Patent Grant
8998613
The present invention relates to devices and methods for measuring optical characteristics such as color of objects such as teeth, and more particularly to devices and methods for measuring the color and other optical characteristics of teeth or other objects or surfaces with a hand-held probe that presents minimal problems with height or angular dependencies. The present invention also relates to devices and methods using a camera and a calibration chart imaged with the camera, as described more particularly, for example, in connection with
A need has been recognized for devices and methods of measuring the color or other optical characteristics of teeth and other objects in the field of dentistry. Various color measuring devices such as spectrophotometers and colorimeters are known in the art. To understand the limitations of such conventional devices, it is helpful to understand certain principles relating to color. Without being bound by theory, Applicants provide the following discussion. In the discussion herein, reference is made to an “object,” etc., and it should be understood that in general such discussion may include teeth as the “object.”
The color of an object determines the manner in which light is reflected from the surface of the object. When light is incident upon an object, the reflected light will vary in intensity and wavelength dependent upon the color of the surface of the object. Thus, a red object will reflect red light with a greater intensity than a blue or a green object, and correspondingly a green object will reflect green light with a greater intensity than a red or blue object.
One method of quantifying the color of an object is to illuminate it with broad band spectrum or “white” light, and measure the spectral properties of the reflected light over the entire visible spectrum and compare the reflected spectrum with the incident light spectrum. Such instruments typically require a broad band spectrophotometer, which generally are expensive, bulky and relatively cumbersome to operate, thereby limiting the practical application of such instruments.
For certain applications, the broad band data provided by a spectrophotometer is unnecessary. For such applications, devices have been produced or proposed that quantify color in terms of a numerical value or relatively small set of values representative of the color of the object.
It is known that the color of an object can be represented by three values. For example, the color of an object can be represented by red, green and blue values, an intensity value and color difference values, by a CIE value, or by what are known as “tristimulus values” or numerous other orthogonal combinations. It is important that the three values be orthogonal; i.e., any combination of two elements in the set cannot be included in the third element.
One such method of quantifying the color of an object is to illuminate an object with broad band “white” light and measure the intensity of the reflected light after it has been passed through narrow band filters. Typically three filters (such as red, green and blue) are used to provide tristimulus light values representative of the color of the surface. Yet another method is to illuminate an object with three monochromatic light sources (such as red, green and blue) one at a time and then measure the intensity of the reflected light with a single light sensor. The three measurements are then converted to a tristimulus value representative of the color of the surface. Such color measurement techniques can be utilized to produce equivalent tristimulus values representative of the color of the surface. Generally, it does not matter if a “white” light source is used with a plurality of color sensors (or a continuum in the case of a spectrophotometer), or if a plurality of colored light sources are utilized with a single light sensor.
There are, however, difficulties with the conventional techniques. When light is incident upon a surface and reflected to a light receiver, the height of the light sensor and the angle of the sensor relative to the surface and to the light source also affect the intensity of the received light. Since the color determination is being made by measuring and quantifying the intensity of the received light for different colors, it is important that the height and angular dependency of the light receiver be eliminated or accounted for in some manner.
One method for eliminating the height and angular dependency of the light source and receiver is to provide a fixed mounting arrangement where the light source and receiver are stationary and the object is always positioned and measured at a preset height and angle. The fixed mounting arrangement greatly limits the applicability of such a method. Another method is to add mounting feet to the light source and receiver probe and to touch the object with the probe to maintain a constant height and angle. The feet in such an apparatus must be wide enough apart to insure that a constant angle (usually perpendicular) is maintained relative to the object. Such an apparatus tends to be very difficult to utilize on small objects or on objects that are hard to reach, and in general does not work satisfactorily in measuring objects with curved surfaces. Such devices are particularly difficult to implement in the field of dentistry.
The use of color measuring devices in the field of dentistry has been proposed. In modern dentistry, the color of teeth typically are quantified by manually comparing a patient's teeth with a set of “shade guides.” There are numerous shade guides available for dentists in order to properly select the desired color of dental prosthesis. Such shade guides have been utilized for decades and the color determination is made subjectively by the dentist by holding a set of shade guides next to a patient's teeth and attempting to find the best match. Unfortunately, however, the best match often is affected by the ambient light color in the dental operatory and the surrounding color of the patient's makeup or clothing and by the fatigue level of the dentist. In addition, such pseudo trial and error methods based on subjective matching with existing industry shade guides for forming dental prostheses, fillings and the like often result in unacceptable color matching, with the result that the prosthesis needs to be remade, leading to increased costs and inconvenience to the patient, dental professional and/or prosthesis manufacturer.
Similar subjective color quantification also is made in the paint industry by comparing the color of an object with a paint reference guide. There are numerous paint guides available in the industry and the color determination also often is affected by ambient light color, user fatigue and the color sensitivity of the user. Many individuals are color insensitive (color blind) to certain colors, further complicating color determination.
While a need has been recognized in the field of dentistry, however, the limitations of conventional color/optical measuring techniques typically restrict the utility of such techniques. For example, the high cost and bulkiness of typical broad band spectrometers, and the fixed mounting arrangements or feet required to address the height and angular dependency, often limit the applicability of such conventional techniques.
Moreover, another limitation of such conventional methods and devices are that the resolution of the height and angular dependency problems typically require contact with the object being measured. In certain applications, it may be desirable to measure and quantify the color of an object with a small probe that does not require contact with the surface of the object. In certain applications, for example, hygienic considerations make such contact undesirable. In the other applications, contact with the object can mar the surface (such as if the object is coated in some manner) or otherwise cause undesirable effects.
In summary, there is a need for a low cost, hand-held probe of small size that can reliably measure and quantify the color and other optical characteristics of an object without requiring physical contact with the object, and also a need for methods based on such a device in the field of dentistry and other applications.
In accordance with the present invention, devices and methods are provided for measuring the color and other optical characteristics of objects such as teeth, reliably and with minimal problems of height and angular dependence. A handheld probe is utilized in the present invention, with the handheld probe containing a number of fiber optics in certain preferred embodiments. Light is directed from one (or more) light source(s) towards the object/tooth to be measured, which in certain preferred embodiments is a central light source fiber optic (other light sources and light source arrangements also may be utilized). Light reflected from the object is detected by a number of light receivers. Included in the light receivers (which may be light receiver fiber optics) are a plurality of perimeter receivers (which may be light receiver fiber optics, etc.). In certain preferred embodiments, three perimeter fiber optics are utilized in order to take measurements at a desired, and predetermined height and angle, thereby minimizing height and angular dependency problems found in conventional methods. In certain embodiments, the present invention also may measure translucence and fluorescence characteristics of the object/tooth being measured, as well as surface texture and/or other optical or surface characteristics.
The present invention may include constituent elements of a broad band spectrophotometer, or, alternatively, may include constituent elements of a tristimulus type colorimeter. The present invention may employ a variety of color measuring devices in order to measure color in a practical, reliable and efficient manner, and in certain preferred embodiments includes a color filter array and a plurality of color sensors. A microprocessor is included for control and calculation purposes. A temperature sensor is included to measure temperature in order to detect abnormal conditions and/or to compensate for temperature effects of the filters or other components of the system. In addition, the present invention may include audio feedback to guide the operator in making color/optical measurements, as well as one or more display devices for displaying control, status or other information.
With the present invention, color/optical measurements of teeth or the like may be made with a handheld probe in a practical and reliable manner, essentially free of height and angular dependency problems, without resorting to fixtures, feet or other undesirable mechanical arrangements for fixing the height and angle of the probe with respect to the object/tooth. In addition, the present invention includes methods of using such color measurement data to implement processes for forming dental prostheses and the like, as well as methods for keeping such color and/or other data as part of a patient record database.
Accordingly, it is an object of the present invention to address limitations of conventional color/optical measuring techniques.
It is another object of the present invention to provide a method and device useful in measuring the color or other optical characteristics of teeth or other objects or surfaces with a hand-held probe of practical size that does not require contact with the object or surface.
It is a further object of the present invention to provide a color/optical measurement probe and method that does not require fixed position mechanical mounting, feet or other mechanical impediments.
It is yet another object of the present invention to provide a probe and method useful for measuring color or other optical characteristics that may be utilized with a probe simply placed near the surface to be measured.
It is a still further object of the present invention to provide a probe and method that are capable of determining translucency characteristics of the object being measured.
It is a further object of the present invention to provide a probe and method that are capable of determining surface texture characteristics of the object/tooth being measured.
It is a still further object of the present invention to provide a probe and method that are capable of determining fluorescence characteristics of the object/tooth being measured.
It is another object of the present invention to provide a probe and method that can measure the area of a small spot singulary, or that also can measure the color of irregular shapes by moving the probe over an area and integrating the color of the entire area.
It is a further object of the present invention to provide a method of measuring the color of teeth and preparing dental prostheses, dentures, intraoral tooth-colored fillings or other materials.
It is yet another object of the present invention to provide a method and apparatus that minimizes contamination problems, while providing a reliable and expedient manner in which to measure teeth and prepare dental prostheses, dentures, intraoral tooth-colored fillings or other materials.
It is an object of the present invention to provide methods of using measured data to implement processes for forming dental prostheses and the like, as well as methods for keeping such measurement and/or other data as part of a patient record database.
It also is an object of the present invention to provide probes and methods for measuring optical characteristics with a probe that is held substantially stationary with respect to the object or tooth being measured.
