Image forming device

Description: TECHNICAL FIELD [Detailed description of the invention]

[Technical field to which the invention belongs]

The present invention relates to an image generator, and more specifically, a radiation image, an autoradiography image, a chemiluminescence image, and an electron microscope image of a subject recorded on a luminescent phosphor layer of an accumulative phosphor sheet. And the radiation diffraction image can be read to generate an image, and the image recorded on a material capable of transmitting light can be read to generate an image, and the fluorescence fluorescence of the accumulative phosphor sheet can be generated. It relates to an image generator capable of erasing residual radiation energy, light energy, and electron beam energy while being accumulated in the body layer.

[Conventional technology]

When radiation is irradiated, it absorbs the energy of the radiation, stores and records it, and then when excited using electromagnetic waves in a specific wavelength range, the amount of light shines according to the amount of energy of the irradiated radiation. A brilliant phosphor having the property of emitting light is used as a radiation detection material, and the energy of the radiation transmitted through the subject is radiated contained in the brilliant phosphor layer formed on the accumulating phosphor sheet. Accumulated and recorded in the luminescent phosphor, and then the brilliant phosphor layer is scanned by electromagnetic waves to excite the brilliant phosphor, and the brilliant light emitted from the brilliant phosphor is photoelectric. A radiological diagnostic system is known that is configured to detect and generate a digital image signal, perform image processing, and generate a radiographic image on a display means such as a CRT or a recording material such as a photographic film. (For example, Japanese Patent Application Laid-Open Nos. 55-12429, 55-116340, 55-163472, 56-11395, 56-104645, etc.). Further, a similar luminescent phosphor is used as a radiation detection material, and after administering a substance to which a radioactive label is given to an organism, the organism or a part of the tissue of the organism is used as a sample. By superimposing the sample on the accumulative phosphor sheet on which the extinct phosphor layer is formed for a certain period of time, the radiation energy is accumulated and recorded in the accumulative phosphor contained in the extinct phosphor layer. After that, the luminescent phosphor layer is scanned by electromagnetic waves to excite the luminescent phosphor, and the luminescent light emitted from the luminescent phosphor is photoelectrically detected to obtain a digital image signal. There are known autoradiography systems that are configured to generate, perform image processing, and generate images on display means such as CRTs or on recording materials such as photographic films (eg, Tokushu 1-). 60784, 1-60782, 4-3952, etc.). Furthermore, when light is irradiated, the energy is absorbed, stored and recorded, and then when excited using electromagnetic waves in a specific wavelength range, the amount of light shines according to the amount of energy of the irradiated light. Characteristics that emit light 197A etc. ). Further, when an electron beam or radiation is irradiated, the energy of the electron beam or radiation is absorbed, stored and recorded, and then excited by using an electromagnetic wave in a specific wavelength range, the irradiated electron beam or radiation is generated. A brilliant phosphor having the property of emitting brilliant light in an amount of light corresponding to the amount of energy of the above is used as an electron beam or radiation detection material, and a metal or non-metal sample is irradiated with the electron beam to diffract the sample. Detection by an electron microscope that detects images or transmission images, performs element analysis, sample composition analysis, sample structure analysis, etc., or irradiates biological tissue with electron beams to detect images of biological tissue There are known systems and radiation diffraction image detection systems that irradiate a sample with radiation, detect the obtained radiation diffraction image, and perform structural analysis of the sample (for example, Japanese Patent Application Laid-Open No. 61-51738). , JP-A-61-93538, JP-A-59-15843, etc.). Unlike the case of using a photographic film, a system using these accumulative phosphor sheets as an image detection material not only does not require a chemical process called development processing, but also performs image processing on the obtained image data. This has the advantage that the image can be reproduced or quantitative analysis by a computer can be performed as desired.

[Problems to be Solved by the Invention]

In the image generator used in these systems using the accumulative phosphor sheet, the exhilarating phosphor layer formed on the accumulative phosphor sheet is irradiated with excitation light from an excitation light source to be extinct. The luminescent phosphor contained in the luminescent phosphor layer is excited, and the luminescent light emitted from the luminescent phosphor is photoelectrically detected by a photodetector to generate image data to generate image data of the subject. It is configured to generate radiographic images, autoradiography images, chemiluminescent images, electromicroscopic images, radiofluorescence images, and the like. An image generator for a system using such an accumulative phosphor sheet is an image recorded on a material capable of transmitting light, such as an autoradiography image recorded on a developed X-ray film, as in the conventional case. If such an image can be read, the usefulness of the image generator can be further improved, which is preferable, and development of such an image generator has been desired. Further, in these systems using the accumulative phosphor sheet, the accumulative phosphor sheet can be repeatedly used, but for that purpose, after reading the image, the luminescent phosphor of the accumulative phosphor sheet can be used. It is necessary to eliminate the remaining radiation energy, light energy, and electron beam energy while remaining accumulated in the layer, and conventionally, it remains by using an energy erasing device separate from the image reading device. The radiation energy, light energy, and electron beam energy were erased. However, in this way, when erasing the remaining radiation energy, light energy, and electron beam energy by using an energy erasing device separate from the image reading device, there is a problem that a large space is required. there were. Therefore, the present invention reads a radiation image, an autoradiography image, a chemiluminescent image, an electron microscope image, and a radiation diffraction image of a subject recorded on the luminescent phosphor layer of the accumulative phosphor sheet to generate an image. It is possible, and further, the image recorded on a light-transmissive material can be read to generate an image, and remains accumulated in the luminescent phosphor layer of the accumulative phosphor sheet. Radiation energy

[Means for solving problems]

