The container according to any one of descriptions 63 to 70, characterized in that the heat conduction enhancer is present in the housing at a concentration of approximately 0.1 to 50% by weight; Description 72. The container according to any one of descriptions 63 to 71, characterized in that the heat conduction accelerator is present in the dental photopolymerizable material container at a concentration of approximately 1 to 10% by weight; description 73. The container according to any one of descriptions 61 to 72, characterized in that the housing sufficiently blocks light from being transmitted through the container to the dental photopolymerizable material contained therein, thereby preventing the dental photopolymerizable material from hardening within the container; Description 74. The container according to any one of descriptions 61 to 73, characterized in that the thermoplastic resin constitutes approximately 50 to 95% by weight of the container; Description 75. The container according to any one of descriptions 61 to 74, characterized in that the photon energy absorption enhancing additive constitutes about 0.1 to 50% by weight of the composition; Description 76. The container is characterized in that it comprises a thermoplastic resin constituting about 95% by weight of the container and a heat additive constituting about 5% by weight of the container, as described in any one of descriptions 61 to 75; Description 77. A method of treating the tooth that is in need of treatment, A step of heating a container as described in any one of descriptions 61 to 76, The container is heated by an apparatus having a photon energy emission source that emits photon energy at the absorption wavelength of the container, or a heating additive present in the container, or dental material contained in the container. The steps include applying the heated dental material to the surface of the tooth, A method characterized by comprising; Description 78. A container for holding dental materials, a) A step of heating the thermoplastic resin to at least its softening point, b) The step of maintaining and controlling the temperature of the resin at least to its softening point, c) While maintaining and controlling the temperature of the resin at least to its softening point, add approximately 0.1 to 5% of an additive having high photon energy absorption in the 520 nm to 2500 nm range, and add a dispersant as necessary. d) A step of mixing the mixtures a to c while maintaining the temperature at least to the softening point of the resin, to homogenize the mixture, e) The step of extruding the heated mixtures a-d into a mold cavity including the shape of a dental material container, and allowing it to cool before being removed from the cavity, A container according to any one of descriptions 61 to 77, characterized by being made by a process comprising: Description 79. A container for holding dental materials, a) A step of heating the thermoplastic resin to at least its softening point, b) The step of maintaining and controlling the temperature of the resin at least to its softening point, c) While maintaining and controlling the temperature of the resin at least to its softening point, add approximately 0.1 to 5% of an additive having high photon energy absorption in the 520 nm to 2500 nm range, and add a dispersant as necessary. d) A step of mixing the mixtures a to c while maintaining the temperature at least to the softening point of the resin, to homogenize the mixture, e) The step of creating pellets from mixtures a-d so that they can later be used for injection molding of dental material containers, A container according to any one of descriptions 61 to 77, characterized by being made by a process comprising: Description 80. A container according to any one of descriptions 61 to 79, characterized in that the manufactured container is filled with dental material; Description 81. A device for heating dental material and applying the heated dental material to the surface or cavity of a tooth, a. The main unit, b. A plunger movably mounted within the body for engaging with a dental material container, c. An actuation means connected to the plunger for controllably distributing dental material from the dental material container, d. A distally mounted photon energy emitter consisting of an electroluminescent source that generates 0.5 watts to 20 watts of light power, e. A rechargeable power supply electrically connected to an electroluminescent source, f. A primary heatsink, which is located within or forms part of the main body of the device, to which an electroluminescent source is coupled, g. A receptacle on the main body of the device for safely receiving the dental material container so that the dental material container is held in close proximity to the electroluminescence source, Apparatus characterized by being equipped with; Description 82. The apparatus described in description 81 is characterized in that the photon energy emission source is capable of emitting photon energies in the range of 0.49 eV to 2.38 eV (2500 nm to 520 nm); Description 83. The apparatus according to any one of descriptions 81 to 82, characterized in that the photon energy emission source emits photon energy in the range of 1.24 eV to 1.77 eV (1000 nm to 700 nm); Description 84. The apparatus according to any one of descriptions 81 to 83, characterized in that the electroluminescence source includes a light-emitting diode (LED), a laser diode, or a combination thereof; Description 85. The apparatus according to any one of descriptions 81 to 84, characterized in that the electroluminescent source is less than approximately 1 cm from a dental material container containing dental material; Description 86. The apparatus according to any one of descriptions 81 to 85, further comprising a collimator including a lens or optical fiber for increasing the photon energy irradiance to a container having