Finally, it is an object of the present invention to provide probes and methods for measuring optical characteristics with a probe that may have a removable tip or shield that may be removed for cleaning, disposed after use or the like
The present invention may be more fully understood by a description of certain preferred embodiments in conjunction with the attached drawings in which:
The present invention will be described in greater detail with reference to certain preferred embodiments. At various places herein, reference is made to an “object,” for example. It should be understood that an exemplary use of the present invention is in the field of dentistry, and thus the object typically should be understood to include teeth, dentures, dental-type cements or the like, although for discussion purposes in certain instances reference is only made to the “object.” As described elsewhere herein, various refinements and substitutions of the various embodiments are possible based on the principles and teachings herein.
With reference to
Probe tip 1 encloses a plurality of fiber optics, each of which may constitute one or more fiber optic fibers. In a preferred embodiment, the fiber optics contained within probe tip 1 includes a single light source fiber optic and three light receiver fiber optics. The use of such fiber optics to measure the color or other optical characteristics of an object will be described later herein. Probe tip 1 is attached to probe body 2, on which is fixed switch 17. Switch 17 communicates with microprocessor 10 through wire 18 and provides, for example, a mechanism by which an operator may activate the device in order to make a color/optical measurement. Fiber optics within probe tip 1 terminate at the forward end thereof (i.e., the end away from probe body 2). The forward end of probe tip 1 is directed towards the surface of the object to be measured as described more fully below. The fiber optics within probe tip 1 optically extend through probe body 2 and through fiber optic cable 3 to light sensors 8, which are coupled to microprocessor 10.
It should be noted that microprocessor 10 includes conventional associated components, such as memory (programmable memory, such as PROM, EPROM or EEPROM; working memory such as DRAMs or SRAMs; and/or other types of memory such as non-volatile memory, such as FLASH), peripheral circuits, clocks and power supplies, although for clarity such components are not explicitly shown. Other types of computing devices (such as other microprocessor systems, programmable logic arrays or the like) are used in other embodiments of the present invention.
In the embodiment of
Light source 11 in the preferred embodiment is a halogen light source (of, for example, 5-100 watts, with the particular wattage chosen for the particular application), which may be under the control of microprocessor 10. The light from light source 11 reflects from cold mirror 6 and into source fiber optic 5. Source fiber optic 5 passes through to the forward end of probe tip 1 and provides the light stimulus used for purposes of making the measurements described herein. Cold mirror 6 reflects visible light and passes infra-red light, and is used to reduce the amount of infra-red light produced by light source 11 before the light is introduced into source fiber optic 5. Such infra-red light reduction of the light from a halogen source such as light source 11 can help prevent saturation of the receiving light sensors, which can reduce overall system sensitivity. Fiber 15 receives light directly from light source 11 and passes through to light sensors 8 (which may be through a neutral density filter). Microprocessor 10 monitors the light output of light source 11 through fiber 15, and thus may monitor and, if necessary compensate for, drift of the output of light source 11. In certain embodiments, microprocessor 10 also may sound an alarm (such as through speaker 16) or otherwise provide some indication if abnormal or other undesired performance of light source 11 is detected.
The data output from light sensors 8 pass to microprocessor 10. Microprocessor 10 processes the data from light sensors 8 to produce a measurement of color and/or other characteristics. Microprocessor 10 also is coupled to key pad switches 12, which serve as an input device. Through key pad switches 12, the operator may input control information or commands, or information relating to the object being measured or the like. In general, key pad switches 12, or other suitable data input devices (such as push button, toggle, membrane or other switches or the like), serve as a mechanism to input desired information to microprocessor 10.
Microprocessor 10 also communicates with UART 13, which enables microprocessor 10 to be coupled to an external device such as computer 13A. In such embodiments, data provided by microprocessor 10 may be processed as desired for the particular application, such as for averaging, format conversion or for various display or print options, etc. In the preferred embodiment, UART 13 is configured so as to provide what is known as a RS232 interface, such as is commonly found in personal computers.
Microprocessor 10 also communicates with LCD 14 for purposes of displaying status, control or other information as desired for the particular application. For example, color bars, charts or other graphic representations of the color or other collected data and/or the measured object or tooth may be displayed. In other embodiments, other display devices are used, such as CRTs, matrix-type LEDs, lights or other mechanisms for producing a visible indicia of system status or the like. Upon system initialization, for example, LCD 14 may provide an indication that the system is stable, ready and available for taking color measurements.
Also coupled to microprocessor 10 is speaker 16. Speaker 16, in a preferred embodiment as discussed more fully below, serves to provide audio feedback to the operator, which may serve to guide the operator in the use of the device. Speaker 16 also may serve to provide status or other information alerting the operator of the condition of the system, including an audio tone, beeps or other audible indication (i.e., voice) that the system is initialized and available for taking measurements. Speaker 16 also may present audio information indicative of the measured data, shade guide or reference values corresponding to the measured data, or an indication of the status of the color/optical measurements.
Microprocessor 10 also receives an input from temperature sensor 9. Given that many types of filters (and perhaps light sources or other components) may operate reliably only in a given temperature range, temperature sensor 9 serves to provide temperature information to microprocessor 10. In particular, color filters, such as may be included in light sensors 8, may be sensitive to temperature, and may operate reliably only over a certain temperature range. In certain embodiments, if the temperature is within a usable range, microprocessor 10 may compensate for temperature variations of the color filters. In such embodiments, the color filters are characterized as to filtering characteristics as a function of temperature, either by data provided by the filter manufacturer, or through measurement as a function of temperature. Such filter temperature compensation data may be stored in the form of a look-up table in memory, or may be stored as a set of polynomial coefficients from which the temperature characteristics of the filters may be computed by microprocessor 10.
In general, under control of microprocessor 10, which may be in response to operator activation (through, for example, key pad switches 12 or switch 17), light is directed from light source 11, and reflected from cold mirror 6 through source fiber optic 5 (and through fiber optic cable 3, probe body 2 and probe tip 1) or through some other suitable light source element and is directed onto object 20. Light reflected from object 20 passes through the receiver fiber optics/elements in probe tip 1 to light sensors 8 (through probe body 2, fiber optic cable 3 and fibers 7). Based on the information produced by light sensors 8, microprocessor 10 produces a color/optical measurement result or other information to the operator. Color measurement or other data produced by microprocessor 10 may be displayed on display 14, passed through UART 13 to computer 13A, or used to generate audio information that is presented to speaker 16. Other operational aspects of the preferred embodiment illustrated in
With reference to
In the illustrated preferred embodiment, receiver fiber optics R1 to R3 are positioned symmetrically around source fiber optic S, with a spacing of about 120 degrees from each other. It should be noted that spacing t is provided between receiver fiber optics R1 to R3 and source fiber optic S. While the precise angular placement of the receiver fiber optics around the perimeter of the fiber bundle in general is not critical, it has been determined that three receiver fiber optics positioned 120 degrees apart generally may give acceptable results. As discussed above, in certain embodiments light receiver fiber optics R1 to R3 each constitute a single fiber, which is divided at splicing connector 4 (refer again to
In one particular aspect of the present invention, area between the fiber optics on probe tip 1 may be wholly or partially filled with a non-reflective material and/or surface (which may be a black mat, contoured or other non-reflective surface). Having such exposed area of probe tip 1 non-reflective helps to reduce undesired reflections, thereby helping to increase the accuracy and reliability of the present invention.
With reference to
Light from fibers 7 is presented to sensors 8, which in a preferred embodiment pass through filters 22 to sensing elements 24. In this preferred embodiment, sensing elements 24 include light-to-frequency converters, manufactured by Texas Instruments and sold under the part number TSL230. Such converters constitute, in general, photo diode arrays that integrate the light received from fibers 7 and output an AC signal with a frequency proportional to the intensity (not frequency) of the incident light. Without being bound by theory, the basic principle of such devices is that, as the intensity increases, the integrator output voltage rises more quickly, and the shorter the integrator rise time, the greater the output frequency. The outputs of the TSL230 sensors are TTL or CMOS compatible digital signals, which may be coupled to various digital logic devices.
The outputs of sensing elements 24 are, in this embodiment, asynchronous signals of frequencies depending upon the light intensity presented to the particular sensing elements, which are presented to processor 26. In a preferred embodiment, processor 26 is a Microchip PIC16C55 or PIC16C57 microprocessor, which as described more fully herein implements an algorithm to measure the frequencies of the signals output by sensing elements 24. In other embodiments, a more integrated microprocessor/microcontroller, such as Hitachi's SH RISC microcontrollers, is utilized to provide further system integration or the like.
As previously described, processor 26 measures the frequencies of the signals output from sensing elements 24. In a preferred embodiment, processor 26 implements a software timing loop, and at periodic intervals processor 26 reads the states of the outputs of sensing elements 24. An internal counter is incremented each pass through the software timing loop. The accuracy of the timing loop generally is determined by the crystal oscillator time base (not shown in
It should be noted that the sensing circuitry and methodology illustrated in
As discussed above with reference to
The remaining twelve fibers (of the preferred embodiment's total of 16 fibers) of fibers 7 pass through color filters and are used to produce the color measurement. In a preferred embodiment, the color filters are Kodak Sharp Cutting Wratten Gelatin Filters, which pass light with wavelengths greater than the cut-off value of the filter (i.e., redish values), and absorb light with wavelengths less than the cut-off value of the filter (i.e., bluish values). “Sharp Cutting” filters are available in a wide variety of cut-off frequencies/wavelengths, and the cut-off values generally may be selected by proper selection of the desired cut-off filter. In a preferred embodiment, the filter cut-off values are chosen to cover the entire visible spectrum and, in general, to have band spacings of approximately the visible band range (or other desired range) divided by the number of receivers/filters. As an example, 700 nanometers minus 400 nanometers, divided by 11 bands (produced by twelve color receivers/sensors), is roughly 30 nanometer band spacing.
