WO2009139110A1 - 口腔内測定装置及び口腔内測定システム - Google Patents
口腔内測定装置及び口腔内測定システム Download PDFInfo
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- WO2009139110A1 WO2009139110A1 PCT/JP2009/001603 JP2009001603W WO2009139110A1 WO 2009139110 A1 WO2009139110 A1 WO 2009139110A1 JP 2009001603 W JP2009001603 W JP 2009001603W WO 2009139110 A1 WO2009139110 A1 WO 2009139110A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/107—Measuring physical dimensions, e.g. size of the entire body or parts thereof
- A61B5/1076—Measuring physical dimensions, e.g. size of the entire body or parts thereof for measuring dimensions inside body cavities, e.g. using catheters
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/24—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor for the mouth, i.e. stomatoscopes, e.g. with tongue depressors; Instruments for opening or keeping open the mouth
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/45—For evaluating or diagnosing the musculoskeletal system or teeth
- A61B5/4538—Evaluating a particular part of the muscoloskeletal system or a particular medical condition
- A61B5/4542—Evaluating the mouth, e.g. the jaw
- A61B5/4547—Evaluating teeth
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C9/00—Impression cups, i.e. impression trays; Impression methods
- A61C9/004—Means or methods for taking digitized impressions
- A61C9/0046—Data acquisition means or methods
- A61C9/0053—Optical means or methods, e.g. scanning the teeth by a laser or light beam
- A61C9/006—Optical means or methods, e.g. scanning the teeth by a laser or light beam projecting one or more stripes or patterns on the teeth
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
- G01B11/00—Measuring arrangements characterised by the use of optical techniques
- G01B11/24—Measuring arrangements characterised by the use of optical techniques for measuring contours or curvatures
- G01B11/25—Measuring arrangements characterised by the use of optical techniques for measuring contours or curvatures by projecting a pattern, e.g. one or more lines, moiré fringes on the object
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- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T7/00—Image analysis
- G06T7/50—Depth or shape recovery
- G06T7/521—Depth or shape recovery from laser ranging, e.g. using interferometry; from the projection of structured light
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C9/00—Impression cups, i.e. impression trays; Impression methods
- A61C9/004—Means or methods for taking digitized impressions
- A61C9/0046—Data acquisition means or methods
- A61C9/0053—Optical means or methods, e.g. scanning the teeth by a laser or light beam
Definitions
- the present invention relates to an intra-oral measurement device and an intra-oral measurement system which directly measure the intraoral area.
- a method of producing a dental prosthesis such as an inlay, a crown, and a bridge
- a method of casting and producing a metal material or a ceramic material by a lost wax method is generally employed.
- intraoral measurement of teeth and gingiva can be performed by directly reading the shapes of the abutment tooth, cavity-formed tooth, adjacent tooth, and opposite tooth in the oral cavity using an optical three-dimensional camera.
- an optical three-dimensional camera a camera for performing non-contact three-dimensional measurement represented by a phase shift method or a space coding method is used.
- an optical three-dimensional camera of this type for example, there is one described in Patent Document 1 (Japanese Patent Application Laid-Open No. 2000-74635).
- FIG. 15 is an explanatory view showing the configuration of a conventional optical three-dimensional camera.
- a conventional optical three-dimensional camera includes a light source 102, a pattern mask 103, diaphragms 104 and 105, a prism 106, and an image sensor 107 such as a CCD inside an exterior case 101.
- the light emitted from the light source 102 passes through the pattern mask 103 and becomes stripe pattern light.
- the fringe pattern light passes through the diaphragm 104 to finely adjust its optical axis, is refracted by the prism 106, and is projected onto the object to be measured 108.
- the fringe pattern light projected onto the object to be measured 108 is reflected by the surface of the object to be measured 108, enters the prism 106, and is refracted by the prism 106.
- the refracted light passes through the diaphragm 105 and is received by the image sensor 107 such as a CCD.
- Design of a dental prosthesis using a CAD / CAM system by converting data of a two-dimensional still image received (captured) by the image sensor 107 into data of three-dimensional coordinates using triangulation. And three-dimensional image data of the object 108 to be manufactured can be obtained.
- a dental prosthesis can be produced more efficiently than the lost wax method, and a dental excellent in the accuracy of fitting into the oral cavity.
- a prosthesis can be made.
- metal powder such as titanium oxide is sprayed into the oral cavity so as to equalize the difference (variation) in the surface reflectance in the oral cavity.
- Non-Patent Document 1 Leo J. Miserendino, Robert M. Pick, Tadamasa Tsuda, "Lasers in Dentistry", 1st Edition, Quintessence Publishing Co., Ltd., 2004 10) May 10) and Non-patent document 2 (Taketaka Takeda, "Colorimetric study of gingiva by spectroradiometry of the gingiva-for anterior teeth of young people-", The Japan Prosthodontic Society Journal, Japan Prosthodontic Society, 1987 On April 1, 2001, vol. 31, No. 2, pp. 363-370).
- Non-Patent Document 1 describes that the peak of the surface reflectance of enamel is around 550 nm, and the peak of the surface reflectance of dentin is around 700 nm. Further, Non-Patent Document 2 describes that the peak of the surface reflectance of the gum is in the vicinity of 650 nm.
- Patent Document 1 spraying metal powder as described in Patent Document 1 is an act accompanied by bitterness and discomfort for the patient, and a doctor is required to spray uniformly in the oral cavity so that time and skill can be obtained. It is a necessary act.
- an object of the present invention is to solve the above-mentioned problems, and to provide an intra-oral measurement device capable of accurately measuring the inside of the oral cavity without spraying metal powder in the oral cavity. is there.
- a light projecting section which emits light of at least two different wavelengths with the same optical axis toward an object to be measured including at least teeth in the oral cavity,
- An imaging unit for receiving and imaging the light reflected by the object to be measured;
- An intraoral measurement device comprising:
- the intraoral measurement device according to the first aspect, wherein the light projecting part comprises at least two LED light sources different in at least two wavelengths.