dental material; Description 87. The primary heat sink is coupled to a secondary heat sink included in the device, or constitutes part of the housing of the device. The apparatus according to any one of descriptions 81 to 86, characterized in that the secondary heat sink prevents the apparatus from reaching an unsafely high temperature exceeding 50°C; Description 88. The apparatus according to any one of descriptions 81 to 87, characterized in that the primary or secondary heat sink is coupled to a heat pipe, and the heat pipe prevents the apparatus from reaching high temperatures; Description 89. The device further includes a heat sensor, The heat sensor prevents the device from reaching high temperatures that could cause dental materials to deteriorate or endanger the operator or patient during treatment. The apparatus according to any one of descriptions 81 to 88, characterized in that the heat sensor can indirectly monitor the temperature of the dental material and reduce or eliminate the output of the photon energy source; Description 90. The apparatus according to any one of descriptions 81 to 89, further comprising a loop control feedback system for maintaining a desired temperature without reaching an undesirable temperature that could cause deterioration of dental materials or endanger the operator or patient during treatment; Description 91. The system further comprises an absorption sensor for determining the absorption characteristics of the dental material or the dental material container, The absorption sensor is characterized in that it provides an output for adjusting the output and / or duration of the photon energy source in order to achieve a desired temperature of the dental material. The apparatus described in any one of the ~90 items; Description 92. The apparatus according to any one of descriptions 81 to 91, further comprising an additional light source for curing dental photopolymerizable materials; Description 93. The apparatus according to any one of descriptions 81 to 92, characterized in that the additional light source emits light with a wavelength of approximately 365 nm to 500 nm; Description 94. An apparatus according to any one of descriptions 81 to 93, characterized in that an additional light source for curing dental photopolymerizable materials emits a light power of 500 mW to 3 W; Description 95. An apparatus according to any one of descriptions 81 to 94, characterized in that an additional light source for curing dental photopolymerizable materials emits a light power of 700 mW to 1.5 W; Description 96. The apparatus according to any one of descriptions 81 to 95, characterized in that the photon energy emission output is used delayed or simultaneously with the photon energy emission output of an additional light source to cure a dental photopolymerizable material; Description 97. The apparatus according to any one of descriptions 81 to 96, characterized in that the curing light and photon energy source are positioned distal to the apparatus to access the patient's oral cavity; Description 98. A handheld multispectral device for accelerating the curing of photopolymerizable dental materials, a. Thermal conductors and, b. comprising at least four separate distally mounted photon energy sources that generate at least two separate emission spectra, a. One photon energy source is positioned in the center, and at least three photon energy sources are arranged radially around the centrally positioned photon energy source. b. The output of the centrally located photon energy source is located in at least three radial directions. The output of the photon energy emission source is either connected to, delayed by, or used simultaneously with, c. Curing the photopolymerizable dental material using at least one emission spectrum, and raising the temperature of the photopolymerizable dental material above the ambient temperature during curing using at least one emission spectrum. d. At least four of the photon energy sources are composed of light-emitting diodes, c. At least four individual photon energy sources are coupled to at least one primary heat sink located within the main body of the device. d. At least one of the primary heat sinks is coupled to the thermal conductor, e. The device is characterized in that the light-emitting diode is electrically connected to a DC power supply; Description 99. The apparatus according to description 98, characterized in that the DC power supply consists of a removable rechargeable power supply; Description 100. The apparatus according to any one of descriptions 98 to 99, characterized in that at least three radially mounted light-emitting diodes are arranged on separate primary heatsinks around the light-emitting diodes on the centrally located primary heatsink, providing a substantially uniform beam profile and illumination field; Description 101. The apparatus according to any one of descriptions 98 to 100, characterized in that at least four of the light-emitting diodes are collimated to produce a spot size of approximately 1 cm at a distance of 1 to 10 mm; Description 102. The apparatus according to any one of descriptions 98 to 101, characterized in that at least one of the photon energy sources for curing a photopolymerizable dental material emits light in the range of 365 nm to 500 nm with an optical output of 500 mW to 3 W; Description 103. The apparatus according to any one of descriptions 98 to 102, characterized in that at least one of the photon energy sources for raising the temperature of the photopolymerizable dental material above the ambient temperature during curing emits light in the range of 520 nm to 2500 nm with a light power of 500 mW to 3 W; Description 104. A method for treating a target tooth, comprising the step of heating a dental composite material or a container containing a dental composite material using the apparatus described in any one of descriptions 81 to 103.