With an array of cut-off filters as described above, and without being bound by theory or the specific embodiments described herein, the received optical spectrum may be measured/calculated by subtracting the light intensities of “adjacent” color receivers. For example, band 1 (400 nm to 430 nm)=(intensity of receiver 12) minus (intensity of receiver 11), and so on for the remaining bands. Such an array of cut-off filters, and the intensity values that may result from filtering with such an array, are more fully described in connection with
It should be noted here that in alternate embodiments other color filter arrangements are utilized. For example, “notch” or bandpass filters may be utilized, such as may be developed using Schott glass-type filters (whether constructed from separate longpass/shortpass filters or otherwise).
In a preferred embodiment of the present invention, the specific characteristics of the light source, filters, sensors and fiber optics, etc., are normalized/calibrated by directing the probe towards, and measuring, a known color standard. Such normalization/calibration may be performed by placing the probe in a suitable fixture, with the probe directed from a predetermined position (i.e., height and angle) from the known color standard. Such measured normalization/calibration data may be stored, for example, in a look-up table, and used by microprocessor 10 to normalize or correct measured color or other data. Such procedures may be conducted at start-up, at regular periodic intervals, or by operator command, etc.
What should be noted from the above description is that the receiving and sensing fiber optics and circuitry illustrated in
It also should be noted that such a system measures the spectral band of the reflected light from the object, and once measured such spectral data may be utilized in a variety of ways. For example, such spectral data may be displayed directly as intensity-wavelength band values. In addition, tristimulus type values may be readily computed (through, for example, conventional matrix math), as may any other desired color values. In one particular embodiment useful in dental applications (such as for dental prostheses), the color data is output in the form of a closest match or matches of dental shade guide value(s). In a preferred embodiment, various existing shade guides (such as the shade guides produced by Vita Zahnfabrik) are characterized and stored in a look-up table, or in the graphics art industry Pantone color references, and the color measurement data are used to select the closest shade guide value or values, which may be accompanied by a confidence level or other suitable factor indicating the degree of closeness of the match or matches, including, for example, what are known as ΔE values or ranges of ΔE values, or criteria based on standard deviations, such as standard deviation minimization. In still other embodiments, the color measurement data are used (such as with look-up tables) to select materials for the composition of paint or ceramics such as for prosthetic teeth. There are many other uses of such spectral data measured in accordance with the present invention.
It is known that certain objects such as human teeth may fluoresce, and such optical characteristics also may be measured in accordance with the present invention. A light source with an ultraviolet component may be used to produce more accurate color/optical data with respect to such objects. In certain embodiments, a tungsten/halogen source (such as used in a preferred embodiment) may be combined with a UV light source (such as a mercury vapor, xenon or other fluorescent light source, etc.) to produce a light output capable of causing the object to fluoresce. Alternately, a separate UV light source, combined with a visible-light-blocking filter, may be used to illuminate the object. Such a UV light source may be combined with light from a red LED (for example) in order to provide a visual indication of when the UV light is on and also to serve as an aid for the directional positioning of the probe operating with such a light source. A second measurement may be taken using the UV light source in a manner analogous to that described earlier, with the band of the red LED or other supplemental light source being ignored. The second measurement may thus be used to produce an indication of the fluorescence of the tooth or other object being measured. With such a UV light source, a silica fiber optic (or other suitable material) typically would be required to transmit the light to the object (standard fiber optic materials such as glass and plastic in general do not propagate UV light in a desired manner, etc.).
As described earlier, in certain preferred embodiments the present invention utilizes a plurality of perimeter receiver fiber optics spaced apart from and around a central source fiber optic to measure color and determine information regarding the height and angle of the probe with respect to the surface of the object being measured, which may include other surface characteristic information, etc. Without being bound by theory, certain principles underlying this aspect of the present invention will now be described with reference to
In order to propagate light without loss, the light must be incident within the core of the fiber optic at an angle greater than the critical angle, which may be represented as Sin−1{n1/n0}, where n0 is the index of refraction of the core and n1 is the index of refraction of the cladding. Thus, all light must enter the fiber at an acceptance angle equal to or less than phi, with phi=2×Sin−{√(n02−n12)}, or it will not be propagated in a desired manner.
For light entering a fiber optic, it must enter within the acceptance angle phi. Similarly, when the light exits a fiber optic, it will exit the fiber optic within a cone of angle phi as illustrated in
Consider using a fiber optic as a light source. One end is illuminated by a light source (such as light source 11 of
The same principle generally is true for a fiber optic being utilized as a receiver. Consider mounting a light sensor on one end of a fiber optic and holding the other end near an illuminated surface. The fiber optic can only propagate light without loss when the light entering the fiber optic is incident on the end of the fiber optic near the surface if the light enters the fiber optic within its acceptance angle phi. A fiber optic utilized as a light receiver near a surface will only accept and propagate light from the circular area of radius r on the surface. As the fiber optic is raised from the surface, the area increases. As the fiber optic is lowered to the surface, the area decreases.
Consider two fiber optics parallel to each other as illustrated in
As discussed earlier, the intensity of the light in the circular area illuminated by the source fiber increases as the fiber is lowered to the surface. The intersection of the two cones, however, decreases as the fiber optic pair is lowered. Thus, as the fiber optic pair is lowered to a surface, the total intensity of light received by the receiver fiber optic increases to a maximal value, and then decreases sharply as the fiber optic pair is lowered still further to the surface. Eventually, the intensity will decrease essentially to zero (assuming the object being measured is not translucent, as described more fully herein), and will remain essentially zero until the fiber optic pair is in contact with the surface. Thus, as a source-receiver pair of fiber optics as described above are positioned near a surface and as their height is varied, the intensity of light received by the receiver fiber optic reaches a maximal value at a peaking or “critical height” hc.
Again without being bound by theory, an interesting property of the critical height hc has been observed. The critical height hc is a function primarily of the geometry of fixed parameters, such as fiber apertures, fiber diameters and fiber spacing. Since the receiver fiber optic in the illustrated arrangement is only detecting a maximum value and not attempting to quantify the value, its maximum in general is independent of the surface characteristics. It is only necessary that the surface reflect sufficient light from the intersecting area of the source and receiver fiber optics to be within the detection range of the receiver fiber optic light sensor. Thus, in general red or green or blue or any color surface will all exhibit a maximum at the same critical height hc. Similarly, smooth reflecting surfaces and rough surfaces also will have varying intensity values at the maximal value, but generally speaking all such surfaces will exhibit a maximum at the same critical height hc. The actual value of the light intensity will be a function of the color of the surface and of the surface characteristics, but the height where the maximum intensity value occurs in general will not. This is particularly true with respect to similar types or categories of materials, such as teeth, industrial objects, etc.
Although the above discussion has focused on two fiber optics perpendicular to a surface, similar analysis is applicable for fiber optic pairs at other angles. When a fiber optic is not perpendicular to a surface, it generally illuminates an elliptical area. Similarly, the acceptance area of a receiver fiber optic generally becomes elliptical. As the fiber optic pair is moved closer to the surface, the receiver fiber optic also will detect a maximal value at a critical height independent of the surface color or characteristics. The maximal intensity value measured when the fiber optic pair is not perpendicular to the surface, however, will be less than the maximal intensity value measured when the fiber optic pair is perpendicular to the surface.
Referring now to
As illustrated, two peak intensity values (discussed as P1 and P2 below) should be detected as the fiber optic pair moves to and from the object at the critical height hc. If peaks P1 and P2 produced by a receiver fiber optic are the same value, this generally is an indication that the probe has been moved to and from the surface of the object to be measured in a consistent manner. If peaks P1 and P2 are of different values, then these may be an indication that the probe was not moved to and from the surface of the object in a desired manner, or that the surface is curved or textured, as described more fully herein. In such a case, the data may be considered suspect and rejected. In addition, peaks P1 and P2 for each of the perimeter fiber optics (see, e.g.,
In addition, the relative intensity level in region 3 serves as an indication of the level of translucency of the object being measured. Again, such principles generally are applicable to the totality of receiver fiber optics in the probe (see, e.g., fibers 7 of
In step 50, the system on a continuing basis monitors the intensity levels for the receiver fiber optics (see, e.g., fibers 7 of
In step 64, the system, under control of microprocessor 10, may analyze the collected data taken by the sensing circuitry for the various receiver fiber optics. In step 64, peaks P1 and P2 of one or more of the various fiber optics may be compared. If any of peaks P1 and P2 for any of the various receiver fiber optics have unequal peak values, then the data may be rejected, and the entire color measuring process repeated. Again, unequal values of peaks P1 and P2 may be indicative, for example, that the probe was moved in a non-perpendicular or otherwise unstable manner (i.e., angular or lateral movement), and, for example, peak P1 may be representative of a first point on the object, while peak P2 may be representative of a second point on the object. As the data is suspect, in a preferred embodiment of the present invention, data taken in such circumstances are rejected in step 64.
If the data are not rejected in step 64, the process proceeds to step 66. In step 66, the system analyzes the data taken from the neutral-density-filtered receivers from each of the perimeter fiber optics (e.g., R1 to R3 of
If the data are not rejected in step 66, the process proceeds to step 68. In step 68, the color data may be processed in a desired manner to produce output color/optical measurement data. For example, such data may be normalized in some manner, or adjusted based on temperature compensation or other data detected by the system. The data also may be converted to different display or other formats, depending on the intended use of the data. In addition, the data indicative of the translucence of the object also may be quantified and/or displayed in step 68. After step 68, the process may proceed to starting step 49, or the process may be terminated, etc.