An object of the present invention is a group consisting of a radiation image, a chemical emission image, and an electron beam image recorded on the brilliant phosphor layer by exciting the brilliant phosphor contained in the brilliant phosphor layer. At least one excitation light source that emits excitation light for reading an image selected from, at least one light source that emits light for returning the brilliant phosphor layer to the ground state, and the brilliant phosphor layer. The stage on which the accumulating phosphor sheet can be placed and the excitation light emitted from at least one excitation light source are irradiated to excite the brilliant phosphor layer, and the emitted brilliant light is emitted. An image generator including a light detector for photoelectric detection, wherein the light detector is arranged at a position where light emitted from at least one light source can be received via the stage. A visible image is recorded by the at least one light source, and the light transmitted through a material through which light can be transmitted is photoelectrically detected by the light detector, so that the light is recorded in the material through which the light can be transmitted. This is achieved by an image generator characterized in that the image is configured to emit light of a reproducible wavelength. According to the present invention, the image generator excites the brilliant phosphor contained in the brilliant phosphor layer, and records a radiation image, a chemical emission image, and an electron beam image in the brilliant phosphor layer. At least one excitation light source that emits excitation light to read an image selected from the group consisting of, and at least one light source that emits light to return the brilliant phosphor layer to the basal state, and the brilliant phosphor layer. The brilliant phosphor layer is excited by being irradiated with the excitation light emitted from at least one excitation light source and the stage on which the accumulative phosphor sheet can be placed, and the emitted brilliant light is photoelectric. An image generator including a light detector that detects light, in which the light detector is arranged at a position where light emitted from at least one light source can be received via a stage, and the light is at least one light source. However, a visible image is recorded, and the light transmitted through the light-transmissive material is photoelectrically detected by the light detector, so that the image recorded on the light-transmissible material can be reproduced. Constructed to emit light Therefore, the luminescent phosphor layer of the accumulative phosphor sheet is irradiated with excitation light for reading the image recorded on the luminescent phosphor layer emitted from at least one excitation light source. By exciting the brilliant phosphor layer and photoelectrically detecting the brilliant light emitted from the brilliant phosphor layer with a photodetector, the brilliant phosphor layer of the accumulative phosphor sheet can be obtained. Not only can the recorded radiation image, chemical emission image, or electron beam image be read to generate an image, but a transmissive manuscript made of a material capable of transmitting the light on which the visible image is recorded is placed on the stage. By irradiating the transmitted document with light emitted from at least one light source to return the brilliant phosphor layer to the ground state, and detecting the light transmitted through the transmitted document photoelectrically by an optical detector. , The image recorded on the transmissive material can be reproduced, and therefore the usefulness of the image generator can be improved, and the radiation energy, the light energy or the electron beam energy is accumulated and remains. By irradiating the brilliant phosphor layer with light emitted from at least one light source to return the brilliant phosphor layer to the basal state, the brilliant phosphor of the accumulating phosphor sheet is obtained. Accumulated in the layer, the remaining radiation energy, light energy or electron beam energy can be released and erased, thus eliminating the radiation energy, light energy or electron beam energy separately from the image generator. It is not necessary to have a device, and the installation space can be significantly reduced. In a preferred embodiment of the present invention, the image generator further excites the luminescent phosphor contained in the luminescent phosphor layer emitted from the at least one excitation source, and the luminescent fluorescence. A scanning mechanism that scans on the luminescent phosphor layer of the accumulative phosphor sheet with excitation light for reading an image selected from the group consisting of a radiographic image, a chemiluminescent image, and an electron beam image recorded on the body layer. And an optical system that guides the fluorescence emitted from the luminescent phosphor layer to the photodetector. According to a preferred embodiment of the present invention The image generator further excites the luminescent phosphor contained in the luminescent phosphor layer emitted from at least one excitation light source, and the radiographic image and chemiluminescence recorded on the luminescent phosphor layer. The excitation light for reading an image selected from the group consisting of a luminescent image and an electron beam image emits a scanning mechanism that scans on the luminescent phosphor layer of the accumulative phosphor sheet and the luminescent phosphor layer. Since it is equipped with an optical system that guides the fluorescence to the light detector, it is possible to generate a radiographic image, a chemiluminescent image, or an electron beam image with high resolution. In a more preferred embodiment of the invention, the scanning mechanism moves the optical system relative to the stage into a luminescent phosphor layer emitted from the at least one excitation light source. The bright light used to excite the contained bright phosphor and read an image selected from the group consisting of a radiation image, a chemiluminescent image, and an electron beam image recorded on the bright phosphor layer. It is configured to scan over the exhaustive phosphor layer. In a more preferred embodiment of the invention, the image generator further synchronizes the movement of the optical system with at least one light source that emits the light to return the brilliant phosphor layer to the ground state. , The sub-scanning means for moving in the sub-scanning direction is provided. According to a more preferred embodiment of the invention, the image generator further synchronizes at least one light source, which emits light to return the brilliant phosphor layer to the ground state, with the movement of the optical system. Since the sub-scanning means for moving in the scanning direction is provided, it is possible to reproduce an image recorded on a transparent original that transmits light with high resolution. In a more preferred embodiment of the invention, the stage comprises a transparent substrate on which the accumulative phosphor sheet or a light-transmissible material on which the visible image is recorded can be placed, wherein the optical system comprises. Along with being arranged below the transparent substrate, at least one light source that emits the light for returning the luminescent phosphor layer to the basal state is arranged above the transparent substrate. According to a more preferred embodiment of the present invention, the stage is stored. It has a stackable phosphor sheet or a transparent