[0165] While the invention as described herein is described in relation to the embodiments described herein, those skilled in the art will understand that additions, modifications, substitutions, and deletions not specifically described may be made without departing from the spirit and scope of the invention as defined in the appended claims. Therefore, it should be understood that the above detailed description is illustrative and not restrictive, and that the following claims, including all equivalents, are intended to define the spirit and scope of the invention.

Claims

1. A method of treating the tooth that needs treatment, A step of heating a dental photopolymerizable material above ambient temperature using a device equipped with a photon energy emission source that emits photon energy, The procedure comprises the step of applying the heated dental photopolymerizable material to cavities on the tooth surface, A method characterized in that photon energy is absorbed by the dental photopolymerizable material, the dental photopolymerizable material container, or the heating additive without photopolymerizing the material, thereby increasing one or more properties, including the energy conversion efficiency from photon energy to heat, or the heating rate of the dental photopolymerizable material.

2. The method according to claim 1, characterized in that the photon energy increases the heating rate of the dental photopolymerizable material compared to heating the dental photopolymerizable material without photon energy.

3. The method according to claim 1, characterized in that the apparatus emits photon energy in the range of approximately 0.49 eV to 2.38 eV (2500 nm to 520 nm).

4. The method according to claim 1, characterized in that the apparatus emits photon energy of approximately 1.23 eV to 2.06 eV (1000 nm to 600 nm).

5. The method according to claim 1, characterized in that the dental photopolymerizable material is heated to a temperature of about 50°C to about 250°C.

6. The method according to claim 1, characterized in that the dental photopolymerizable material is heated to a temperature of about 60°C to about 80°C.

7. The method according to claim 1, further comprising the step of curing the dental photopolymerizable material.

8. The method according to claim 1, characterized in that the dental photopolymerizable material includes a composite resin, a high-filler composite resin, a glass ionomer resin, a sealant, a cement, a cavity liner, or a combination thereof.

9. The method according to claim 1, further comprising the step of curing the dental photopolymerizable material by applying a second source of photon energy that emits wavelengths suitable for absorption by the photopolymerizable material to initiate polymerization.

10. The method according to claim 1, characterized in that the photon energy applied to heat the dental photopolymerizable material does not overlap with the absorption of the photoinitiator present in the dental photopolymerizable material.

11. The method according to claim 1, characterized in that the dental photopolymerizable material or the dental photopolymerizable material container further comprises a heating additive, a thermal conductivity accelerator, or a polymerization accelerator, or a combination thereof.

12. The method according to claim 1, characterized in that the heating additive is a dye having an absorption spectrum that overlaps with the emission spectrum of photon energy emitted from the photon energy source.

13. The thermal conductivity enhancer is the dental photopolymerizable material or the dental photopolymerizable material container. The method according to 11, characterized in that it is an additive that improves thermal conductivity.

14. The method according to 11, characterized in that the thermal conductivity enhancer is selected from graphite fibers, graphene flakes, ceramic particles, metal oxides, metal particles, carbon nanotubes, and combinations thereof.

15. The method according to claim 1, characterized in that the photon energy at the absorption wavelength of the dental photopolymerizable material or the container for the dental photopolymerizable material is emitted during or immediately before the curing step of the dental photopolymerizable material.