In accordance with the process illustrated in
With a system constructed and operating as described above, color/optical measurements may be taken of an object, with accepted data having height and angular dependencies removed. Data not taken at the critical height, or data not taken with the probe perpendicular to the surface of the object being measured, etc., are rejected in a preferred embodiment of the present invention. In other embodiments, data received from the perimeter fiber optics may be used to calculate the angle of the probe with respect to the surface of the object being measured, and in such embodiments non-perpendicular or curved surface data may be compensated instead of rejected. It also should be noted that peak values P1 and P2 for the neutral density perimeter fiber optics provide a measure of the luminance (gray value) of the surface of the object being measured, and also may serve to quantify the color value.
The translucency of the object being measured may be quantified as a ratio or percentage, such as, for example, (IS/P1)×100%. In other embodiments, other methods of quantifying translucency data provided in accordance with the present invention are utilized, such as some other arithmetic function utilizing IS and P1 or P2, etc.
In another particular aspect of the present invention, data generated in accordance with the present invention may be used to implement an automated material mixing/generation machine. Certain objects/materials, such as dental prostheses, are made from porcelain or other powders/materials that may be combined in the correct ratios to form the desired color of the object/prosthesis. Certain powders often contain pigments that generally obey Beer's law and/or act in accordance with Kubelka-Munk equations and/or Saunderson equations (if needed) when mixed in a recipe. Color and other data taken from a measurement in accordance with the present invention may be used to determine or predict desired quantities of pigment or other materials for the recipe. Porcelain powders and other materials are available in different colors, opacities, etc. Certain objects, such as dental prostheses, may be layered to simulate the degree of translucency of the desired object (such as to simulate a human tooth). Data generated in accordance with the present invention also may be used to determine the thickness and position of the porcelain or other material layers to more closely produce the desired color, translucency, surface characteristics, etc. In addition, based on fluorescence data for the desired object, the material recipe may be adjusted to include a desired quantity of fluorescing-type material. In yet other embodiments, surface characteristics (such as texture) information (as more fully described herein) may be used to add a texturing material to the recipe, all of which may be carried out in accordance with the present invention.
For more information regarding such pigment-material recipe type technology, reference may be made to: “The Measurement of Appearance,” Second Edition, edited by Hunter and Harold, copyright 1987; “Principles of Color Technology,” by Billmeyer and Saltzman, copyright 1981; and “Pigment Handbook,” edited by Lewis, copyright 1988. All of the foregoing are believed to have been published by John Wiley & Sons, Inc., New York, N.Y., and all of which are hereby incorporated by reference.
In certain operative environments, such as dental applications, contamination of the probe is of concern. In certain embodiments of the present invention, implements to reduce such contamination are provided.
The thickness of the sapphire window should be less than the critical height of the probe in order to preserve the ability to detect peaking in accordance with the present invention, and preferably has a thickness less than the minimal height at which the source/receiver cones overlap (see
Similarly, in other embodiments body 80 has a cap with a hole in the center (as opposed to a sapphire window), with the hole positioned over the fiber optic source/receivers The cap with the hole serves to prevent the probe from coming into contact with the surface, thereby reducing the risk of contamination. It should be noted that, with such embodiments, the hole is positioned so that the light from/to the light source/receiver elements of the probe tip is not adversely affected by the cap.
In still other embodiments, a plastic, paper or other type shield (which may be disposable, cleanable/reusable or the like) may be used in order to address any contamination concerns that may exist in the particular application. In such embodiments, the methodology may include positioning such a shield over the probe tip prior to taking color/optical measurements, and may include removing and disposing/cleaning the shield after taking color/optical measurements, etc.
With reference to
Probe tip 100 includes central source fiber optic 106, surrounded by (and spaced apart from) three perimeter receiver fiber optics 104 and three color receiver fiber optics 102. Three perimeter receiver fiber optics 104 are optically coupled to neutral density filters and serve as height/angle sensors in a manner analogous to the embodiment describe above. Three color receiver fiber optics are optically coupled to suitable tristimulus filters, such as red, green and blue filters. With this embodiment, a measurement may be made of tristimulus color values of the object, and the process described with reference to
The plurality of receiver fiber optics are each coupled to two or more fiber optics in a manner similar to the arrangement illustrated in
Since a probe as illustrated in
In general, with the embodiment of
In general, with the embodiment of
As will be clear from the foregoing description, with the present invention a variety of types of spectral color/optical photometers (or tristimulus-type colorimeters) may be constructed, with perimeter receiver fiber optics used to collect color/optical data essentially free from height and angular deviations. In addition, in certain embodiments, the present invention enables color/optical measurements to be taken at a critical height from the surface of the object being measured, and thus color/optical data may be taken without physical contact with the object being measured (in such embodiments, the color/optical data is taken only by passing the probe through region 1 and into region 2, but without necessarily going into region 3 of
Additional description will now be provided with respect to cut-off filters of the type described in connection with the preferred embodiment(s) of
Reference should be made to the
The operator may initiate a color/optical measurement by activation of a switch (such as switch 17 of
With unique audio tones presented to an operator in accordance with the particular operating state of the system, the operator's use of the system may be greatly facilitated. Such audio information also tends to increase operator satisfaction and skill level, as, for example, acceptance tones provide positive and encouraging feedback when the system is operated in a desired manner.
The color/optical measuring systems and methods in accordance with the present invention may be applied to particular advantage in the field of dentistry, as will be more fully explained hereinafter. In particular the present invention includes the use of such systems and methods to measure the color and other attributes of a tooth in order to prepare a dental prosthesis or intraoral tooth-colored fillings, or to select denture teeth or to determine a suitable cement color for porcelain/resin prostheses. The present invention also provides methods for storing and organizing measured data such as in the form of a patient database.
At step 202, the patient and the tooth to be measured are prepared. Any required cleaning or other tooth preparation would be performed at step 202. Any required patient consultation about the type of prosthesis or area of a tooth to be matched would be performed at (or before) step 202. In certain embodiments, a positioning device is prepared at step 202, such as is illustrated in
At step 204, the operator (typically a dentist or other dental professional) moves the probe towards the area of the tooth to be measured. This process preferably is conducted in accordance with the methodology described with reference to
Upon successful completion of one or more measurements taken at step 204, the process proceeds to step 206. At step 206, any data conversion or processing of data collected at step 204 may be performed. For example, in the embodiment of
At step 208, a matching is optionally attempted between the data produced at steps 204 and 206 (if performed) and a desired color (in other embodiments, the process may proceed from 204 directly to 210, or alternatively steps 206 and 208 may be combined). For example, a number of “shade guides” are available in the market, some of which are known in the industry as Vita shade guides, Bioform shade guides or other color matching standards, guides or references or custom shade guides. In certain preferred embodiments, a lookup table is prepared and loaded into memory (such as memory associated with microprocessor 10 or computer 13A of
In a particular aspect of certain embodiments of the present invention, at step 208 a material correlation lookup table is accessed. Based on the color and translucency data obtained at step 204, a proposed recipe of materials, pigments or other instruction information is prepared for a prosthesis or filling, etc., of the desired color and translucency, etc. With the detailed color and other information made available in accordance with the present invention, a direct correlation with the relevant constituent materials may be made. In still other embodiments, such information is made available to an automated mixing or manufacturing machine for preparation of prosthesis or material of the desired color and translucency, etc., as more fully described elsewhere herein.
At step 210, based on the results of the preceding steps, the prosthesis, denture, intraoral tooth-colored filling material or other items are prepared. This step may be performed at a dental lab, or, in certain embodiments, at or near the dental operatory. For remote preparation, relevant data produced at steps 204, 206 and/or 208 may be sent to the remote lab or facility by hardcopy, facsimile or modem or other transmission. What should be understood from the foregoing is that, based on data collected at step 204, a prosthesis may be prepared of a desirable color and/or other optical characteristic at step 210.
At step 212, the prosthesis or other material prepared at step 210 may be measured for confirmation purposes, again preferably conducted in accordance with the methodology described with reference to
In another particular aspect of the present invention, for example, data processing such as illustrated in
At step 288, for example, the dentist or other dental professional may select parameters for a particular tooth of the patient to be measured. Depending on the size and condition of the tooth (such as color gradient or the like), the dentist may sector the tooth into one or more regions, such as a grid. Thus, for example, in the case of tooth for which it is decided to take four measurements, the tooth may be sectored into four regions. Such parameters, which may include a pictorial representation on the computer of the tooth sectored into four regions (such as by grid lines), along with tooth identification and patient information may be entered into the computer at this time.
At step 290, one or more measurements of the tooth may be taken, such as with a system and method as described in connection with
In yet another particular aspect of the present invention, a measuring device and method (such as described elsewhere herein) may be combined with an intraoral camera and other implements. As illustrated in
Further embodiments of the present invention will now be described with reference to
With this embodiment, a relatively greater number of perimeter sensors are utilized (as opposed, for example, to the three perimeter sensors used in certain preferred embodiments of the present invention). As illustrated in
The probe illustrated in
As described earlier, the light receiver elements for the plurality of receivers/perimeter sensors may be individual elements such as Texas Instruments TSL230 light-to-frequency converters, or may be constructed with rectangular array elements or the like such as may be found in a CCD camera. Other broadband-type of light measuring elements are utilized in other embodiments. Given the large number of perimeter sensors used in such embodiments (such as 30 for the embodiment of
Optical measurements may be made with such a probe by holding/positioning the probe near the surface of the object being measured (i.e., within the range of acceptable heights of the particular probe). The light source providing light to light source 310 is turned on and the reflected light received by receivers 312-320 (coupled to the perimeter sensors) is measured. The light intensity of the rings of triad sensors is compared. Generally, if the probe is perpendicular to the surface and if the surface is flat, the light intensity of the three sensors of each triad should be approximately will be equal. If the probe is not perpendicular to the surface or if the surface is not flat, the light intensity of the three sensors within a triad will not be equal. It is thus possible to determine if the probe is perpendicular to the surface being measured, etc. It also is possible to compensate for non-perpendicular surfaces by mathematically adjusting the light intensity measurements of the color sensors with the variance in measurements of the triads of perimeters sensors.