substrate on which a light-transmissible material on which a visible image is recorded can be placed, an optical system is arranged below the transparent substrate, and a brilliant phosphor layer. Since at least one light source that emits light to return the image to the ground state is placed above the transparent substrate, a transmissive document that transmits the light on which the image is recorded is placed on the transparent substrate of the stage. Then, the transmitted original is irradiated with light emitted from at least one light source to return the brilliant phosphor layer to the ground state, and the light transmitted through the transmitted original is guided to the optical detector using an optical system. By detecting light by photoelectric, it becomes possible to reproduce an image recorded on a transparent original that transmits light with high resolution, and radiation energy, light energy, or electrons can be reproduced on a transparent substrate of the stage. A storage phosphor sheet with the remaining luminescent phosphor layer in which linear energy is stored is placed to return the brilliant phosphor layer emitted from at least one light source to the basal state. By irradiating the brilliant phosphor layer with the light for the purpose, it is possible to release and eliminate the remaining radiation energy, light energy or electron beam energy accumulated in the brilliant phosphor layer. Become. In a more preferred embodiment of the present invention, at least one light source that emits the light for returning the brilliant phosphor layer to the ground state is configured to emit white light. In a more preferred embodiment of the present invention, at least one light source that emits the light for returning the brilliant phosphor layer to the ground state is configured by an LED array that emits white light. In a more preferred embodiment of the present invention, at least one light source that emits the light for returning the brilliant phosphor layer to the ground state is configured by a fluorescent lamp. In a more preferred embodiment of the present invention, the image generator further excites the luminescent phosphor contained in the luminescent phosphor layer emitted from the at least one excitation light source, and the luminescent phosphor is emitted. Read an image selected from the group consisting of radiographic images, chemiluminescent images and electron beam images recorded on the sex phosphor layer. An excitation light cut filter means for cutting the excitation light for taking is provided, and the excitation light cut filter means has a cut position located in the optical path of the brilliant light emitted from the brilliant phosphor layer and the brilliance. It is configured to be movable to and from the retracted position located outside the optical path of the exhaustion. According to a more preferred embodiment of the present invention, the radiation recorded in the brilliant phosphor layer by exciting the brilliant phosphor contained in the brilliant phosphor layer emitted from at least one excitation light source. Since the excitation light cut filter means for cutting the excitation light for reading the image selected from the group consisting of the image, the chemical emission image and the electron beam image is provided, the excitation light is incident on the light detector, and the radiation image, It is possible to prevent the generation of noise in the chemical emission image or the electron beam image, and further, the excitation light cut filter means is a cut located in the optical path of the brilliant light emitted from the brilliant phosphor layer. Light for returning the brilliant phosphor layer emitted from at least one light source to the basal state because it is configured to be movable between the position and the retracted position located outside the optical path of the brilliant light. By irradiating the transmitted original with light and detecting the light transmitted through the transmitted original photoelectrically with an optical detector, it is possible to generate an image having a sufficient dynamic range. In a more preferred embodiment of the invention, the photodetector is configured by a photomultiplier. In another preferred embodiment of the invention, the stage is configured transparently and at least one light source that emits the light to return the luminescent phosphor layer to the ground state is below the stage. From the group consisting of a radiation image, a chemiluminescent image, and an electron beam image recorded in the brilliant phosphor layer by exciting the brilliant phosphor contained in the brilliant phosphor layer while being arranged. The at least one excitation light source that emits excitation light to read the selected image is located above the stage. According to another preferred embodiment of the present invention, at least one that emits light to return the brilliant phosphor layer to the ground state while the stage is configured transparent. A light source is placed below the stage and excites the brilliant phosphor contained in the brilliant phosphor layer, resulting in a radiation image, a chemical emission image and an electron beam recorded on the brilliant phosphor layer. Since at least one excitation light source that emits excitation light to read an image selected from the group consisting of images is located above the stage, a visible image is recorded on the transparent stage and the light can be transmitted. A transmissive document is placed, and at least one light source irradiates the transmissive document with light for returning the brilliant phosphor layer to the ground state, and the light transmitted through the transmissive document is photoelectrically transmitted by an optical detector. By detecting, it becomes possible to reproduce the visible image recorded on the transmitted original, and the radiation energy, the light energy, or the electron beam energy is accumulated, and the remaining brilliant phosphor layer is provided. Accumulation by placing the accumulative phosphor sheet on a transparent stage and irradiating the exhilarating phosphor layer with light from at least one light source to return the extinct phosphor layer to the basal state. It is accumulated in the brilliant phosphor layer of the sex phosphor sheet, and the remaining radiation energy, light energy, or electron beam energy can be released and eliminated. In a more preferred embodiment of the invention, the light detector excites a bright phosphor contained in the bright phosphor layer emitted from at least one excitation light source in front of the light detector, wherein the light detector excites the bright phosphor contained in the bright phosphor layer. A removable excitation light cut filter that cuts the excitation light for reading an image selected from the group consisting of a radiation image, a chemiluminescent image, and an electron beam image recorded on the luminescent phosphor layer is provided. According to a more preferred embodiment of the present invention, the light detector excites a luminescent phosphor contained in a luminescent phosphor layer emitted from at least one excitation light source in front of the light detector to shine. A light detector because it is detachably equipped with an excitation light cut filter that cuts the excitation light for reading an image selected from the group consisting of a radiation