- an intraoral cavity according to the first aspect, wherein the light projecting unit comprises a white light source and at least two different wavelength filters of different wavelengths movable on the optical axis of the white light source.
- the light projecting unit comprises a white light source and at least two different wavelength filters of different wavelengths movable on the optical axis of the white light source.
- the intraoral measurement device according to the first aspect, wherein the light projecting unit emits light having a coded fringe pattern.
- the intraoral measurement device wherein the light of different wavelengths comprises light of wavelengths of 500 to 565 nm and light of wavelengths of 625 to 740 nm. .
- a plurality of images of light of different wavelengths captured by the imaging unit are combined, the combined image is converted into three-dimensional coordinates, and a three-dimensional image of the object is measured.
- An intraoral measurement device comprising an image processing unit to be obtained.
- the intra-oral measurement according to the sixth aspect wherein the image processing unit combines a plurality of images of light of different wavelengths based on luminance information of each pixel of the image.
- the image processing unit combines a plurality of images of light of different wavelengths based on luminance information of each pixel of the image.
- a light projecting section which emits light of at least two different wavelengths with the same optical axis toward an object to be measured including at least teeth in the oral cavity,
- An imaging unit for receiving and imaging the light reflected by the object to be measured;
- An image processing unit that combines a plurality of images of different wavelengths captured by the imaging unit, converts the combined image into three-dimensional coordinates, and obtains a three-dimensional image of the object to be measured;
- An intra-oral measurement system comprising:
- the intra-oral measurement device and the intra-oral measurement system according to the present invention since the above configuration is provided, it is possible to accurately measure the shape in the oral cavity without spraying the metal powder in the oral cavity.
- FIG. 1 is an explanatory view showing a schematic configuration of an intra-oral measurement system having an oral scanner according to a first embodiment of the present invention
- FIG. 2 is a view from below of the oral scanner shown in FIG.
- FIG. 3 is a schematic perspective view showing measurement of the surface shape of the patient's back teeth using the oral scanner shown in FIG.
- FIG. 4 is a schematic perspective view showing measurement of the surface shape of the patient's front teeth using the oral scanner shown in FIG.
- FIG. 1 is an explanatory view showing a schematic configuration of an intra-oral measurement system having an oral scanner according to a first embodiment of the present invention
- FIG. 2 is a view from below of the oral scanner shown in FIG.
- FIG. 3 is a schematic perspective view showing measurement of the surface shape of the patient's back teeth using the oral scanner shown in FIG.
- FIG. 4 is a schematic perspective view showing measurement of the surface shape of the patient's front teeth using the oral scanner shown in FIG.
- FIG. 1 is an explanatory view showing a schematic configuration
- FIG. 5 is a block diagram of the intra-oral measurement system according to the first embodiment of the present invention
- 6 is an explanatory view showing a schematic configuration of a light projecting unit of the intraoral measurement system shown in FIG.
- FIG. 7 is a flowchart for measuring the shape of the object using the intra-oral measurement system according to the first embodiment of the present invention
- FIG. 8 is a view showing an example of a gray pattern as fringe pattern light projected onto the object to be measured
- FIG. 9 is a flowchart of image photographing of an object in the intra-oral measurement system according to the first embodiment of the present invention
- FIG. 10 is a flowchart of an image combining process in the intra-oral measurement system according to the first embodiment of the present invention
- FIG. 11A is a diagram showing a G signal image captured in the intraoral measurement system according to the first embodiment of the present invention
- 11B is a histogram of luminance values at respective pixels of the G signal image of FIG. 11A
- FIG. 11C is a graph in which the histogram of FIG. 11B is connected by a smooth line using the method of least squares
- FIG. 12 is an explanatory view showing a schematic configuration of an oral scanner incorporating an image processing unit
- FIG. 13 is a flowchart of an image combining process of the intra-oral measurement system according to the second embodiment of the present invention
- FIG. 14 is an explanatory view showing a schematic configuration of a light projecting unit of the intra-oral measurement system according to the third embodiment of the present invention
- FIG. 15 is a conceptual view showing the measurement of teeth and gums described in Patent Document 1.
- FIG. 1 is an explanatory view showing a schematic configuration of an intra-oral measurement system having an intra-oral measurement device (hereinafter referred to as an oral scanner) according to a first embodiment of the present invention.
- an oral scanner an intra-oral measurement device
- the oral scanner 1 is provided with an outer case 2 of a size that can be inserted directly into the oral cavity of a patient and made of a material that does not affect the human body.
- a rubber attachment portion 3 is provided at the tip of the outer case 2, and the rubber 4 which is an example of a gap holding member is detachably attached to the rubber attachment portion 3.
- the rubber 4 is disposed adjacent to the irradiation port 5 provided on the front end side of the outer case 2.
- the rubber 4 is a disposable member for keeping the gap between the irradiation port 2 and the measurement object 21 at a constant distance L (for example, 5 mm), and is made of a material having no problem in terms of hygiene.
- L for example, 5 mm
- the rubber 4 has a predetermined hardness so that the gap between the irradiation port 5 and the object 2 can be held constant, its tip can be deformed according to the shape of the portion in contact in the oral cavity It's getting softer.
- the rubber 4 is made of rubber having a two-layer structure in which the material is different between the main body and the tip.
- the oral scanner 1 When measuring the surface shape of the back teeth of a patient using the oral scanner 1, as shown in FIG. 3, a portion where the rubber 4 is adjacent to the object to be measured 21 (for example, the tooth next to the tooth to be measured)
- the oral scanner 1 may be arranged to be in contact with
- the attachment position and the number of rubbers 4 are not particularly limited, and may be appropriately set according to the object 21 to be measured.
- FIG. 3 and 4 show the configuration of the oral scanner 1 in a simplified manner.