Since the three sensors forming triads of sensors are at different distances (radii) from central light source 310, it is expected that the light intensities measured by light receivers 312-320 and the perimeter sensors will vary. For any given triad of sensors, as the probe is moved closer to the surface, the received light intensity will increase to a maximum and then sharply decrease as the probe is moved closer to the surface. As with previously-described embodiments, the intensity decreases rapidly as the probe is moved less than the critical height and decreases rapidly to zero or almost zero for opaque objects. The value of the critical height depends principally upon the distance of the particular receiver from light source 310. Thus, the triads of sensors will peak at different critical heights. By analyzing the variation in light values received by the triads of sensors, the height of the probe can be determined. Again, this is particularly true when measuring similar types of materials.
The system initially is calibrated against a neutral background (e.g., a gray background), and the calibration values are stored in non-volatile memory (see, e.g., processor 10 of
To determine a measure of the height of the probe from the surface being measured, the intensities of the perimeter sensors (coupled to receivers 312-320) is measured. The variance in light intensity from the inner ring of perimeter sensors to the next ring and so on is analyzed and compared to the values in the look-up table to determine the height of the probe. The determined height of the probe with respect to the surface thus may be utilized by the system processor to compensate for the light intensities measured by the color sensors in order to obtain reflectivity readings that are in general independent of height. As with previously described embodiments, the reflectivity measurements may then be used to determine optical characteristics of the object being measured, etc.
It should be noted that audio tones, such as previously described, may be advantageously employed when such an embodiment is used in a handheld configuration. For example, audio tones of varying pulses, frequencies and/or intensities may be employed to indicate the operational status of the instrument, when the instrument is positioned within an acceptable range for color measurements, when valid or invalid color measurements have been taken, etc. In general, audio tones as previously described may be adapted for advantageous use with such further embodiments.
In the embodiment of
The probe is held within the useful range of the instrument (determined by the particular configuration and construction, etc.), and a color measurement is initiated. The angle of the perimeter receivers/sensors with respect to the central light source is varied from parallel to pointing towards the central source fiber optic. While the angle is being varied, the intensities of the light sensors for the perimeter sensors (e.g., neutral sensors) and the color sensors is measured and saved along with the angle of the sensors at the time of the light measurement. The light intensities are measured over a range of angles. As the angle is increased the light intensity will increase to a maximum value and will then decrease as the angle is further increased. The angle where the light values is a maximum is utilized to determine the height of the probe from the surface. As will be apparent to those skilled in the art based on the teachings provided herein, with suitable calibration data, simple geometry may be utilized to calculate the height based on the data measured during variation of the angle. The height measurement may then be utilized to compensate for the intensity of the color/optical measurements and/or utilized to normalize color values, etc.
A further embodiment of the present invention utilizing an alternate removable probe tip will now be described with reference to
Light conduit 340 in this embodiment serves to conduct light from the light source to the surface of the object being measured, and also to receive reflected light from the surface and conduct it to light receiver fiber optics 346 in probe handle 344. Light conduit 340 is held in position with respect to fiber optics 346 by way or compression jaws 342 or other suitable fitting or coupled that reliably positions light conduit 340 so as to couple light effectively to/from fiber optics 346. Fiber optics 346 may be separated into separate fibers/light conduits 348, which may be coupled to appropriate light sensors, etc., as with previously described embodiments.
In general, the aperture of the fiber optics used in light conduit 340 may be chosen to match the aperture of the fiber optics for the light source and the light receivers. Thus, the central part of the light conduit may conduct light from the light source and illuminate the surface as if it constituted a single fiber within a bundle of fibers. Similarly, the outer portion of the light conduit may receive reflected light and conduct it to light receiver fiber optics as if it constituted single fibers. Light conduit 340 has ends that preferably are highly polished and cut perpendicular, particularly the end coupling light to fiber optics 346. Similarly, the end of fiber optics 346 abutting light conduit 340 also is highly polished and cut perpendicular to a high degree of accuracy in order to minimize light reflection and cross talk between the light source fiber optic and the light receiver fiber optics and between adjacent receiver fiber optics. Light conduit 340 offers significant advantages including in the manufacture and installation of such a removable tip. For example, the probe tip need not be particularly aligned with the probe tip holder; rather, it only needs to be held against the probe tip holder such as with a compression mechanism (such as with compression jaws 342) so as to couple light effectively to/from fiber optics 346. Thus, such a removable tip mechanism may be implemented without alignment tabs or the like, thereby facilitating easy installation of the removable probe tip. Such an easy installable probe tip may thus be removed and cleaned prior to installation, thereby facilitating use of the color/optical measuring apparatus by dentists, medical professions or others working in an environment in which contamination may be a concern. Light conduit 340 also may be implemented, for example, as a small section of light conduit, which may facilitate easy and low cost mass production and the like.
A further embodiment of such a light conduit probe tip is illustrated as light conduit 352 in
Light conduit 352 of
As should be apparent to those skilled in the art in view of the disclosures herein, light conduits 340 and 356 of
Referring now to
Intraoral reflectometer 380, which may be constructed as described above, includes probe 381. Data output from reflectometer 380 is coupled to computer 384 over bus 390 (which may be a standard serial or parallel bus, etc.). Computer 384 includes a video freeze frame capability and preferably a modem. Intraoral camera 382 includes handpiece 383 and couples video data to computer 384 over bus 392. Computer 384 is coupled to remote computer 386 over telecommunication channel 388, which may be a standard telephone line, ISDN line, a LAN or WAN connection, etc. With such an embodiment, video measurements may be taken of one or more teeth by intraoral camera 382, along with optical measurements taken by intraoral reflectometer 380. Computer 384 may store still picture images taken from the output of intraoral camera 382.
Teeth are known to have variations in color from tooth to tooth, and teeth are known to have variations in color over the area of one tooth. Intraoral cameras are known to be useful for showing the details of teeth. Intraoral cameras, however, in general have poor color reproducability. This is due to variations in the camera sensing elements (from camera to camera and over time etc.), in computer monitors, printers, etc. As a result of such variations, it presently is not possible to accurately quantify the color of a tooth with an intraoral camera. With the present embodiment, measuring and quantifying the color or other optical properties of teeth may be simplified through the use of an intraoral reflectometer in accordance with the present invention, along with an intraoral camera.
In accordance with this embodiment, the dentist may capture a still picture of a tooth and its adjacent teeth using the freeze frame feature of computer 384. Computer 384, under appropriate software and operator control, may then “postureize” the image of the tooth and its adjacent teeth, such as by limiting the number of gray levels of the luminance signal, which can result in a color image that shows contours of adjacent color boundaries. As illustrated in
With teeth postureized as illustrated in
Computer 384 may then assess if the measured value of a particular color region is consistent with color measurements for adjacent color regions. If, for example, a color/optical measurement for one region indicates a darker region as compared to an adjacent region, but the postureized image indicates that the reverse should be true, then computer 384 may notify the dentist (such as with an audio tone) that one or more regions should be re-measured with intraoral reflectometer 380. Computer 384 may make such relative color determinations (even though the color values stored in computer 384 from the freeze frame process are not true color values) because the variations from region to region should follow the same pattern as the color/optical measurements taken by intraoral reflectometer 380. Thus, if one region is darker than its neighbors, then computer 384 will expect that the color measurement data from intraoral reflectometer 380 for the one region also will be darker relative to color measurement data for the neighboring regions, etc.
As with the color measurement data and captured images discussed previously, the postureized image of the teeth, along with the color/optical measurement data for the various regions of the teeth, may be conveniently stored, maintained and accessed as part of the patient dental records. Such stored data may be utilized advantageously in creating dental prosthesis that more correctly match the colors/regions of adjacent teeth.
In a further refinement to the foregoing embodiment, computer 384 preferably has included therein, or coupled thereto, a modem. With such a modem capability (which may be hardware or software), computer 384 may couple data to remote computer 386 over telecommunication channel 388. For example, remote computer 386 may be located at a dental laboratory remotely located. Video images captured using intraoral camera 382 and color/optical data collected using intraoral reflectometer may be transmitted to a dental technician (for example) at the remote location, who may use such images and data to construct dental prosthesis. Additionally, computer 384 and remote computer 386 may be equipped with an internal or external video teleconference capability, thereby enabling a dentist and a dental technician or ceramist, etc., to have a live video or audio teleconference while viewing such images and/or data.
For example, a live teleconference could take place, whereby the dental technician or ceramist views video images captured using intraoral camera 383, and after viewing images of the patient's teeth and facial features and complexion, etc., instruct the dentist as to which areas of the patient's teeth are recommended for measurement using intraoral reflectometer 380. Such interaction between the dentist and dental technician or ceramist may occur with or without postureization as previously described. Such interaction may be especially desirable at, for example, a try-in phase of a dental prosthesis, when minor changes or subtle characterizations may be needed in order to modify the prosthesis for optimum esthetic results.
A still further refinement may be understood with reference to
As an additional example, such a color calibration chart may be utilized by computer 384 and/or 386 to “calibrate” the color data within a captured image to true or known color values. For example, color calibration chart 404 may include one or more orientation markings 406, which may enable computers 384 and/or 386 to find and position color calibration chart 404 within a video frame. Thereafter, computers 384 and/or 386 may then compare “known” color data values from color calibration chart (data indicative of the colors within color calibration chart 404 and their position relative to orientation mark or markings 406 are stored within computers 384 and/or 386, such as in a lookup table, etc.) with the colors captured within the video image at positions corresponding to the various colors of color calibration chart 404. Based on such comparisons, computers 384 and/or 386 may color adjust the video image in order to bring about a closer correspondence between the colors of the video image and known or true colors from color calibration chart 404.