16. The method according to claim 1, characterized in that by applying photon energy at the absorption wavelength of the dental photopolymerizable material or the dental photopolymerizable material container, one or more post-curing properties of the dental photopolymerizable material, selected from conversion degree and hardness, are increased compared to the dental photopolymerizable material that has not been heated with photon energy at the absorption wavelength of the dental photopolymerizable material container.

17. The method according to claim 1, characterized in that the application of photon energy at the absorption wavelength of the dental photopolymerizable material or the dental photopolymerizable material container stimulates one or more photochemical effects selected from photodegradation, photofading, or photocatalysis of the dental photopolymerizable material.

18. A photopolymerizable dental composition, Unreacted monomers and Filler and, At least one photoinitiator, A heating additive that increases one or more properties, including the energy conversion efficiency from photon energy to heat, or the heating rate of dental photopolymerizable materials, The heating additive is characterized in that it does not impart an unnatural tooth color to the photopolymerizable dental composition after photopolymerization.

19. The composition according to claim 18, characterized in that the heating additive and at least one of the photoinitiators are activated by distinctly different photon energy spectra.

20. The aforementioned heating additive is High absorbance between 0.49 eV and 2.38 eV (2500 nm to 520 nm), Compatibility with the aforementioned dental photopolymerizable material, Stability at temperatures higher than room temperature, Soluble and dispersible properties within the aforementioned dental photopolymerizable material, It shall not adversely affect the performance of the aforementioned dental photopolymerizable material. High conversion efficiency from photon energy to heat, or, The combination of those characteristics, The composition according to claim 18, characterized in that it possesses one or more of the following properties.

21. The composition according to claim 18, characterized in that the heating additive includes a photon energy absorption enhancer, a heat conduction enhancer, or a combination thereof.

22. The composition according to claim 21, characterized in that the photon energy absorption enhancer is present in the dental photopolymerizable material at a concentration of up to approximately 10% by weight of the dental photopolymerizable material.

23. The composition according to claim 21, characterized in that the photon energy absorption enhancer is present in the dental photopolymerizable material at a concentration of about 0.001% to about 0.5%.

24. The composition according to claim 21, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancer and the normalized emission spectrum of the photon energy source is at least 10% of the area under the curve of either spectrum.

25. The composition according to claim 24, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancer and the normalized emission spectrum of the photon energy source is at least 25% of the area under the curve of either spectrum.

26. The composition according to claim 24, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancer and the normalized emission spectrum of the photon energy source is at least 50% of the area under the curve of either spectrum.

27. The composition according to claim 21, characterized in that the heat conduction promoter is an additive that improves the thermal conductivity of the dental photopolymerizable material.

28. The composition according to claim 21, characterized in that the heat conduction promoter is selected from graphite particles, graphene particles, ceramic particles, metal oxide particles, metal particles, carbon nanotubes, and combinations thereof.

29. The composition according to claim 21, characterized in that the heat conduction promoter is present in the dental photopolymerizable material at a concentration of about 0.01% to about 90% by weight of the dental photopolymerizable material.

30. The composition according to claim 21, characterized in that the heat conduction promoter is present in the dental photopolymerizable material at a concentration of about 1% to about 10% by weight of the dental photopolymerizable material.

31. The composition according to claim 18, further comprising a polymerization accelerator comprising a photoinitiator, a coinitiator, or a combination thereof.

32. The composition according to claim 31, characterized in that the polymerization accelerator increases the photopolymerization of photopolymerizable monomers present in the dental photopolymerizable material.

33. The polymerization accelerator is characterized by increasing one or more properties, consisting of improved polymerization, improved curing depth, improved conversion degree using photon energy, and a combination of these properties. The composition according to claim 31.

34. The composition according to claim 18, characterized in that the heating additive contains a dye exhibiting an absorbance of 0.49 eV to 2.38 eV (2500 nm to 520 nm).

35. The composition according to claim 34, characterized in that the dye is contained in the composition in an amount of about 0.001% to about 10% by weight.