- a pattern mask 12 composed of a light projecting unit 10, a condensing lens 11, an LCD shutter (liquid crystal shutter), etc., a beam splitter 13, a diaphragm 14, an objective condensing lens 15 are disposed on the same axis, and in parallel to them, the mirror 16, the imaging lens 17, and the image sensor 18 such as a CCD are disposed on the same axis. Further, the oral scanner 1 is connected to an external device 20 such as a PC (personal computer) via a transfer cable 19.
- an external device 20 such as a PC (personal computer) via a transfer cable 19.
- the light emitted from the light projecting unit 10 passes through the condensing lens 11 and is condensed, and is converted into stripe pattern light by the pattern mask 12.
- the converted stripe pattern light is incident on the beam splitter 13 and is separated by the beam splitter 13 into a projection light path 31 directed to the object 21 side and an observation light path 32 directed to the image sensor 18 side.
- the stripe pattern light traveling on the projection light path 31 passes through the diaphragm 14 and the objective condenser lens 15 and is projected onto the object to be measured 21.
- the stripe pattern light projected onto the object to be measured 21 is reflected by the object to be measured 21, passes through the objective condenser lens 15, the diaphragm 14, the beam splitter 13, the mirror 16 and the imaging lens 17 in this order, The light is received and imaged. Data of a two-dimensional image captured by the image sensor 18 is transferred to the image processing unit 40 through the transfer cable 19.
- the image processing unit 40 is stored in a CPU (central processing unit: not shown) of the external device 20.
- the image processing unit 40 converts the transferred two-dimensional image data into three-dimensional coordinate data to obtain three-dimensional image data of the object to be measured 21 for designing and manufacturing a dental prosthesis.
- the image processing unit 40 includes a photographing control unit 41, an image storage unit 42, a two-dimensional image processing unit 43, a low precision three-dimensional image conversion unit 44, and a three-dimensional image storage unit 45. , A three-dimensional image determination unit 46, and a high-precision three-dimensional image conversion unit 47.
- the functions of the units of the image processing unit 40 will be described in detail later.
- FIG. 6 is an explanatory view showing a schematic configuration of a light projecting unit of the intra-oral measurement system according to the first embodiment of the present invention.
- the light projecting unit 10 is a light source for clearly photographing the object to be measured 21 including at least the teeth 22 in the oral cavity of the patient.
- the light projector 10 emits an LED light source 24 which is an example of a first light source that emits light with a wavelength of 500 to 565 nm (green color), and a second light source that emits light with a wavelength of 625 to 740 nm (red color).
- An LED light source 25, which is an example of a light source, and a mirror group 30 configured of mirrors 26 to 28 and a beam splitter 29 are provided.
- the light from the two LED light sources 24 and 25 is adjusted and illuminated through the mirror group 30 so that the respective optical axes are aligned, ie, the same optical axis.
- Table 1 shows the visual states at each projection wavelength for the teeth 22 and the gums 23 in the oral cavity from various experiments and documents, and summarizes them.
- the circle shows the case where a clear image was obtained
- the triangle shows a case where a partially unsharp but distinguishable image was obtained
- a cross does not give a distinguishable image. The case is shown.
- the intraoral measurement system obtains clear images in all of enamel, dentin and gum by using two LED light sources 24 and 25 having different wavelengths of irradiation light. It is configured to be able to.
- FIG. 7 shows a flowchart for measuring the inside of the oral cavity using the intraoral measurement system according to the first embodiment.
- the oral scanner 1 is set in the patient's oral cavity, and when the dentist presses the video imaging start button (not shown) of the external device 20, for example, the intraoral video imaging with the oral scanner 1 starts. (Step S1).
- Video shooting with the oral scanner 1 is performed by receiving light shot by the object to be measured 21 by the image sensor 18 and shooting while emitting light from the light emitting unit 10 under the control of the shooting control unit 41. .
- An image taken by the oral scanner 1 is transferred to the imaging control unit 41 through the transfer cable 19, and is displayed on the display unit 50 of the external device 20 under the control of the imaging control unit 41.
- the oral scanner 1 performs the same operation as a normal video camera.
- the oral scanner 1 is moved so that the object to be measured 21 is accurately displayed on the display unit 50, and it is confirmed whether the image of the object to be measured 21 projected is good (step S2).
- the imaging position of the oral scanner 1 can be more accurately positioned on the object 21 It can be fitted.
- the judgment of the quality of the image of the object to be measured 21 is carried out, for example, by using an LED light source with an output of 3 W as the light projecting unit 10 and expressing the luminance value with 256 gradations. It is determined whether the average gradation is 40 gradations or more. That is, if it is 40 gradations or more, it will be judged as favorable, and if less than 40 gradations, it will be judged that it is not favorable. Note that this determination may be performed by a dentist or may be automatically performed by the image processing unit 40.
- step S3 This imaging may be performed, for example, by the dentist stepping on a foot switch provided on a medical examination table.
- the image of the object 21 is irradiated with the stripe pattern light by the control of the photographing control unit 41. Capture the image. Thereby, image (two-dimensional still image) data of the object to be measured 21 is obtained.
- the wavelength of light emitted from the light projecting unit 10 is changed (for example, the light source of the light projecting unit 10 is changed from the LED light source 24 to the LED light source 25), and the object to be measured 21 is imaged. Thereafter, under the control of the imaging control unit 40, the object to be measured 21 is irradiated with the stripe pattern light to capture an image of the object to be measured 21. Thereby, image (two-dimensional still image) data of the object to be measured 21 is obtained.
- the captured image (two-dimensional still image) data is stored in the image storage unit 42 in order to convert it into a three-dimensional image using triangulation.
- the image photography method of the to-be-measured object 21 using the light from which a wavelength mutually differs is demonstrated in detail later.