image, a chemiluminescent image, and an electron beam image recorded on the sex phosphor layer. Excitation light is incident on the light, and it is noisy in the radiation image, chemiluminescence image or electron beam image. It is possible to prevent the generation of light, and with the excitation light cut filter removed, the light emitted from at least one light source to return the brilliant phosphor layer to the ground state is transmitted to the transmitted original. By irradiating and detecting the light transmitted through the transmitted original by a photodetector, it is possible to generate an image having a sufficient dynamic range. In a more preferred embodiment of the invention, the photodetector is located above the stage. In a more preferred embodiment of the present invention, the at least one light source that emits light to return the luminescent phosphor layer to the ground state is configured to emit white light. In a more preferred embodiment of the present invention, the at least one light source that emits light to return the luminescent phosphor layer to the ground state is configured in an array. In a more preferred embodiment of the invention, the image generator further comprises a diffuser on the stage. According to a more preferred embodiment of the present invention, the light that emits light for returning the brilliant phosphor layer emitted from at least one light source to the ground state is more uniformly transmitted to the transmitted original or the accumulating phosphor sheet. It is possible to irradiate the luminescent phosphor layer of the light, read a transmitted original, and reproduce a high-quality image, and at the same time, it is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet. , It becomes possible to improve the emission and erasure efficiency of the remaining radiation energy, light energy or electron beam energy. In a more preferred embodiment of the invention, the photodetector is configured by a two-dimensional area sensor. In a more preferred embodiment of the present invention, the photodetector is configured by a CCD camera and the photodetector is configured by a CCD camera. This makes it possible to generate an image having a sufficient dynamic range. In a more preferred embodiment of the invention, the photodetector is located above the stage. In a more preferred embodiment of the present invention, the at least one light source that emits light to return the luminescent phosphor layer to the ground state is configured to emit white light. In a more preferred embodiment of the present invention, the at least one light source that emits light to return the luminescent phosphor layer to the ground state is configured in an array. In a more preferred embodiment of the invention, the image generator further comprises a diffuser on the stage. According to a more preferred embodiment of the present invention, the light that emits light for returning the brilliant phosphor layer emitted from at least one light source to the ground state is more uniformly transmitted to the transmitted original or the accumulating phosphor sheet. It is possible to irradiate the luminescent phosphor layer of the light, read a transmitted original, and reproduce a high-quality image, and at the same time, it is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet. , It becomes possible to improve the emission and erasure efficiency of the remaining radiation energy, light energy or electron beam energy. In a more preferred embodiment of the invention, the photodetector is configured by a two-dimensional area sensor. In a more preferred embodiment of the present invention, the photodetector is configured by a CCD camera and the photodetector is configured by a CCD camera. This makes it possible to generate an image having a sufficient dynamic range. In a more preferred embodiment of the invention, the photodetector is located above the stage. In a more preferred embodiment of the present invention, the at least one light source that emits light to return the luminescent phosphor layer to the ground state is configured to emit white light. In a more preferred embodiment of the present invention, the at least one light source that emits light to return the luminescent phosphor layer to the ground state is configured in an array. In a more preferred embodiment of the invention, the image generator further comprises a diffuser on the stage. According to a more preferred embodiment of the present invention, the light that emits light for returning the brilliant phosphor layer emitted from at least one light source to the ground state is more uniformly transmitted to the transmitted original or the accumulating phosphor sheet. It is possible to irradiate the luminescent phosphor layer of the light, read a transmitted original, and reproduce a high-quality image, and at the same time, it is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet. , It becomes possible to improve the emission and erasure efficiency of the remaining radiation energy, light energy or electron beam energy. In a more preferred embodiment of the invention, the photodetector is configured by a two-dimensional area sensor. In a more preferred embodiment of the present invention, the photodetector is configured by a CCD camera and the photodetector is configured by a CCD camera. It is configured in. In a more preferred embodiment of the invention, the image generator further comprises a diffuser on the stage. According to a more preferred embodiment of the present invention, the light that emits light for returning the brilliant phosphor layer emitted from at least one light source to the ground state is more uniformly transmitted to the transmitted original or the accumulating phosphor sheet. It is possible to irradiate the luminescent phosphor layer of the light, read a transmitted original, and reproduce a high-quality image, and at the same time, it is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet. , It becomes possible to improve the emission and erasure efficiency of the remaining radiation energy, light energy or electron beam energy. In a more preferred embodiment of the invention, the photodetector is configured by a two-dimensional area sensor. In a more preferred embodiment of the present invention, the photodetector is configured by a CCD camera and the photodetector is configured by a CCD camera. It is configured in. In a more preferred embodiment of the invention, the image generator further comprises a diffuser on the stage. According to a more preferred embodiment of the present invention, the light that emits light for returning the brilliant phosphor layer emitted from at least one light source to the ground state is more uniformly transmitted to the transmitted original or the accumulating phosphor sheet. It is possible to irradiate the luminescent phosphor layer of the light, read a transmitted original, and reproduce a high-quality image, and at the same time, it is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet. , It becomes possible to improve the emission and erasure efficiency of the remaining radiation energy, light energy or electron beam energy. In a more preferred embodiment of the invention, the photodetector is configured by a two-dimensional area sensor. In a more preferred embodiment of the present invention, the photodetector is configured by a CCD camera and the photodetector is configured by a CCD camera.