36. The aforementioned composition, a. Unreacted acrylate monomer containing approximately 5-30% by weight, b. An inorganic filler containing approximately 60-95% by weight, c. A photoinitiator containing approximately 0.001 to 0.5% by weight, d. A co-initiator containing approximately 0.001 to 1% by weight, e. A dye containing approximately 0.001 to 10% by weight and exhibiting an absorbance of 0.49 eV to 2.38 eV (2500 nm to 520 nm), The composition according to claim 18, characterized by comprising:

37. The aforementioned composition, a. Unreacted acrylate monomers containing approximately 40-90% by weight, b. An inorganic filler containing approximately 1 to 20% by weight, c. A photoinitiator containing approximately 0.001 to 0.5% by weight, d. A co-initiator containing approximately 0.001 to 0.5% by weight, e. A dye containing approximately 0.001 to 10% by weight and exhibiting an absorbance of 0.49 eV to 2.38 eV (2500 nm to 520 nm), The composition according to claim 18, characterized by comprising:

38. A method of treating the tooth that needs treatment, A step of heating the composition according to claim 18 with an apparatus having a photon energy emission source that emits photon energy at the absorption wavelength of the composition or a heating additive present in the composition, The steps include applying the heated composition to the surface of the tooth, A method characterized by comprising:

39. A dental composition, Polyisoprene, Inorganic fillers, Radiopaque agents, wax or resin, and Heating additives that increase one or more properties, including the energy conversion efficiency from photon energy to heat, or the heating rate of dental compositions. A composition characterized by comprising the following:

40. The composition according to claim 39, characterized in that the polyisoprene contains natural or synthetic gutta-percha.

41. The composition according to claim 39, characterized in that the polyisoprene is contained in about 10 to 30% by weight of the composition.

42. The composition according to claim 39, characterized in that the filler is contained in about 50 to 85% by weight of the composition.

43. The composition according to claim 39, characterized in that the radiopaque agent is contained in about 1 to 35% by weight of the composition.

44. The composition according to claim 39, characterized in that the wax or resin is contained in about 1 to 10% by weight of the composition.

45. The composition according to claim 39, characterized in that the heating additive is contained in about 0.001 to 10% by weight of the composition.

46. The aforementioned composition, a. Natural gutta-percha or synthetic gutta-percha comprising about 10 to 30% by weight of the composition, b. An inorganic filler comprising about 50 to 85% by weight of the composition, c. A radiopaque agent comprising about 1 to 35% by weight of the composition, d. A wax or resin comprising about 0 to 10% by weight of the composition, e. A heating additive comprising about 0.001 to 10% by weight of the composition and exhibiting an absorbance of 0.49 eV to 2.38 eV (2500 nm to 520 nm), The composition according to claim 39, characterized by comprising:

47. A method of treating the tooth that needs treatment, A step of heating the composition of claim 39 with an apparatus having a photon energy emission source that emits photon energy at the absorption wavelength of the composition or a heating additive present in the composition, The steps include applying the heated composition to the surface of the tooth, A method characterized by comprising:

48. A photopolymerizable dental composition, Unreacted monomers and Filler and, At least one photoinitiator is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), and at least one other photoinitiator is externally... At least two photoinitiators activated by photon energy, A co-initiator comprising at least one borate derivative, The photoinitiator is characterized in that it does not impart an unnatural tooth color to the photopolymerizable dental composition after photopolymerization.

49. The composition according to claim 48, characterized in that the two photoinitiators include a type I or type II photoinitiator or a combination thereof.

50. The composition according to claim 48, characterized in that the photopolymerizable material comprises two type II photoinitiators.

51. The composition according to claim 48, characterized in that the photoinitiator, which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), promotes photopolymerization.

52. The composition according to claim 48, characterized in that the photoinitiator, which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), is present in the composition at a concentration of about 0.0001 to 0.5% by weight.

53. The composition according to claim 48, characterized in that the photoinitiator, which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), is present in the composition at a concentration of about 0.001 to 0.1% by weight.