- a plurality of image data of the obtained object to be measured 21 are synthesized as follows. First, in order to improve the contrast of the fringe pattern of the image data stored in the image storage unit 42, the two-dimensional image processing unit 43 performs noise removal, gradation correction, gamma correction, etc. on the image data. The dimensional image processing is performed (step S4).
- the two-dimensional image processing unit 43 determines each pixel of the image data as a pixel group corresponding to the area of the teeth 22 and a pixel corresponding to the area of the gum 23 based on the luminance value of each pixel of the image data. Divide into groups.
- the teeth (enamel) 22 are clearly shown in the image captured using the LED light source 24, and the gums 23 are clear in the image captured using the LED light source 25. Is projected. For this reason, the two-dimensional image processing unit 43 selects data of the pixel group corresponding to the area of the teeth 22 in the image captured using the LED light source 24 and the gums 23 in the image captured using the LED light source 25.
- the data of the pixel group corresponding to the area of (1) is synthesized (step S5).
- tone correction of the pixel group to be converted into the three-dimensional coordinates may be performed with reference to the histogram of the luminance value of each pixel.
- the image synthesis processing method of the area of the teeth 22 and the area of the gums 23 will be described in detail later.
- the low-accuracy three-dimensional image conversion unit 44 thins out the data amount of the combined image data, and converts the data, for example, into 10% to 50% data amount, into three-dimensional coordinates using triangulation. Do. Thereby, a low precision three-dimensional image is obtained (step S6).
- the low precision three-dimensional image is stored in the three-dimensional image storage unit 45.
- the three-dimensional image determination unit 46 determines whether the low-accuracy three-dimensional image is good (step S7). When the three-dimensional image determination unit 46 determines that the low-accuracy three-dimensional image is not good, the process returns to the step S1.
- the high-accuracy three-dimensional image conversion unit 47 uses triangulation for all of the synthesized image data. Convert to three-dimensional coordinates.
- the obtained three-dimensional coordinates are stored, for example, as point cloud data or STL (Stereo Lithography) data in the three-dimensional image storage unit 45 and displayed on the display unit 50 (step S8).
- a high-precision three-dimensional image can be obtained by combining these point cloud data or STL data.
- the space coding method or the phase shift method for measuring the three-dimensional coordinates of the object to be measured 21.
- measurement accuracy can be improved.
- a pattern called a gray code hereinafter referred to as a gray pattern
- FIG. 8 shows an example of seven gray patterns.
- the phase shift method it is desirable to use a known gray-scale pattern that changes in a sine wave as the fringe pattern light projected onto the object to be measured 21. If high measurement accuracy is not required, a normal code pattern may be used as the fringe pattern light projected onto the object to be measured 21.
- step S6 when the obtained three-dimensional image differs from the surface shape of the object to be measured 21 due to poor imaging etc., the time taken to obtain the three-dimensional image is wasted There is no need to perform this process.
- the determination of the quality of the low accuracy three-dimensional image in step S6 may be performed by the dentist by displaying the low accuracy three-dimensional image on the display unit 50. That is, in this case, the dentist determines the quality of the low accuracy three-dimensional image by comparing the shape of the object to be measured 21 seen by oneself with the shape of the object to be measured 21 of the low accuracy three-dimensional image. I do.
- FIG. 9 is a flowchart of image photographing of an object to be measured in the intra-oral measurement system according to the first embodiment. Note that the image capturing of the object to be measured 21 is performed under the control of the imaging control unit 41 unless otherwise noted.
- step S11 only the LED light source 24 that emits light with a wavelength of 500 to 565 nm (green color) is made to emit light (step S11).
- step S12 image data of the object to be measured 21 imaged using light of a wavelength of 500 to 565 nm is referred to as a G signal.
- the G signal is stored in the image storage unit 42 (step S13).
- the LED light source 24 for emitting light of a wavelength of 500 to 565 nm is quenched (step S14).
- the LED light source 25 that emits light of a wavelength (red) of 625 to 740 nm is made to emit light (step S15).
- step S16 image data of the object to be measured 21 imaged using light of a wavelength of 625 to 740 nm is referred to as an R signal.
- the R signal is stored in the image storage unit 42 (step S17).
- FIG. 10 is a flowchart of the image combining process in the intra-oral measurement system according to the first embodiment.
- the object to be measured 21 is the teeth 22 and the gums 23.
- the image combining processing is performed under the control of the two-dimensional image processing unit 43 unless otherwise noted.
- G and R signals stored in the image storage unit 42 are fetched (step S21).
- pre-processing such as noise removal is performed on the captured G signal and R signal (step S22).
- the preprocessed G signal and R signal are converted from analog signals to digital signals (step S23).
- the G signal and the R signal converted into the digital signal are stored in the image storage unit 42 as a G signal image and an R signal image (step S24).
- a luminance value is extracted for each pixel from the G signal image and the R signal image as luminance information used to determine the area of the tooth 22 and the gum 23 which are the object to be measured 21 (step S25).
- a luminance value is taken as an example of information used to determine the area of the teeth 22 and the gums 23, but when a color CCD is used as the image sensor 18, saturation or hue may be substituted for the luminance value. Specific color signals may be used.
- a threshold value of the luminance value used to determine the area of the teeth 22 and the gums 23 is calculated (step S26).
- the image used to calculate the threshold may be either a G signal image or an R signal image. The method of setting this threshold will be described in detail later.
- each pixel in the G signal image and the R signal image is compared with the calculated threshold value for area determination, and the pixel whose luminance value is less than the threshold value is It determines that it is a corresponding pixel, and determines that a pixel whose luminance value is equal to or greater than a threshold value is a pixel that corresponds to the area of the tooth 22. Based on these determination results, each pixel in the G signal image and the R signal image is divided into a pixel group corresponding to the area of the tooth 22 and a pixel group corresponding to the gingiva 23 (step S27).
- the area signal GA of the gum 23 is added to the data of the pixel group determined to correspond to the area of the gum 23 in step S27 (step S28).