In certain embodiments, such color adjusted video data may be used in the prosthesis preparation process, such as to color adjust the video image (whether or not postureized) in conjunction with color/optical data collected using intraoral reflectometer 380 (for example, as described above or using data from intraoral reflectometer 380 to further color adjust portions of the video image), or to add subtle characterizations or modifications to a dental prosthesis, or to even prepare a dental prosthesis, etc. While not believed to be as accurate, etc. as color/optical data collected using intraoral reflectometer 380, such color adjusted video data may be adequate in certain applications, environments, situations, etc., and such color adjusted video data may be utilized in a similar manner to color data taken by a device such as intraoral reflectometer 380, including, for example, prosthesis preparation, patient data collection and storage, materials preparation, such as described elsewhere herein.
It should be further noted that color calibration chart 404 may be specifically adapted (size, form and constituent materials, etc.) to be positioned inside of the patient's mouth to be placed near the tooth or teeth being examined, so as to be subject to the same or nearly the same ambient lighting and environmental conditions, etc., as is the tooth or teeth being examined. It also should further be noted that the utilization of color calibration chart 404 to color correct video image data with a computer as provided herein also may be adapted to be used in other fields, such as medical, industrial, etc., although its novel and advantageous use in the field of dentistry as described herein is of particular note and emphasis herein.
Additionally, and to emphasize the wide utility and variability of various of the inventive concepts and techniques disclosed herein, it should be apparent to those skilled in the art in view of the disclosures herein that the apparatus and methodology may be utilized to measure the optical properties of objects/teeth using other optical focusing and gathering elements, in addition to the fiber optics employed in preferred embodiments herein. For example, lenses or mirrors or other optical elements may also be utilized to construct both the light source element and the light receiver element. A flashlight or other commonly available light source, as particular examples, may be utilized as the light source element, and a common telescope with a photoreceiver may be utilized as the receiver element in a large scale embodiment of the invention. Such refinements utilizing teachings provided herein are expressly within the scope of the present invention.
As will be apparent to those skilled in the art, certain refinements may be made in accordance with the present invention. For example, a central light source fiber optic is utilized in certain preferred embodiments, but other light source arrangements (such as a plurality of light source fibers, etc.). In addition, lookup tables are utilized for various aspects of the present invention, but polynomial type calculations could similarly be employed. Thus, although various preferred embodiments of the present invention have been disclosed for illustrative purposes, those skilled in the art will appreciate that various modifications, additions and/or substitutions are possible without departing from the scope and spirit of the present invention as disclosed in the claims.
Reference is also made to copending international application filed on even date herewith under the Patent Cooperation Treaty, for “Apparatus and Method for Measuring Optical Characteristics of an Object,” by the inventors hereof, which is hereby incorporated by reference.
This application is a continuation of application Ser. No. 12/661,542, filed Mar. 17, 2010, abandoned, which is a continuation of application Ser. No. 11/510,494, Aug. 25, 2006 now U.S. Pat. No. 7,682,150, which is a continuation of application Ser. No. 10/407,624, filed Apr. 4, 2003, now U.S. Pat. No. 7,097,450, which is a continuation of application Ser. No. 09/865,801, filed May 25, 2001, now U.S. Pat. No. 6,726,476, which is a continuation of application Ser. No. 09/091,170, filed Jun. 8, 1998, now U.S. Pat. No. 6,254,385, which was the national stage application of PCT/US97/00129 Jan. 2, 1997.
| Number | Name | Date | Kind |
|---|---|---|---|
| 3327584 | Kissinger | Jun 1967 | A |
| 3436157 | Adler et al. | Apr 1969 | A |
| 3507042 | Hana | Apr 1970 | A |
| 3555262 | Shimada | Jan 1971 | A |
| 3663813 | Shaw | May 1972 | A |
| 3684868 | Christie | Aug 1972 | A |
| 3709612 | Clemens | Jan 1973 | A |
| 3743429 | Kawai | Jul 1973 | A |
| 3748741 | Yerkes, Jr. | Jul 1973 | A |
| 3778541 | Bowker | Dec 1973 | A |
| 3792928 | Poilleux | Feb 1974 | A |
| 3940608 | Kissinger | Feb 1976 | A |
| 3986777 | Roll | Oct 1976 | A |
| 4054389 | Owen | Oct 1977 | A |
| 4088890 | Waters | May 1978 | A |
| 4096217 | Roll | Jun 1978 | A |
| 4115922 | Alderman | Sep 1978 | A |
| 4125329 | French et al. | Nov 1978 | A |
| 4150287 | Perkins | Apr 1979 | A |
| 4184175 | Mullane, Jr. | Jan 1980 | A |
| 4196988 | Kawasaki | Apr 1980 | A |
| 4207678 | Jeannette | Jun 1980 | A |
| 4241738 | Lübbers | Dec 1980 | A |
| 4269512 | Nosler | May 1981 | A |
| 4278353 | Ostermayer et al. | Jul 1981 | A |
| 4290433 | Alfano | Sep 1981 | A |
| 4324546 | Heitlinger et al. | Apr 1982 | A |
| 4382784 | Freller | May 1983 | A |
| 4411626 | Becker et al. | Oct 1983 | A |
| 4434654 | Hulsing, II et al. | Mar 1984 | A |
| 4464054 | Karras et al. | Aug 1984 | A |
| 4487206 | Aagard | Dec 1984 | A |
| 4505589 | Ott et al. | Mar 1985 | A |
| 4560275 | Goetz | Dec 1985 | A |
| 4568191 | Barry | Feb 1986 | A |
| 4575805 | Moermann et al. | Mar 1986 | A |
| 4589846 | Annoni | May 1986 | A |
| 4616933 | Leveque et al. | Oct 1986 | A |
| 4653905 | Farrar et al. | Mar 1987 | A |
| 4654794 | O'Brien | Mar 1987 | A |
| 4666309 | Barry et al. | May 1987 | A |
| 4687329 | Schultz | Aug 1987 | A |
| 4707138 | Coatney | Nov 1987 | A |
| 4728290 | Eisner et al. | Mar 1988 | A |
| 4730922 | Bach et al. | Mar 1988 | A |
| 4773063 | Hunsperger et al. | Sep 1988 | A |
| 4798951 | Walker | Jan 1989 | A |
| 4823169 | Ogura | Apr 1989 | A |
| 4836674 | Lequime et al. | Jun 1989 | A |
| 4844617 | Kelderman et al. | Jul 1989 | A |
| 4870267 | Beeckel | Sep 1989 | A |
| 4878485 | Adair | Nov 1989 | A |
| 4881811 | O'Brien | Nov 1989 | A |
| 4886355 | Keane | Dec 1989 | A |
| 4909633 | Okui | Mar 1990 | A |
| 4914512 | Sekiguchi | Apr 1990 | A |
| 4917500 | Lugos | Apr 1990 | A |
| 4957371 | Pellicori et al. | Sep 1990 | A |
| 4966458 | Burns et al. | Oct 1990 | A |
| 4986671 | Sun et al. | Jan 1991 | A |
| 4988206 | Melleney et al. | Jan 1991 | A |
| 5017772 | Hafle | May 1991 | A |
| 5028139 | Kramer et al. | Jul 1991 | A |
| 5040940 | Kolodziej et al. | Aug 1991 | A |
| 5095210 | Wheatley et al. | Mar 1992 | A |
| 5103085 | Zimmerman | Apr 1992 | A |
| 5131844 | Marinaccio et al. | Jul 1992 | A |
| 5139335 | Lundeen et al. | Aug 1992 | A |
| 5142383 | Mallik | Aug 1992 | A |
| 5149963 | Hassler, Jr. | Sep 1992 | A |
| 5159199 | LaBaw | Oct 1992 | A |
| 5164597 | Lodder | Nov 1992 | A |
| 5166755 | Gat | Nov 1992 | A |
| 5177694 | Graham | Jan 1993 | A |
| 5193525 | Silverstein | Mar 1993 | A |
| 5214274 | Yang | May 1993 | A |
| 5223917 | Richert | Jun 1993 | A |
| 5229841 | Taranowski et al. | Jul 1993 | A |