BEST MODE FOR CARRYING OUT THE INVENTION

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings. FIG. 1 is a schematic perspective view of an image generator according to a preferred embodiment of the present invention, and FIG. 2 is a schematic perspective view showing details of the vicinity of a photomultiplier. As shown in FIG. 1, the image generator according to this embodiment has a first laser excitation light source 1 that emits a laser beam 4 having a wavelength of 640 nm and a second laser excitation source 1 that emits a laser beam 4 having a wavelength of 532 nm. It includes a light source 2 and a third laser excitation light source 3 that emits a laser beam 4 having a wavelength of 473 nm. In this embodiment, the first laser excitation light source 1 is composed of a semiconductor laser light source, and both the second laser excitation light source 2 and the third laser excitation light source 3 generate a second harmonic (Second Harmonic). Generation) It is composed of elements. The laser beam 4 generated by the first laser excitation light source 1 is made into parallel light by the collimator lens 5 and then reflected by the mirror 6. In the optical path of the laser beam 4 generated by the first laser excitation light source 1, the first dichroic mirror 7 that transmits the laser beam 4 of 640 nm and reflects the light of the wavelength of 532 nm and the light of the wavelength of 532 nm or more are transmitted. A second dichroic mirror 8 that transmits and reflects light with a wavelength of 473 nm is provided, and the laser light 4 generated by the first laser excitation light source 1 and reflected by the mirror 6 is the first dichroic mirror. It passes through the 7th and 2nd dichroic mirrors 8 and enters the mirror 9. On the other hand, the laser beam 4 generated by the second laser excitation light source 2 is made into parallel light by the collimator lens 10 and then reflected by the first dichroic mirror 7 to change its direction by 90 degrees. It passes through the second dichroic mirror 8 and enters the mirror 9. Further, the laser beam 4 generated from the third laser excitation light source 3 is made into parallel light by the collimator lens 11 and then reflected by the second dichroic mirror 8 to change its direction by 90 degrees. It is incident on the mirror 9. The laser beam 4 incident on the mirror 9 is reflected by the mirror 9, and further incident on the mirror 12 and reflected. A perforated mirror 14 having a hole 13 formed in the center is arranged in the optical path of the laser beam reflected by the mirror 12, and the laser beam reflected by the mirror 12 passes through the hole 13 of the perforated mirror 14. It passes through and is incident on the concave mirror 18. The laser beam 4 incident on the concave mirror 18 is reflected by the concave mirror 18 and is incident on the optical head 15. The optical head 15 includes a mirror 16 and an aspherical lens 17, and the laser beam 4 incident on the optical head 15 is reflected by the mirror 16 and is reflected by the aspherical lens 17 on the glass plate 21 of the stage 20. It is focused on the surface of the set image carrier 22. The image generator according to this embodiment is a laser beam 4 The electrophoretic image of the denatured DNA labeled with the fluorescent dye recorded on the gel support or the transfer support, and the radioactive label recorded on the luminescent phosphor layer provided on the accumulative phosphor sheet. It is configured to be able to read an autoradiography image regarding the position information of a substance, and a gel support, a transfer support, or an accumulative phosphor sheet is configured to be set as an image carrier 22 on the stage 20. In the image generator according to the present embodiment, an LED array 23 that is movable in the sub-scanning direction perpendicular to the paper surface is further provided above the stage 20 in FIG. 1, and will be described in detail later. The LED array 23 reads the image recorded on the transmissive document, that is, the material capable of transmitting light, or remains accumulated in the luminescent phosphor layer provided on the accumulative phosphor sheet. It is configured to be able to eliminate the radiation energy that is present. Electrophoretic images of denatured DNA labeled with a fluorescent dye are recorded on the transcription support, for example: That is, first, a plurality of DNA fragments containing a DNA fragment consisting of a gene of interest are separated and developed by electrophoresis on a gel-supporting medium, and denatured by alkaline treatment to form a single strand. Let it be DNA. Next, the gel support medium and the transfer support are superposed by a known Southern blotting method, and at least a part of the denatured DNA fragment is transferred onto the transfer support and fixed by warming treatment and ultraviolet irradiation. To do. Then, the probe prepared by labeling the DNA or RNA complementary to the DNA of the target gene with a fluorescent dye and the denatured DNA fragment on the transcription support 12 are hybridized by warming treatment and double-stranded. DNA formation (renaturation) or DNA-RNA conjugate formation. Then, for example, fluorescein, rhodamine, Cy-5 Probes are prepared by labeling DNA or RNA complementary to the DNA of the gene of interest, respectively, using fluorescent dyes such as. At this time, since the denatured DNA fragment on the transcription support is fixed, only the probe DNA or the DNA fragment complementary to the probe RNA hybridizes to capture the fluorescently labeled probe. Then, by flushing the non-hybrid-forming probe with a suitable solution, only the DNA fragment carrying the gene of interest forms a hybrid with the fluorescently labeled DNA or RNA on the transcription support. Fluorescent labeling is given. An electrophoretic image of the denatured DNA labeled with the fluorescent dye is recorded on the obtained transcription support in this way. Further, the position information of the radiolabeled substance is recorded in the luminescent phosphor layer formed on the accumulative phosphor sheet as follows. Here, the position information refers to various types of information centered on the position of the radioactively labeled substance or the aggregate thereof in the sample, for example, the existence position and shape of the aggregate of the radioactively labeled substance existing in the sample, and the position thereof. It means various kinds of information obtained as one or an arbitrary combination of information consisting of the concentration