- the gums 23 are clearly displayed in the R signal image as described above, it is preferable to apply the area signal GA only to the pixel group of the R signal image corresponding to the area of the gums 23.
- step S29 histogram data of the luminance value of the pixel group corresponding to the region of the gum 23 is acquired.
- step S30 gradation correction is appropriately performed on the pixel group corresponding to the region of the gum 23 (step S30).
- the histogram data of the luminance value of the pixel group corresponding to the region of the gum 23 is concentrated in the low gradation portion. For this reason, it is preferable to perform gradation correction so as to increase the luminance value of the pixel group corresponding to the region of the gingiva 23 (step S30).
- the area signal DA of the tooth 22 is added to the data of the pixel group determined to correspond to the area of the tooth 22 in step S27 (step S31).
- the teeth 22 are clearly displayed in the G signal image as described above, it is preferable to apply the area signal DA only to the pixel group of the G signal image corresponding to the area of the teeth 22.
- step S32 histogram data of the luminance value of the pixel group corresponding to the area of the tooth 22 is acquired.
- gradation correction is appropriately performed on the pixel group corresponding to the area of the tooth 22.
- the histogram data of the luminance values of the pixel group corresponding to the area of the teeth 22 is concentrated in the high gradation part. For this reason, it is not necessary to perform tone correction to increase the luminance value of the pixel group corresponding to the area of the teeth 22.
- step S34 the data of the pixel group corresponding to the area of the gum 23 to which the area signal GA is applied and the data of the pixel group corresponding to the area of the tooth 22 to which the area signal DA is applied.
- the image combining process is completed by carrying out the steps S21 to S34.
- the G signal image includes images of the teeth 22 and gums 23 and their peripheral area (here, space).
- FIG. 11A is a diagram showing a G signal image.
- FIG. 11B is a histogram of luminance values in the G signal image of FIG. 11A.
- FIG. 11C is a graph in which the histogram of FIG. 11B is connected by a smooth line using the method of least squares.
- the vertical axis indicates the frequency of the luminance value
- the horizontal axis indicates the gradation.
- the peak gradation 33 is the peak gradation of the tooth 22
- the peak gradation 34 is the peak gradation of the gingiva 23
- the peak gradation 35 is the peak gradation of the peripheral area.
- the purpose is to set a threshold between the area of the tooth 22 and the area of the gum 23, for example, the midpoint between the peak tone 33 of the tooth 22 and the peak tone 34 of the gum 23 is used as the threshold.
- the threshold is 100 tones.
- the middle point of the peak gradation 33 and the peak gradation 34 is used as a threshold here, this invention is not limited to this.
- this invention may be set in a range R1 between the gray level which is a half frequency of the peak gray level 33 and the gray level which is a half frequency of the peak gray level 34.
- the two LED light sources 24 and 25 having different wavelengths are provided, clear images of both the area of the teeth 22 and the area of the gums 23 can be obtained. You can get it. Thereby, the inside of the oral cavity can be measured accurately. At this time, it is not necessary to spray the metal powder in the oral cavity.
- the present invention is not limited to the first embodiment, and can be implemented in other various modes.
- the image processing unit 40 may be built in the oral scanner 1A.
- the oral scanner 1A may be provided with a data extracting mechanism 81 for extracting data of three-dimensional coordinates of the object 2 measured by the oral scanner 1A to the outside.
- the data extracting mechanism 81 is, for example, a cable connector, a wireless communication (wireless LAN) transmitting / receiving unit, and a slot of an SD memory.
- the small-sized display unit 82 capable of changing the angle is provided in the oral scanner 1A, the necessity of connecting the oral scanner 1A to the external device 20 provided with the display unit 50 can be eliminated. The convenience can be further improved.
- FIG. 13 is a flowchart of an image combining process of the intra-oral measurement system according to the second embodiment of the present invention.
- the intra-oral measurement system according to the second embodiment differs from the intra-oral measurement system according to the first embodiment in that steps S41 to S44 in place of steps S25 to S27 shown in FIG. Is the point to do.
- Steps S21 to S24 and steps S28 to S34 in FIG. 13 are the same as those in the first embodiment described with reference to FIG. 10, and thus redundant description will be omitted, and only steps S41 to S44 will be described.
- a comparison area frame is set in the G signal image and the R signal image.
- the comparison area frame includes the boundary between the teeth 22 and the gums 23 and is set so that the teeth 22 and the gums 23 have the same area. Further, the comparison area frame is set at mutually corresponding positions of the G signal image and the R signal image.
- step S42 the luminance value of each pixel located in the comparison area frame of the G signal image and the R signal image is extracted.
- step S43 an average value of the luminance values of each pixel in the extracted comparison area frame (hereinafter, referred to as comparison area average luminance value) is calculated.
- the image used to calculate the comparison area average luminance value may be either the G signal image or the R signal image. In the second embodiment, this comparison area average luminance value is used as a threshold.
- step S44 for each pixel in the comparison area frame, the luminance value of the pixel is compared with the calculated comparison area average luminance value, and the pixel whose luminance value is less than the comparison area average luminance value is gummed A pixel corresponding to the area 23 is determined, and a pixel having a luminance value equal to or greater than the comparison area average luminance value is determined as a pixel corresponding to the area of the tooth 22.
- each pixel in the comparison area frame of the G signal image and each pixel in the comparison area frame of the R signal image are a pixel group corresponding to the area of the teeth 22 and a pixel group corresponding to the gingiva 23 Divide into and.
- the division of the area of the teeth 22 and the area of the gums 23 is performed only in the vicinity of the boundary between the teeth 22 and the gums 23. That is, in regions other than the vicinity of the boundary, it is clear whether the G signal image or the R signal image is clearly displayed. Therefore, the teeth 22 or a part of the pixels of the G signal image and the R signal image It is determined which of the regions of the gums 23 it corresponds to. As a result, it is possible to shorten the time of the image combining process.