| 5245404 | Jannson et al. | Sep 1993 | A |
| 5270818 | Ottenstein | Dec 1993 | A |
| 5272518 | Vincent | Dec 1993 | A |
| 5273429 | Rekow | Dec 1993 | A |
| 5306144 | Hibst et al. | Apr 1994 | A |
| 5308771 | Zhou et al. | May 1994 | A |
| 5309256 | Takada et al. | May 1994 | A |
| 5309257 | Bonino | May 1994 | A |
| 5329935 | Takahashi | Jul 1994 | A |
| 5369261 | Shamir | Nov 1994 | A |
| 5369481 | Berg et al. | Nov 1994 | A |
| 5371586 | Chau | Dec 1994 | A |
| 5377669 | Schulz | Jan 1995 | A |
| 5383020 | Vieillefosse | Jan 1995 | A |
| 5386292 | Massen et al. | Jan 1995 | A |
| 5387977 | Berg et al. | Feb 1995 | A |
| 5392110 | Yojima et al. | Feb 1995 | A |
| 5401954 | Richert | Mar 1995 | A |
| 5401967 | Stedman et al. | Mar 1995 | A |
| 5404218 | Nave et al. | Apr 1995 | A |
| 5406305 | Shimomura | Apr 1995 | A |
| 5410410 | Yamazaki et al. | Apr 1995 | A |
| 5410413 | Sela | Apr 1995 | A |
| 5424720 | Kirkpatrick | Jun 1995 | A |
| 5428450 | Vieillefosse et al. | Jun 1995 | A |
| 5450193 | Carlsen et al. | Sep 1995 | A |
| 5450203 | Penkethman | Sep 1995 | A |
| 5450511 | Dragone | Sep 1995 | A |
| 5453838 | Danielian et al. | Sep 1995 | A |
| 5457525 | Ohtsuka et al. | Oct 1995 | A |
| 5461476 | Fournier | Oct 1995 | A |
| 5467289 | Abe et al. | Nov 1995 | A |
| 5469249 | Magyar, Jr. et al. | Nov 1995 | A |
| 5474449 | Loge et al. | Dec 1995 | A |
| 5477332 | Stone et al. | Dec 1995 | A |
| 5479252 | Worster et al. | Dec 1995 | A |
| 5483259 | Sachs | Jan 1996 | A |
| 5483335 | Tobias | Jan 1996 | A |
| 5487661 | Peithman | Jan 1996 | A |
| 5497227 | Takeuchi et al. | Mar 1996 | A |
| 5498157 | Hall | Mar 1996 | A |
| 5528266 | Arbeitman | Jun 1996 | A |
| 5533628 | Tao | Jul 1996 | A |
| 5543920 | Collins | Aug 1996 | A |
| 5560355 | Merchant et al. | Oct 1996 | A |
| 5565976 | Fieggen et al. | Oct 1996 | A |
| 5575284 | Athan et al. | Nov 1996 | A |
| 5583631 | Lazzerini | Dec 1996 | A |
| 5590251 | Takagi | Dec 1996 | A |
| 5592294 | Ota et al. | Jan 1997 | A |
| 5604594 | Juffinger | Feb 1997 | A |
| 5609978 | Giorgianni et al. | Mar 1997 | A |
| 5619936 | Veltmann | Apr 1997 | A |
| 5625459 | Driver | Apr 1997 | A |
| 5650940 | Tonozuka | Jul 1997 | A |
| 5663656 | Wilson | Sep 1997 | A |
| 5668633 | Cheetam et al. | Sep 1997 | A |
| 5671043 | Ivers | Sep 1997 | A |
| 5671735 | MacFarlane et al. | Sep 1997 | A |
| 5683243 | Andreiko et al. | Nov 1997 | A |
| 5684294 | Kouhi | Nov 1997 | A |
| 5684807 | Bianchini, Jr. | Nov 1997 | A |
| 5690486 | Zigelbaum | Nov 1997 | A |
| 5695949 | Galen et al. | Dec 1997 | A |
| 5696751 | Juffinger | Dec 1997 | A |
| 5701175 | Kostizak | Dec 1997 | A |
| 5715823 | Wood | Feb 1998 | A |
| 5742060 | Ashburn | Apr 1998 | A |
| 5745229 | Jung et al. | Apr 1998 | A |
| 5754283 | Keane et al. | May 1998 | A |
| 5757496 | Yamazaki | May 1998 | A |
| 5759030 | Jung et al. | Jun 1998 | A |
| 5760913 | Falk | Jun 1998 | A |
| 5766006 | Murljacic | Jun 1998 | A |
| 5768528 | Stumm | Jun 1998 | A |
| 5774610 | O'Rourke et al. | Jun 1998 | A |
| 5784507 | Holm-Kennedy et al. | Jul 1998 | A |
| 5798839 | Berner et al. | Aug 1998 | A |
| 5818044 | Sodickson | Oct 1998 | A |
| 5819119 | Imafuji | Oct 1998 | A |
| 5822474 | Hara | Oct 1998 | A |
| 5845077 | Fawcett | Dec 1998 | A |
| 5850195 | Berlien, Jr. et al. | Dec 1998 | A |
| 5850301 | Mizuochi et al. | Dec 1998 | A |
| 5851113 | Jung et al. | Dec 1998 | A |
| 5864834 | Arai | Jan 1999 | A |
| 5871351 | Jung et al. | Feb 1999 | A |
| 5880826 | Jung et al. | Mar 1999 | A |
| 5883708 | Jung et al. | Mar 1999 | A |
| 5884156 | Gordon | Mar 1999 | A |
| 5889683 | Ismail | Mar 1999 | A |
| 5892585 | Lianza | Apr 1999 | A |
| 5900909 | Parulski | May 1999 | A |
| 5924981 | Rothfritz et al. | Jul 1999 | A |
| 5926262 | Jung et al. | Jul 1999 | A |
| 5946220 | Lemelson | Aug 1999 | A |
| 5952992 | Helms | Sep 1999 | A |
| 5961324 | Lehmann | Oct 1999 | A |
| 5961327 | Lohn | Oct 1999 | A |
| 5963332 | Feldman | Oct 1999 | A |
| 5966205 | Jung et al. | Oct 1999 | A |
| 5989022 | Yamamoto et al. | Nov 1999 | A |
| 5995235 | Sui et al. | Nov 1999 | A |
| 6002488 | Berg et al. | Dec 1999 | A |
| 6007332 | O'Brien | Dec 1999 | A |
| 6008905 | Breton et al. | Dec 1999 | A |
| 6030209 | Panzera et al. | Feb 2000 | A |
| 6031928 | Scott | Feb 2000 | A |
| 6037629 | Gardner | Mar 2000 | A |
| 6038016 | Jung et al. | Mar 2000 | A |
| 6038024 | Berner | Mar 2000 | A |
| 6040902 | Jung et al. | Mar 2000 | A |
| 6043445 | Gigliotti | Mar 2000 | A |
| 6043894 | Van Aken | Mar 2000 | A |
| 6052195 | Mestha et al. | Apr 2000 | A |
| 6057925 | Anthon | May 2000 | A |
| 6078398 | Feldman et al. | Jun 2000 | A |
| 6086274 | Krzyminski | Jul 2000 | A |
| 6101265 | Bacaus et al. | Aug 2000 | A |
| 6111650 | Rawicz | Aug 2000 | A |
| 6118521 | Jung et al. | Sep 2000 | A |
| 6127673 | Jung et al. | Oct 2000 | A |
| 6130752 | Smith | Oct 2000 | A |
| 6163377 | Boles | Dec 2000 | A |
| 6188471 | Jung et al. | Feb 2001 | B1 |
| 6198862 | Nakajima | Mar 2001 | B1 |
| 6205716 | Peltz | Mar 2001 | B1 |
| 6212256 | Miesbauer et al. | Apr 2001 | B1 |
| 6222620 | Jung et al. | Apr 2001 | B1 |
| 6233047 | Jung et al. | May 2001 | B1 |
| 6239868 | Jung et al. | May 2001 | B1 |
| 6246471 | Jung et al. | Jun 2001 | B1 |
| 6246479 | Jung et al. | Jun 2001 | B1 |
| 6246862 | Grivas | Jun 2001 | B1 |
| 6249000 | Muramatsu | Jun 2001 | B1 |
| 6249339 | Jung et al. | Jun 2001 | B1 |
| 6249340 | Jung et al. | Jun 2001 | B1 |
| 6249348 | Jung et al. | Jun 2001 | B1 |
| 6249887 | Gray | Jun 2001 | B1 |
| 6254385 | Jung et al. | Jul 2001 | B1 |
| 6256668 | Slivka et al. | Jul 2001 | B1 |
| 6264470 | Jung et al. | Jul 2001 | B1 |
| 6271913 | Jung et al. | Aug 2001 | B1 |
| 6301004 | Jung et al. | Oct 2001 | B1 |
| 6307629 | Jung et al. | Oct 2001 | B1 |
| 6323487 | Wu | Nov 2001 | B1 |
| 6362888 | Jung et al. | Mar 2002 | B1 |
| 6373573 | Jung et al. | Apr 2002 | B1 |
| 6381017 | Jung et al. | Apr 2002 | B2 |
| 6414750 | Jung et al. | Jul 2002 | B2 |
| 6417917 | Jung et al. | Jul 2002 | B1 |
| 6449041 | Jung et al. | Sep 2002 | B1 |
| 6490038 | Jung et al. | Dec 2002 | B1 |
| 6501542 | Jung et al. | Dec 2002 | B2 |
| 6512577 | Ozanich | Jan 2003 | B1 |
| 6519037 | Jung et al. | Feb 2003 | B2 |
| 6538726 | DeJung et al. | Mar 2003 | B2 |
| 6570654 | Jung et al. | May 2003 | B2 |
| 6573984 | Jung et al. | Jun 2003 | B2 |
| 6583866 | Jung et al. | Jun 2003 | B2 |
| 6590660 | Jung et al. | Jul 2003 | B2 |
| 6596981 | Aswell | Jul 2003 | B1 |
| 6726476 | Jung et al. | Apr 2004 | B2 |
| 6750971 | Overbeck | Jun 2004 | B2 |
| 6836325 | Maczura | Dec 2004 | B2 |
| 6847447 | Ozanich | Jan 2005 | B2 |
| 6870616 | Jung et al. | Mar 2005 | B2 |
| 6888634 | Jung et al. | May 2005 | B2 |
| 6903813 | Jung et al. | Jun 2005 | B2 |
| 6915955 | Jung et al. | Jul 2005 | B2 |
| 6950189 | Jung et al. | Sep 2005 | B2 |
| 6958810 | Jung et al. | Oct 2005 | B2 |
| 7018204 | Jung et al. | Mar 2006 | B2 |
| 7069186 | Jung et al. | Jun 2006 | B2 |
| 7097450 | Jung et al. | Aug 2006 | B2 |
| 7099012 | Crawford | Aug 2006 | B1 |
| 7110096 | Jung et al. | Sep 2006 | B2 |
| 7113283 | Jung et al. | Sep 2006 | B2 |
| 7116408 | Jung et al. | Oct 2006 | B2 |
| 7119892 | Jung et al. | Oct 2006 | B2 |
| 7139068 | Jung et al. | Nov 2006 | B2 |
| 7240839 | Jung et al. | Jul 2007 | B2 |
| 7244122 | Jung et al. | Jul 2007 | B2 |
| 7580130 | Shannon | Aug 2009 | B2 |
| 7768645 | Roman | Aug 2010 | B2 |
| 7957762 | Herz | Jun 2011 | B2 |