and distribution of radioactive labeling substances. For example, when recording the position information of a radiolabeled substance in a gene using the Southern blot hybridization method on a luminescent phosphor layer formed on an accumulative phosphor sheet, first, the purpose is Multiple DNA fragments, including DNA fragments consisting of the genes to be used, are separated and developed by electrophoresis on a gel-supporting medium, and denatured by alkali treatment. Then, it becomes a single-stranded DNA. Then, by a known Southern blotting method, the gel support medium and a transfer support such as a nitrocellulose filter are superposed, and at least a part of the denatured DNA fragment is transferred onto the transfer support to perform a heating treatment. Fix by UV irradiation. Furthermore, the probe and the denatured DNA fragment on the transcription support prepared by a method such as radioactively labeling a DNA or RNA complementary to the DNA of the target gene are hybridized by a heating treatment, and the two are hybridized. Strand DNA re-naturation Alternatively, it forms a DNA / RNA conjugate. At this time, since the denatured DNA fragment on the transcription support is fixed, only the probe DNA or the DNA fragment complementary to the probe RNA hybridizes to capture the radiolabeled probe. Then, by flushing the non-hybrid-forming probe with a suitable solution, on the transcription support, only the DNA fragment carrying the gene of interest will hybridize with the radiolabeled DNA or RNA. A radioactive label is given. Then, by superimposing the dried transfer support and the accumulative fluorescent sheet for a certain period of time and performing an exposure operation, at least a part of the radiation emitted from the radioactive labeling substance on the transfer support is accumulated. It is absorbed by the luminescent phosphor layer formed on the fluorescent phosphor sheet, and the position information of the radioactive labeling substance in the sample is accumulated and recorded in the luminescent phosphor layer in the form of an image. When the laser beam 4 is incident on an image carrier 22 such as a gel support or a transfer support carrying an image of a fluorescent substance, the fluorescent substance is excited to emit fluorescence 25, and cumulative fluorescence carrying a radiographic image is emitted. When the laser beam is incident on the image carrier 22 made of the body sheet, the luminescent phosphor is excited and the luminescent light 25 is emitted. The fluorescence 25 emitted from the gel support, the transfer support, or the like, or the bright light 25 emitted from the accumulative phosphor sheet, is focused on the mirror 16 by the aspherical lens 17 provided in the optical head 15. It is reflected by the mirror 16 on the same side as the optical path of the laser beam 4 by the mirror 16 to be parallel light, and is incident on the concave mirror 18. The fluorescence 25 or the brilliant light 25 incident on the concave mirror 18 is reflected by the concave mirror 18 and is incident on the perforated mirror 14. As shown in FIG. 2, the fluorescence 25 or the brilliant light 25 incident on the perforated mirror 14 is reflected downward by the perforated mirror 14 formed by the concave mirror, is incident on the filter unit 28, and is predetermined. The light of the wavelength of is cut off, enters the photomultiplier 30, and is detected photoelectrically. As shown in Figure 2 , The filter unit 28 includes four filter members 31a, 31b, 31c, and 31d, and the filter unit 28 is configured to be movable in the left-right direction in FIG. 2 by a motor (not shown). FIG. 3 is a schematic cross-sectional view taken along the line AA of FIG. As shown in FIG. 3, the filter member 31a includes a filter 32a, and the filter 32a uses the first laser excitation light source 1 to excite the fluorescent dye contained in the image carrier 22 and read the fluorescence. It is a filter member used in the above, and has the property of cutting light with a wavelength of 640 nm and transmitting light with a wavelength longer than 640 nm. FIG. 4 is a schematic cross-sectional view taken along the BB line of FIG. As shown in FIG. 4, the filter member 31b includes a filter 32b, and the filter 32b uses a second laser excitation light source 2 to excite the fluorescent dye contained in the image carrier 22 and read the fluorescence. It is a filter member used in the above, and has the property of cutting light with a wavelength of 532 nm and transmitting light with a wavelength longer than 532 nm. FIG. 5 is a schematic cross-sectional view taken along the CC line of FIG. As shown in FIG. 5, the filter member 31c includes a filter 32c, and the filter 32c uses a third laser excitation light source 3 to excite the fluorescent dye contained in the image carrier 22 and read the fluorescence. It is a filter member used in the above, and has the property of cutting light with a wavelength of 473 nm and transmitting light with a wavelength longer than 473 nm. FIG. 6 is a schematic cross-sectional view taken along the DD line of FIG. As shown in FIG. 6, the filter member 31d includes a filter 32d, and the filter 32d uses a first laser excitation light source 1 when the image carrier 22 is a storage phosphor sheet. It is a filter used to excite the brilliant phosphor contained in the sheet and read the brilliant light emitted from the brilliant phosphor. It has the property of transmitting only light in the wavelength range and cutting light with a wavelength of 640 nm. Therefore, the type of laser excitation light source to be used, i.e. the image carrier 22 And by selectively locating the filter members 31a, 31b, 31c, 31d in the optical path of the fluorescence 25 or the brilliant light 25 in front of the photomultiplier 30 according to the type of fluorescent dye, the photomultiplier 30 is , Only the light to be detected can be detected photoelectrically. In this embodiment, the filter unit 28 is further configured to be able to move to a position retracted from the optical path of the fluorescence 25 or the brilliant light 25 in front of the photomultiplier 30. The analog image data that is photoelectrically detected by the photomultiplier 30 and generated is converted into digital image data by the A / D converter 33 and sent to the image data processing device 34. Although not shown in FIG. 1, the optical head 15 is configured to be movable in the XY directions in FIG. 1 by a scanning mechanism so that the entire surface of the image carrier 22 is scanned by the laser beam 4. ing. FIG. 7 is a schematic