- FIG. 14 is an explanatory view showing a schematic configuration of a light projecting unit of the intra-oral measurement system according to the third embodiment of the present invention.
- the intra-oral measurement system according to the third embodiment is different from the intra-oral measurement system according to the first embodiment in that a light projecting unit 10A is provided instead of the light projecting unit 10.
- a light projecting unit 10A is provided instead of the light projecting unit 10.
- the second embodiment is the same as the first embodiment, the overlapping description is omitted, and only the difference will be described.
- the light projecting unit 10A includes one white light source 36, and an R (red) wavelength filter 38 and a G (green) wavelength filter 39 movable on the optical axis of the white light source 36.
- the R wavelength filter 38 converts light emitted from the white light source 36 into light having a wavelength of 500 to 565 nm
- the G wavelength filter 39 generates light emitted from the white light source 36 to a wavelength of 625 to 740 nm. It is converted to light.
- the R wavelength filter 38 and the G wavelength filter 39 are disposed on the rotary disk 37, and are configured to be able to move on the optical axis of the white light source 36 by rotating the rotary disk 37.
- the number of light sources can be reduced to one.
- light projection part 10A can be designed comparatively compactly.
- the wavelength of the light emitted from the light emitting unit 10A can be switched at high speed.
- the rotary disk 37 is provided with the two wavelength filters 38 and 39, but the present invention is not limited to this, and three or more wavelength filters may be provided.
- the present invention is not limited to this.
- resin dentures plastic dentures
- metal dentures by appropriately setting the surface reflectance and the gradation of luminance. This allows the individual patient to know the current condition such as dentures.
- plaque and tartar can be determined by appropriately setting the surface reflectance and the gradation of luminance. In this case, it is considered that tartar prophylaxis can be performed even at home by regularly checking the presence or absence of plaque and tartar.
- the intra-oral measurement apparatus and the intra-oral measurement system according to the present invention can accurately measure the shape of an object to be measured in the oral cavity such as teeth and gums having different surface reflectances of light. It can be applied to the application of measuring the compatibility of different dental prostheses directly in the oral cavity.
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Abstract
Description
図15において、従来の光学三次元カメラは、外装ケース101の内部に、光源102と、パターンマスク103と、絞り104、105と、プリズム106と、CCD等のイメージセンサー107とを備えている。
)、及び非特許文献2(武田友孝、「歯肉の分光放射測定法による色彩学的研究-若年者の前歯部について-」、日本補綴歯科学会雑誌、社団法人日本補綴歯科学会、1987年4月1日、第31巻、第2号、pp.363-370)に記載されている。
本発明の第1実施形態によれば、口腔内の少なくとも歯を含む被測定物に向けて少なくとも2つの波長の異なる光を同一光軸で照射する投光部と、
前記被測定物で反射された光を受光し撮像する撮像部と、
を備える、口腔内測定装置。
前記被測定物で反射された光を受光し撮像する撮像部と、
前記撮像部が撮像した前記波長が異なる複数の画像を合成し、当該合成した画像を三次元座標に変換して前記被測定物の三次元画像を得る画像処理部と、
を備える、口腔内測定システムを提供する。
以下、本発明の実施の形態については、図面を参照しながら説明する。
図1は、本発明の実施の形態1にかかる口腔内測定装置(以下、オーラルスキャナという)を有する口腔内測定システムの概略構成を示す説明図である。
まず、二次元画像処理部43が、画像記憶部42に保存された前記画像データの縞パターンのコントラストを改善する為に、前記画像データに対してノイズ除去、階調補正、ガンマ補正等の二次元画像処理を行う(ステップS4)。
三次元画像判定部46が、前記低精度三次元画像が良好でないと判定したとき、前記ステップS1に戻る。
また、前記ステップS6の低精度三次元画像の良否の判定は、表示部50に低精度三次元画像を表示して歯科医が行うようにしてもよい。すなわち、この場合、歯科医は、自分の目で見た被測定物21の形状と、低精度三次元画像の被測定物21の形状とを見比べることで、低精度三次元画像の良否の判定を行う。
図13は、本発明の実施の形態2にかかる口腔内測定システムの画像合成処理のフローチャートである。本実施の形態2にかかる口腔内測定システムが前記第1実施形態にかかる口腔内測定システムと異なる点は、画像合成処理のフローにおいて、図10に示すステップS25~S27に代えてステップS41~S44を行う点である。図13において、ステップS21~S24、S28~S34は、図10を用いて説明した前記実施の形態1と同様であるため、重複する説明は省略し、ステップS41~S44についてのみ説明する。
ステップS43では、前記抽出した比較領域枠内の各画素の輝度値の平均値(以下、比較領域平均輝度値という)を算出する。なお、このとき、比較領域平均輝度値の算出に用いる画像は、前記G信号画像及びR信号画像のいずれか一方でよい。本実施の形態2においては、この比較領域平均輝度値を閾値とする。
図14は、本発明の実施の形態3にかかる口腔内測定システムの投光部の概略構成を示す説明図である。本実施の形態3にかかる口腔内測定システムが前記第1実施形態にかかる口腔内測定システムと異なる点は、投光部10に代えて投光部10Aを備えている点である。投光部10A以外は、前記実施の形態1と同様であるため、重複する説明は省略し、相違点についてのみ説明する。
Claims (8)
- 口腔内の少なくとも歯を含む被測定物に向けて少なくとも2つの波長の異なる光を同一光軸で照射する投光部と、
前記被測定物で反射した光を受光し撮像する撮像部と、