| 8008613 | Tam | Aug 2011 | B2 |
| Number | Date | Country |
|---|---|---|
| 2256355 | Dec 1973 | DE |
| 3038786 | Apr 1982 | DE |
| 9012977 | Mar 1991 | DE |
| 0167750 | Jan 1986 | EP |
| 0263016 | Jun 1988 | EP |
| 0266682 | Nov 1988 | EP |
| 0681256 | Nov 1995 | EP |
| 2669526 | May 1992 | FR |
| 2115175 | Jan 1983 | GB |
| 2135074 | Aug 1984 | GB |
| 2269012 | Jul 1993 | GB |
| 54103055 | Aug 1979 | JP |
| 5011774 | Jul 1987 | JP |
| 01262428 | Oct 1989 | JP |
| 02066429 | Mar 1990 | JP |
| 02236127 | Sep 1990 | JP |
| 03296626 | Dec 1991 | JP |
| 04045776 | Jul 1992 | JP |
| 04295328 | Oct 1992 | JP |
| 07294425 | Nov 1995 | JP |
| 8603292 | Jun 1986 | WO |
| 95 17663 | Jun 1995 | WO |
| Entry |
|---|
| Aswell, Cecil J. et al., “A Monolithic Light-to-Frequency Converter with a Scalable Sensor Array”, IEEE, 1994, pp. 122-123 and 158-159. |
| Bangtson et al.; “The conversion of Chromascan designations to CIE tristimilus values”; Nov. 1982; pp. 610-617 vol. 48 No. 5, Journal of Prosthetic Dentistry. |
| Barghi et al.; “Effects of batch variation on shade of dental porcelain”; Nov. 1985; pp. 625-627, vol. 54 No. 5, Journal of Prosthetic Dentistry. |
| Billmeyer & Saltman, “Principles of color technology,” pp. 79-80, Second Ed. 1981. |
| Correria, Jose Higino, et al., “A CMOS Optical Microspectrometer with Light-to-Frequency Converter, Bus Interface, and Stray-Light Compensation,” EEE Transactions on Instrumentation and Measurement, vol. 50, No. 6, Dec. 2001, pp. 1530-1537. |
| Council on Dental Materials, Instruments, and Equipment “How to improve shade matching in the dental operatory”; Feb. 1981; pp. 209-210, vol. 102: JADA. |
| Davison et al.; “Shade selection by color vision-defective dental personnel”; Jan. 1990; pp. 97-101 vol. 63 No. 1, Journal of Prosthetic Dentistry. |
| de Graaf, G., et al., “On-Chip Integrated CMOS Optical Microspectrometer with Light-to-Frequency Converter and Bus Interface,” 1999 IEEE International Solid-State Circuits Conference, 10 pages, 1999. |
| Demro, James C., R. Hartshorne, P.A. Levine, L.M. Woody, “Design of Multispectral, Wedge Filter, Remote-Sensing Instrument incorporating a multi-port, thinned, CCD area array” SPIE vol. 24 80 p. 280, Jun. 1995. |
| Dickerson; “Trilogy of Creating an Esthetic Smile”; Jul. 1996; pp. 1-7, vol. 1, Issue 3; Technical Update—A Publication of Micro Dental Laboratories. |
| Elerding, George T. John G. Thunen, Loren M. Woody “Wedge Imaging Spectrometer: Application to drug and pollution law enforcement” SPIE vol. 1479 Surveillance Technologies,.p. 380 (1991). |
| Goldstein et al.; “Repeatability of a specially designed intraoral colorimeter”; Jun. 1993; pp. 616-619, vol. 69 No. 6, Journal of Prosthetic Dentistry. |
| Goodkind et al.; “A comparison of Chromascan and spectrophotometric color measurement of 100 natural teeth”; Jan. 1985; pp. 105-109, vol. 53 No. 1, Journal of Prosthetic Dentistry. |
| Ichikawa et al.; “Trial Manufacture of Photoelectric Colorimeter Using Optical Fibers”; Nov. 1969; pp. 191-197, vol. 10, No. 4, Bull. Tokyo dent. Coll. |
| Johnston et al.; “The Color Accuracy of the Kubelka-Munk Theory for Various Colorants in Maxillofacial Prosthetic Material”; Sep. 1987; pp. 1438-1444, vol. 66, No. 9; J. Dent. Res. |
| Johnston et al.; “Assessment of Appearance Match by Visual Observation and Clinical Colorimetry”; May 1989; pp. 819-822, vol. 68, No. 5; J. Dent. Res. |
| Kato et al; “The Current State of Porcelain Shades: A Discussion”; Oct. 1984; pp. 559-571, vol. 8, No. 9; Quintessence of Dental Technology. |
| Milca, Aram M., “Linear-Wedge Spectrometer” SPIE vol. 1298 Imaging Spectroscopy of the Terrearial Environment , p. 127 (1990). |
| Miller; “Organizing color in dentistry”; Dec. 1987; pp. 26E-40E. Special Issue; JADA. |
| Miller et al; “Shade selection and laboratory communication”; May 1993; pp. 305-309, vol. 24, No. 5; Quintessence International. |
| O'Brien et al.; “Coverage Errors of Two Shade Guides”; Jan./Feb. 1991; pp. 45-50. vol. 4, No. 1; The International Journal of Prosthodontics. |
| O'Brien et al.; “A New, Small-color-difference Equation for Dental Shades”: Nov. 1990; pp. 1762-1764, vol. 69, No. 11; J. Dent Res. |
| O'Keefe et al.; “Color Shade and Matching: The Weak Link in Esthetic Dentistry”; Feb. 1990; pp. 116-120, vol. XI, No. 2, Compend Contin Educ Dent. |
| Pensler, “A New Approach to Shade Selection”; Sep. 1991; pp. 668-675, vol. XII, No. 9, Compend Conlin Educ Dent. |
| Preston et al.; “Light and Lighting in the Dental Office”; Jul. 1978; pp. 431-451, vol. 22, No. 3; Dental Clinics of North America. |
| Preston; “Current status of shade selection and color matching”; Jan. 1985; pp. 47.58, vol. 16, No. 1; Quintessence International. |
| Rosenstiel et al.; “The effects of manipulative variables on the color of ceramic metal restorations”: Sep. 1987; pp. 297-303, vol. 60 No. 3, Journal of Prosthetic Dentistry. |
| Rugh et al.; “The Relationship Between Elastomer Opacity, Colorimeter Beam Size, and Measured Colorimetric Response”; Nov./Dec. 1991; pp. 569-576, vol. 4, No. 6; The International Journal of Prosthodontics. |
| Ryther et al.; “Colometric Evaluation of Shade Guide Variability”; 1993; p. 215; J. Dent. Res. 72 (IADIR Abstracts) Special Issue. |
| Schwabacher et al.; “Three-dimensional color coordinates of natural teeth compared with three shade guides”; Oct. 1990; pp. 425-431, vol. 64 No. 4, Journal of Prosthetic Dentistry. |
| Seghi et al.; “Spectrophotometric analysis of color differences between porcelain systems”; Jul. 1936; pp. 35-40, vol. 56 No. 1, Journal of Prosthetic Dentistry. |
| Seghi et al.; “Visual and Instrumental Colorimetric Assessments of Small Color Differences on Translucent Dental Porcelain”; Dec. 1989; pp. 1760-1764, vol. 68, No. 12; J. Dent. Res. |
| Seghi et al.; “Performance Assessment of Colorimetric Devices on Dental Porcelains”; Dec. 1989; pp. 1755-1759, vol. 69, No. 11; J. Dent. Res. |
| Seghi; “Effects of Instrument-measuring Geometry on Colorimetric Assessments of Dental Porcelains”; May 1990; pp. 1130-1183, vol. 69, No. 5; J. Dent. Res. |
| Sorensen et al.; “Improved color matching of metal-ceramic restorations. Part I: A systematic method for shade determination”; Aug. 1987; pp. 133-139, vol. 58, No. 2, Journal of Prosthetic Dentistry. |
| Sorensen et al; “Improved color matching of metal-ceramic restorations. Part II: Procedures for visual communication”; Dec. 1987; pp. 669-677. vol. 58, No. 6, Journal of Prosthetic Dentistry. |
| Sproul; “Color matching in dentistry. Part 1. The three-dimensional nature of color”; Apr. 1973; pp. 416-424, vol. 29, No. 4; J. Prosthet. Dent. |
| Sproul; “Color matching in dentistry. Part 1. Color control”; Feb. 1974; pp. 146-154, vol. 31, No. 2; J. Prosthet. Dent. |
| Sproul; “Color matching in dentistry. Part 2. Practical applications of the organization of color”; May 1973; pp. 556-566, vol. 29, No. 5; J. Prosthet. Dent. |
| Swift et al.; “Colormetric Evaluation of Vita Shade Resin Composites”: 1994; pp. 356-361, vol. 7, No. 4; The International Journal of Prosthodontics. |
| van der Burgt et al.; “A comparison of new and conventional methods for quantification of tooth color”; Feb. 1990; pp. 155-162, vol. 63 No. 2, Journal of Prosthetic Dentistry. |
| Slaughter, et al., “Nondestruction Determination of Soluble Solids in Tomatoes using Near Infrared Spectroscopy”, 1996, pp. 695-697. |
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