plan view of the scanning mechanism of the optical head. In FIG. 7, for the sake of simplicity, the optical system excluding the optical head 15 and the optical path of the laser light 4 and the fluorescence 25 or the brilliant light 25 are omitted. As shown in FIG. 7, the scanning mechanism for scanning the optical head 15 includes a substrate 40, on which the sub-scanning pulse motor 41 and a pair of guides 42, 42 are fixed and mounted on the substrate 40. Further, in FIG. 7, a movable substrate 43 is provided in the sub-scanning direction indicated by Y. The movable substrate 43 is formed with a threaded hole (not shown), in which the threaded rod 44 rotated by the sub-scanning pulse motor 41 is engaged. ing. A main scanning pulse motor 45 is provided on the movable substrate 43, and the main scanning pulse motor 45 is configured to be able to drive the endless belt 46. The optical head 15 is fixed to the endless belt 46, and when the main scanning pulse motor 45 drives the endless belt 46, it is configured to move in the main scanning direction indicated by X in FIG. 7. ing. Figure 7 Smell 47 is a linear encoder that detects the position of the optical head 15 in the main scanning direction, and 48 is a slit of the linear encoder 47. Therefore, the main scanning pulse motor 45 drives the endless belt 46 in the main scanning direction, and the sub scanning pulse motor 41 moves the substrate 43 in the sub scanning direction, so that the optical head 15 is XY in FIG. Moved in the direction, the laser beam 4 scans the entire surface of the image carrier 22. FIG. 8 is a schematic side view showing details of the vicinity of the stage 20. As shown in FIG. 8, an LED array 23 is provided above the stage 20. The LED array 23 reads a transmissive document such as a developed X-ray film on which an autoradiography image is recorded, that is, an image recorded on a material capable of transmitting light, or is provided on a storage phosphor sheet. It is turned on and used when erasing the residual radiation energy that remains accumulated in the luminescent phosphor layer, and is used by the scanning mechanism (not shown) of the optical head 15. It is configured to move only in the sub-scanning direction, that is, in the Y direction in FIG. 7, in synchronization with the movement in the sub-scanning direction. When reading a transparent document such as a developed X-ray film on which an autoradiography image is recorded, the transparent document is placed on the glass plate 21 of the stage 20 as an image carrier 22. Prior to scanning the transparent document, the filter unit 28 is moved to a position retracted from the front surface of the photomultiplier 30, followed by a first laser excitation light source 1, a second laser excitation light source 2, and a third laser. The excitation light source 3 is kept off and the LED array 23 is turned on. As a result, the white light 24 is emitted from the LED array 23, and the white light 24 is uniformly irradiated to the region of the transmitted document 22 corresponding to the main scanning line. The white light 24 applied to the transmitted original 22 passes through the transmitted original 22, is incident on the optical head 15, is focused on the mirror 16 by the aspherical lens 17, and is the same as the optical path of the laser beam 4 by the mirror 16. Reflected to the side, flat It is regarded as a line of light and is incident on the concave mirror 18. The white light 24 that has passed through the transmission original 22 and is reflected by the mirror 16 and is incident on the concave mirror 18 is reflected by the concave mirror 18 and is incident on the perforated mirror 14. The white light 24 incident on the perforated mirror 14 is reflected downward by the perforated mirror 14 formed by the concave mirror, as shown in FIG. Here, since the filter unit 28 is moved to a position retracted from the front surface of the photomultiplier 30, the white light 24 reflected by the perforated mirror 14 is incident on the photomultiplier 30 and detected photoelectrically. Will be done. The analog image data that is photoelectrically detected by the photomultiplier 30 and generated is converted into digital image data by the A / D converter 33 and sent to the image data processing device 34. On the other hand, when the radiation energy accumulated in the luminescent phosphor layer formed on the accumulating phosphor sheet and erasing the remaining radiation energy is eliminated, the accumulating phosphor sheet is placed on the glass plate 21 of the stage 20. It is placed so that the luminescent phosphor layer faces upward. The first laser excitation light source 1, the second laser excitation light source 2, the third laser excitation light source 3, and the photomultiplier 30 are then held in the off state, the optical head 15 is held in the stationary state, and the LED array. 23 is turned on. As a result, white light 24 is emitted from the LED array 23, the region of the luminescent phosphor layer corresponding to the main scanning line is uniformly irradiated with the light 24, and the brilliance contained in the luminescent phosphor layer is emitted. Radiation energy is emitted from the exhaustive phosphor. Since the LED array 23 is configured to be moved in the sub-scanning direction by a scanning mechanism (not shown), the entire surface of the luminescent phosphor layer formed on the accumulative phosphor sheet is the LED array. Scanned by the white light 24 emitted from 23, accumulated in the luminescent phosphor layer, the remaining radiation energy is released. FIG. 9 shows a block diagram showing a control system, an input system, and a drive system of an image reading device used in the image generating device according to a preferred embodiment of the present invention. Gram. As shown in FIG. 9, the control system of the image reading device includes a control unit 50 that controls the entire image reading device, and the input system of the image reading device is operated by the user to provide various instruction signals. It is equipped with a keyboard 51 that can input. As shown in FIG. 9, the drive system of the image reader moves the filter unit motor 52 and the optical head 15 for moving the filter unit 28 including the four filter members 31a, 31b, 31c, and 31d in the main scanning direction. It includes a main scanning pulse motor 45 for moving the optical head 15, a sub scanning pulse motor 41 for moving the optical head 15 in the sub scanning direction, and a sub scanning pulse motor 53 for moving the LED array 23 in the sub scanning direction. The control unit 