を備える、口腔内測定装置。 - 前記投光部は、少なくとも2つの波長の異なるLED光源を備えている、請求項1に記載の口腔内測定装置。
- 前記投光部は、白色光源と、前記白色光源の光軸上に移動可能な少なくとも2つの波長の異なる波長フィルタと、を備えている、請求項1に記載の口腔内測定装置。
- 前記投光部は、コード化された縞パターンの光を照射するものである、請求項1に記載の口腔内測定装置。
- 前記波長が異なる光は、500~565nmの波長の光と、625~740nmの波長の光とを含む、請求項1に記載の口腔内測定装置。
- 前記撮像部が撮像した前記異なる波長の光による複数の画像を合成し、当該合成した画像を三次元座標に変換して前記被測定物の三次元画像を得る画像処理部を備える、請求項1に記載の口腔内測定装置。
- 前記画像処理部は、前記異なる波長の光による複数の画像を、当該画像の各画素の輝度情報に基づいて合成する、請求項6に記載の口腔内測定装置。
- 口腔内の少なくとも歯を含む被測定物に向けて少なくとも2つの波長の異なる光を同一光軸で照射する投光部と、
前記被測定物で反射された光を受光し撮像する撮像部と、
前記撮像部が撮像した前記波長が異なる複数の画像を合成し、当該合成した画像を三次元座標に変換して前記被測定物の三次元画像を得る画像処理部と、
を備える、口腔内測定システム。
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US9436868B2 (en) | 2010-09-10 | 2016-09-06 | Dimensional Photonics International, Inc. | Object classification for measured three-dimensional object scenes |
JP2016529959A (ja) * | 2013-07-12 | 2016-09-29 | ケアストリーム ヘルス インク | 歯牙表面撮像装置のためのビデオベースの自動取得 |
WO2017070928A1 (en) * | 2015-10-30 | 2017-05-04 | Carestream Health, Inc. | Target with features for 3-d scanner calibration |
JP2017533000A (ja) * | 2014-09-16 | 2017-11-09 | ケアストリーム ヘルス インク | レーザ投影を用いる歯科用表面撮像装置 |
WO2018042829A1 (ja) * | 2016-08-30 | 2018-03-08 | オムロンヘルスケア株式会社 | 歯ブラシおよびシステム |
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Families Citing this family (22)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8570530B2 (en) * | 2009-06-03 | 2013-10-29 | Carestream Health, Inc. | Apparatus for dental surface shape and shade imaging |
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WO2018012862A1 (ko) * | 2016-07-13 | 2018-01-18 | 문정본 | 3차원 스캐너와 이를 이용한 인공물가공장치 |
US10507087B2 (en) * | 2016-07-27 | 2019-12-17 | Align Technology, Inc. | Methods and apparatuses for forming a three-dimensional volumetric model of a subject's teeth |
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US11648095B2 (en) | 2017-08-10 | 2023-05-16 | D4D Technologies, Llc | Intra-oral scanning device |
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JP2023553670A (ja) * | 2020-12-16 | 2023-12-25 | コーニンクレッカ フィリップス エヌ ヴェ | 歯の硬質物質の厚さの推定 |
EP4014838A1 (en) * | 2020-12-16 | 2022-06-22 | Koninklijke Philips N.V. | Detecting distance of a probe to pulp of a tooth |
KR102341890B1 (ko) * | 2021-02-01 | 2021-12-20 | 전승현 | 구강 스캐너 |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH11183145A (ja) * | 1997-10-15 | 1999-07-09 | Yuusuke Nonomura | 3次元観察装置 |
JP2001505993A (ja) * | 1996-09-13 | 2001-05-08 | オーラメトリクス ゲーエムベーハー | 三次元物体計測方法および装置 |
JP2004089239A (ja) * | 2002-08-29 | 2004-03-25 | Matsushita Electric Ind Co Ltd | 口腔組織観察装置 |
JP2007296249A (ja) * | 2006-05-03 | 2007-11-15 | Microdent:Kk | 歯科疾患確定装置 |
Family Cites Families (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2848857B2 (ja) * | 1989-08-14 | 1999-01-20 | 株式会社モリタ製作所 | 光診断装置 |
JP2879003B2 (ja) * | 1995-11-16 | 1999-04-05 | 株式会社生体光情報研究所 | 画像計測装置 |
US5688118A (en) * | 1995-12-27 | 1997-11-18 | Denx Ltd. | Image sound and feeling simulation system for dentistry |
US6179611B1 (en) * | 1999-01-22 | 2001-01-30 | The Regents Of The University Of California | Dental optical coherence domain reflectometry explorer |
US6244863B1 (en) * | 2000-03-10 | 2001-06-12 | Andrew H. Rawicz | Dental color comparator scope |
FR2825260B1 (fr) * | 2001-06-01 | 2004-08-20 | Centre Nat Rech Scient | Procede et dispositif de detection de caries dentaires |
JP2005110828A (ja) * | 2003-10-06 | 2005-04-28 | Omega Wave Kk | 歯科用診断装置 |
CA2600938A1 (en) * | 2004-03-24 | 2005-10-06 | Andre Hoffmann | Identification, verification, and recognition method and system |
ATE383817T1 (de) * | 2004-06-17 | 2008-02-15 | Cadent Ltd | Verfahren zum bereitstellen von daten im zusammenhang mit der mundhöhle |
DE112004003014T5 (de) * | 2004-11-15 | 2008-01-03 | Kabushiki Kaisha Morita Tokyo Seisakusho | Optische Zahndiagnosevorrichtung |
US9111372B2 (en) * | 2006-08-11 | 2015-08-18 | Visionary Technologies, Inc. | System and method for object identification and anomaly detection |
US8270689B2 (en) * | 2006-09-12 | 2012-09-18 | Carestream Health, Inc. | Apparatus for caries detection |
US20080062429A1 (en) * | 2006-09-12 | 2008-03-13 | Rongguang Liang | Low coherence dental oct imaging |
US7702139B2 (en) * | 2006-10-13 | 2010-04-20 | Carestream Health, Inc. | Apparatus for caries detection |