54. The composition according to claim 48, characterized in that the borate derivative is borate V.

55. The composition according to claim 48, characterized in that the borate derivative is at least 10 times more concentrated than at least one of the photoinitiators which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm).

56. The composition according to claim 48, characterized in that the photoinitiator, which is activated by a photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm), is photobleached and / or consumed during a photopolymerization process occurring at 0.49 eV to 1.90 eV (2500 nm to 650 nm), thereby reducing the visible color.

57. Photon energy in the range of 0.49 eV to 1.90 eV (2500 nm to 650 nm) The composition according to claim 48, characterized in that the photoinitiator activated by increases radical formation and simultaneously promotes the curing of the material, and as the formed radicals are depleted, bleaching occurs, providing a visible change indicating complete curing.

58. The aforementioned composition, a. Unreacted acrylate monomer containing approximately 5-30% by weight, b. An inorganic filler containing approximately 60-95% by weight, c. A first photoinitiator containing approximately 0.001 to 0.5% by weight, d. A second photoinitiator containing approximately 0.001 to 0.5% by weight and exhibiting an absorbance of 0.49 eV to 1.90 eV (2500 nm to 650 nm), e. A borate derivative co-initiator containing approximately 0.01 to 5% by weight, The composition according to claim 48, characterized by comprising:

59. The aforementioned composition, a. Unreacted acrylate monomers containing approximately 40-90% by weight, b. An inorganic filler containing approximately 1 to 20% by weight, c. A first photoinitiator containing approximately 0.001 to 0.5% by weight, d. A second photoinitiator containing approximately 0.001 to 0.5% by weight and exhibiting an absorbance of 0.49 eV to 1.90 eV (2500 nm to 650 nm), e. A borate derivative co-initiator containing approximately 0.01 to 5% by weight, The composition according to claim 48, characterized by comprising:

60. A method of treating the tooth that needs treatment, A step of heating the composition of claim 48 with an apparatus having a photon energy emission source that emits photon energy at the absorption wavelength of the composition or a photoinitiator present in the composition, The steps include applying the heated composition to the surface of the tooth, A method characterized by comprising:

61. A container for materials, A thermoplastic resin and at least one photon energy absorption enhancing additive that forms the container, Equipped with, The additive enhances one or more properties, including an improvement in the energy conversion efficiency from photon energy to heat, or an increase in the heating rate of the material contained within. The aforementioned additive is characterized in that, after injection molding of thermoplastic plastic, the container has an optical density value greater than 1 for photon energies of 0.49 eV to 2.38 eV (2500 nm to 520 nm).

62. The container according to claim 61, further comprising a pigment, a colorant, a plasticizer, or a filler, or a combination thereof.

63. The container according to claim 61, characterized in that the container includes an additional photon energy absorption enhancing additive, or at least one heat conduction enhancing agent, or a combination thereof, as an integral part of the container.

64. The container according to claim 63, characterized in that the photon energy absorption enhancing additive is present in the container at a concentration of about 0.01 to 20% by weight of the container of dental photopolymerizable material.

65. The container according to claim 63, characterized in that the photon energy absorption enhancing additive is present in the container at a concentration of about 0.1 to 5% by weight of the dental photopolymerizable material container.

66. The container according to claim 61, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancing additive and the normalized emission spectrum of the photon energy source is at least 10% of the area under the curve of either spectrum.

67. The container according to claim 66, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancing additive and the normalized emission spectrum of the photon energy source is at least 25% of the area under the curve of either spectrum.

68. The container according to claim 66, characterized in that the area intersection of the normalized absorption spectrum of the photon energy absorption enhancing additive and the normalized emission spectrum of the photon energy source is at least 50% of the area under the curve of either spectrum.

69. The container according to claim 63, characterized in that the heat conduction promoter is an additive that improves the thermal conductivity of the dental material container.

70. The container according to claim 63, characterized in that the heat conduction enhancer is selected from graphite particles, graphene particles, ceramic particles, metal oxide particles, metal particles, carbon nanotubes, and combinations thereof.

71. The container according to claim 63, characterized in that the heat conduction promoter is present in the housing at a concentration of about 0.1 to 50% by weight.

72. The container according to claim 63, characterized in that the heat conduction accelerator is present in the dental photopolymerizable material container at a concentration of about 1 to 10% by weight of the dental photopolymerizable material container.

73. The container according to claim 61, characterized in that the housing sufficiently blocks light from being transmitted through the container to the dental photopolymerizable material contained therein, thereby preventing the dental photopolymerizable material from hardening inside the container.

74. The container according to claim 61, characterized in that the thermoplastic resin constitutes about 50 to 95% by weight of the container.

75. The container according to claim 61, characterized in that the photon energy absorption enhancing additive constitutes about 0.1 to 50% by weight of the composition.

76. The container according to claim 61, characterized in that the container comprises a thermoplastic resin constituting about 95% by weight of the container and a heat additive constituting about 5% by weight of the container.

77. A method of treating the tooth that is in need of treatment, A step of heating the container according to claim 61, The container is heated by an apparatus having a photon energy emission source that emits photon energy at the absorption wavelength of the container, or a heating additive present in the container, or dental material contained in the container. The steps include applying the heated dental material to the surface of the tooth, A method characterized by comprising:

78. A container for holding dental materials, a) A step of heating the thermoplastic resin to at least its softening point, b) The step of maintaining and controlling the temperature of the resin at least to its softening point, c) While maintaining and controlling the temperature of the resin at least to its softening point, add about 0.1 to 5% of an additive having high photon energy absorption in the range of 520 nm to 2500 nm, and add a dispersant as necessary. d) A step of mixing the mixtures a to c while maintaining the temperature at least to the softening point of the resin, to homogenize the mixture, e) The step of extruding the heated mixtures a to d into a mold cavity including the shape of a dental material container, and allowing it to cool before being removed from the cavity, The container according to claim 61, characterized in that it is made by a process comprising the following:

79. A container for holding dental materials, a) A step of heating the thermoplastic resin to at least its softening point, b) The step of maintaining and controlling the temperature of the resin at least to its softening point, c) While maintaining and controlling the temperature of the resin at least to its softening point, add about 0.1 to 5% of an additive having high photon energy absorption in the range of 520 nm to 2500 nm, and add a dispersant as necessary. d) A step of mixing the mixtures a to c while maintaining the temperature at least to the softening point of the resin, to homogenize the mixture, e) The step of preparing pellets from mixtures a to d so that they can later be used for injection molding of dental material containers, The container according to claim 61, characterized in that it is made by a process comprising the following:

80. The container according to claim 61, characterized in that the manufactured container is filled with dental material.

81. A device for heating dental material and applying the heated dental material to the surface or cavity of a tooth, h. The main body and, i. A plunger movably mounted within the main body for engaging with a dental material container, j. An actuator connected to the plunger for controllably distributing dental material from the dental material container, k. A distally mounted photon energy emission source consisting of an electroluminescent source that generates 0.5 watts to 20 watts of light power, l. A rechargeable power supply electrically connected to an electroluminescent source, m. A primary heatsink, which is located within the main body of the device or constitutes part of the main body of the device, to which an electroluminescent source is coupled, n. A receptacle on the main body of the device for safely receiving the dental material container so that the dental material container is held in close proximity to the electroluminescence source, An apparatus characterized by being equipped with

82. The apparatus according to claim 81, characterized in that the photon energy emission source can emit photon energies of 0.49 eV to 2.38 eV (2500 nm to 520 nm).

83. The apparatus according to claim 81, characterized in that the photon energy emission source emits photon energy in the range of 1.24 eV to 1.77 eV (1000 nm to 700 nm).

84. The apparatus according to claim 81, characterized in that the electroluminescence source includes a light-emitting diode (LED), a laser diode, or a combination thereof.

85. The apparatus according to claim 79, characterized in that the electroluminescent source is less than about 1 cm from a dental material container having dental material therein.

86. The apparatus according to claim 81, further comprising a collimator including a lens or optical fiber for increasing the photon energy irradiance to a container having dental material.