US9539062B2 (en) * | 2006-10-16 | 2017-01-10 | Natural Dental Implants, Ag | Methods of designing and manufacturing customized dental prosthesis for periodontal or osseointegration and related systems |
US20080118886A1 (en) * | 2006-11-21 | 2008-05-22 | Rongguang Liang | Apparatus for dental oct imaging |
DE102007012584A1 (de) * | 2007-03-13 | 2008-09-18 | Paul Weigl | Verfahren zur Kontrolle einer Präparation eines präparierten Zahns mit CAD-Verfahren |
US8377500B2 (en) * | 2008-01-29 | 2013-02-19 | Uriel Yarovesky | Process for making a dental restoration and resultant apparatus |
US20100297585A1 (en) * | 2008-01-29 | 2010-11-25 | Uriel Yarovesky | Process for making a dental restoration and resultant apparatus |
-
2009
- 2009-04-07 US US12/675,183 patent/US20100253773A1/en not_active Abandoned
- 2009-04-07 JP JP2009536548A patent/JP5276006B2/ja not_active Expired - Fee Related
- 2009-04-07 WO PCT/JP2009/001603 patent/WO2009139110A1/ja active Application Filing
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2001505993A (ja) * | 1996-09-13 | 2001-05-08 | オーラメトリクス ゲーエムベーハー | 三次元物体計測方法および装置 |
JPH11183145A (ja) * | 1997-10-15 | 1999-07-09 | Yuusuke Nonomura | 3次元観察装置 |
JP2004089239A (ja) * | 2002-08-29 | 2004-03-25 | Matsushita Electric Ind Co Ltd | 口腔組織観察装置 |
JP2007296249A (ja) * | 2006-05-03 | 2007-11-15 | Microdent:Kk | 歯科疾患確定装置 |
Cited By (24)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2013512695A (ja) * | 2009-12-04 | 2013-04-18 | ヘレーウス クルツァー ゲゼルシャフト ミット ベシュレンクテル ハフツング | Cad/camによる個々の義歯の製造およびデジタル印象データからのラピッドマニュファクチャリング/ラピッドプロトタイピング |
JP2013515546A (ja) * | 2009-12-23 | 2013-05-09 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | 歯のホワイトニング物質に対する軟組織の保護のためのシステム |
US9436868B2 (en) | 2010-09-10 | 2016-09-06 | Dimensional Photonics International, Inc. | Object classification for measured three-dimensional object scenes |
EP2428913B1 (en) * | 2010-09-10 | 2018-07-25 | Dental Imaging Technologies Corporation | Object classification for measured three-dimensional object scenes |
JP2014518378A (ja) * | 2011-06-15 | 2014-07-28 | シロナ・デンタル・システムズ・ゲゼルシャフト・ミット・ベシュレンクテル・ハフツング | 歯科対象物の3次元光学測定のための方法 |
WO2013121605A1 (ja) * | 2012-02-15 | 2013-08-22 | メディア株式会社 | 口腔内歯列撮影装置 |
KR101176770B1 (ko) * | 2012-03-22 | 2012-08-23 | 추상완 | 치과용 3차원 스캐너 및 이를 이용한 스캐닝 방법 |
WO2013141502A1 (ko) * | 2012-03-22 | 2013-09-26 | Choo Sang Wan | 치과용 3차원 스캐너 및 이를 이용한 스캐닝 방법 |
JP2016508753A (ja) * | 2012-12-21 | 2016-03-24 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | 歯科衛生検出装置における光検出器を用いた歯肉検出 |
JP2016529959A (ja) * | 2013-07-12 | 2016-09-29 | ケアストリーム ヘルス インク | 歯牙表面撮像装置のためのビデオベースの自動取得 |
US10271720B2 (en) | 2014-03-26 | 2019-04-30 | 3M Innovative Properties Company | Intraoral imaging illumination apparatus |
JP2017533000A (ja) * | 2014-09-16 | 2017-11-09 | ケアストリーム ヘルス インク | レーザ投影を用いる歯科用表面撮像装置 |
US11382559B2 (en) | 2014-09-16 | 2022-07-12 | Carestream Health, Inc. | Dental surface imaging apparatus using laser projection |
WO2017070928A1 (en) * | 2015-10-30 | 2017-05-04 | Carestream Health, Inc. | Target with features for 3-d scanner calibration |
US11333490B2 (en) | 2015-10-30 | 2022-05-17 | Carestream Dental Technology Topco Limited | Target with features for 3-D scanner calibration |
CN109561820A (zh) * | 2016-05-10 | 2019-04-02 | 神原正树 | 牙龈诊断辅助装置和牙龈诊断辅助系统 |
JP2018033591A (ja) * | 2016-08-30 | 2018-03-08 | オムロンヘルスケア株式会社 | 歯ブラシおよびシステム |
CN109640738B (zh) * | 2016-08-30 | 2021-11-26 | 欧姆龙健康医疗事业株式会社 | 牙刷和系统 |
US11311363B2 (en) | 2016-08-30 | 2022-04-26 | Omron Healthcare Co., Ltd. | Toothbrush and system |
CN109640738A (zh) * | 2016-08-30 | 2019-04-16 | 欧姆龙健康医疗事业株式会社 | 牙刷和系统 |
WO2018042829A1 (ja) * | 2016-08-30 | 2018-03-08 | オムロンヘルスケア株式会社 | 歯ブラシおよびシステム |
US10835352B2 (en) | 2018-03-19 | 2020-11-17 | 3D Imaging and Simulation Corp. Americas | Intraoral scanner and computing system for capturing images and generating three-dimensional models |
JP7484641B2 (ja) | 2020-10-06 | 2024-05-16 | コニカミノルタ株式会社 | 口腔内測定装置 |
JP7394330B2 (ja) | 2021-02-22 | 2023-12-08 | パナソニックIpマネジメント株式会社 | 口腔内カメラシステム及び撮影動作判定方法 |
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US20100253773A1 (en) | 2010-10-07 |
JP5276006B2 (ja) | 2013-08-28 |
JPWO2009139110A1 (ja) | 2011-09-15 |
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