87. The primary heat sink is coupled to a secondary heat sink included in the device, or constitutes part of the housing of the device. The apparatus according to claim 81, characterized in that the secondary heat sink prevents the apparatus from reaching an unsafely high temperature of 50°C.

88. The apparatus according to claim 81, wherein the primary heat sink or secondary heat sink is connected to a heat pipe, and the heat pipe prevents the apparatus from reaching a high temperature.

89. The device further includes a heat sensor, The heat sensor prevents the device from reaching high temperatures that could cause dental materials to deteriorate or endanger the operator or patient during treatment. The apparatus according to claim 81, characterized in that the heat sensor can indirectly monitor the temperature of the dental material and reduce or eliminate the output of the photon energy source.

90. The apparatus according to claim 81, further comprising a loop control feedback system for maintaining a desired temperature without reaching an undesirable temperature that could cause deterioration of dental materials or endanger the operator or patient during treatment.

91. The system further comprises an absorption sensor for determining the absorption characteristics of the dental material or the dental material container, The absorption sensor is characterized in that it provides an output for adjusting the output and / or duration of the photon energy source in order to achieve a desired temperature of the dental material.8 The apparatus described in 1.

92. The apparatus according to claim 81, further comprising an additional light source for curing dental photopolymerizable materials.

93. The apparatus according to claim 81, characterized in that the additional light source emits light with a wavelength of approximately 365 nm to 500 nm.

94. The apparatus according to claim 81, characterized in that an additional light source for curing dental photopolymerizable materials emits a light power of 500 mW to 3 W.

95. The apparatus according to claim 81, characterized in that an additional light source for curing dental photopolymerizable materials emits a light power of 700 mW to 1.5 W.

96. The apparatus according to claim 81, characterized in that the photon energy emission output is used delayed or simultaneously with the photon energy emission output of an additional light source to cure a dental photopolymerizable material.

97. The apparatus according to claim 81, characterized in that the curing light and photon energy source are positioned distal to the apparatus to access the patient's oral cavity.

98. A handheld multispectral device for accelerating the curing of photopolymerizable dental materials, f. Thermal conductors and, g. comprising at least four separate distally mounted photon energy sources that generate at least two separate emission spectra, a. One photon energy source is positioned in the center, and at least three photon energy sources are arranged radially around the centrally positioned photon energy source. b. The output of the centrally located photon energy source is connected to, delayed by, or used simultaneously with the outputs of at least three radially located photon energy emission sources. c. Curing the photopolymerizable dental material using at least one emission spectrum, and raising the temperature of the photopolymerizable dental material above the ambient temperature during curing using at least one emission spectrum. d. At least four of the photon energy sources are composed of light-emitting diodes, h. At least four individual photon energy sources are coupled to at least one primary heat sink located within the main body of the device. i. At least one of the primary heat sinks is coupled to the heat conductor, j. The apparatus is characterized in that the light-emitting diode is electrically connected to a DC power supply.

99. The apparatus according to claim 98, characterized in that the DC power supply consists of a removable rechargeable power supply.

100. The apparatus according to 98, wherein at least three radially mounted light-emitting diodes are arranged on separate primary heatsinks around the light-emitting diodes on the centrally located primary heatsink, providing a substantially uniform beam profile and illumination field.

101. The apparatus according to 98, characterized in that at least four of the light-emitting diodes are collimated to generate a spot size of about 1 cm at a distance of 1 to 10 mm.

102. The apparatus according to 98, characterized in that at least one of the photon energy sources for curing a photopolymerizable dental material emits light in the range of 365 nm to 500 nm with an optical output of 500 mW to 3 W.

103. The apparatus according to 98, wherein at least one photon energy source for raising the temperature of the photopolymerizable dental material above the ambient temperature during curing emits light in the range of 520 nm to 2500 nm with an optical power of 500 mW to 3 W.

104. A method for treating a target tooth, comprising the step of heating a dental composite material or a container containing a dental composite material using the apparatus described in claim 81 or 98.

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