50 selectively outputs a drive signal to the first laser excitation light source 1, the second laser excitation light source 2, the third laser excitation light source 3, or the LED array 23, and also outputs the drive signal to the filter unit motor 52 and the main scan. The drive signal can be output to the pulse motor 45, the sub-scanning pulse motor 41, and the sub-scanning pulse motor 53. The image reading device configured as described above reads the fluorescence image supported on the gel support or the transfer support and generates digital image data as follows. First, the transfer support or gel support, which is the image carrier 22, is set on the glass plate 21 of the stage 20. When the transfer support or gel support is set on the glass plate 21 of the stage 20, the user identifies the type of fluorescent substance labeling the sample on the keyboard 51, and the transfer support or gel support. An instruction signal indicating that the fluorescent image carried on the screen should be read is input. The instruction signal input to the keyboard 51 is input to the control unit 50, and when the control unit 50 receives the instruction signal, the laser excitation light source to be used is determined according to the table stored in the memory (not shown). Determine and determine whether filters 32a, 32b, 32c, or 32d should be located in the optical path of fluorescence 25. .. For example, when the sample is labeled with Rhodamine, Rhodamine can be most efficiently excited by a laser with a wavelength of 532 nm, so the control unit 50 selects the second laser excitation light source 2 as well as Select the filter 32b, output the drive signal to the filter unit motor 52, move the filter unit 28, cut the light with a wavelength of 532 nm, and transmit the light with a wavelength longer than 532 nm. The provided filter member 31b is positioned in the optical path of the fluorescence 25. Next, the control unit 50 outputs a drive signal to the second laser excitation light source 2, activates the second laser excitation light source 2, and emits the laser light 4 having a wavelength of 532 nm. The laser beam 4 emitted from the second laser excitation light source 2 is made into parallel light by the collimator lens 10 and then incident on the first dichroic mirror 7 and reflected. The laser beam 4 reflected by the first dichroic mirror 7 passes through the second dichroic mirror 8 and is incident on the mirror 9. The laser beam 4 incident on the mirror 9 is reflected by the mirror 9, and further incident on the mirror 12 and reflected. The laser beam 4 reflected by the mirror 12 is incident on the perforated mirror 14, passes through the hole 13 formed in the perforated mirror 14, and is incident on the concave mirror 18. The laser beam 4 incident on the concave mirror 18 is reflected by the concave mirror 18 and is incident on the optical head 15. The laser beam 4 incident on the optical head 15 is reflected by the mirror 16 and focused by the aspherical lens 17 on the transfer support or the gel support set on the glass plate 21 of the stage 20. As a result, rhodamine, which is a fluorescent substance contained in the transfer support or the gel support, is excited by the laser beam 4, and the fluorescence 25 is emitted from the rhodamine. The fluorescence 25 emitted from Rhodamine is focused by an aspherical lens 17 provided on the optical head 15 and reflected by a mirror 16 on the same side as the optical path of the laser beam 4 to be parallel light. Then, it is incident on the concave mirror 18. The laser beam 4 incident on the concave mirror 18 is reflected by the concave mirror 18 and is incident on the perforated mirror 14. The fluorescence 25 incident on the perforated mirror 14 is reflected downward by the perforated mirror 14 formed by the concave mirror, as shown in FIG. 2, and is incident on the filter 32b of the filter unit 28. Since the filter 32b has the property of cutting light with a wavelength of 532 nm and transmitting light with a wavelength longer than 532 nm, the light with a wavelength of 532 nm, which is the excitation light, is cut and the fluorescence emitted from Rhodamine is emitted. Only light in the 25 wavelength range passes through the filter 32b and is photoelectrically detected by the photomultiplier 30. As described above, the optical head 15 is moved on the substrate 43 in the X direction by the main scanning pulse motor 45 provided on the substrate 43 in FIG. 7, and the substrate 42 is moved by the sub-scanning pulse motor 41. , In FIG. 7, since it is moved in the Y direction, the entire surface of the transfer support or gel support is scanned by the laser beam 4, and is contained in the transfer support or gel support and emitted from the loadamine labeling the sample. By photoelectrically detecting the resulting fluorescence with the photomultiplier 30, the fluorescence image of Rhodamine, which is a fluorescent substance recorded on the transfer support or the gel support, can be read and analog image data can be generated. The analog image data that is photoelectrically detected by the photomultiplier 30 and generated is converted into digital image data by the A / D converter 33 and sent to the image data processing device 34. On the other hand, when the autoradiography image regarding the position information of the radiolabeled substance recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet is read and digital image data is generated, the accumulative phosphor sheet is used. It is set on the glass plate 21 of the stage 20. An autoradiographic image of the position information of the radiolabeled material recorded on the keyboard 51 by the user on the luminescent phosphor layer formed on the accumulative phosphor sheet. An instruction signal to read is input. As a result, the filter unit motor 52 is driven by the control unit 50, and a filter having a property of transmitting only the light in the wavelength range of the brilliant light emitted from the brilliant phosphor and cutting the light having the wavelength of 640 nm. After the filter unit 28 is moved so that the filter member 31d provided with 32d is located in the optical path of the extinct light 25, the first laser excitation light source 1 is activated and from the first laser excitation light source 1. , 640 nm wavelength laser light 4 is emitted. The laser beam 4 emitted from the first laser excitation light source 1 is made into parallel light by the collimator lens 5, then incident on the mirror 6 and reflected. The laser beam 4 reflected by the mirror 6 passes through the first dichroic mirror 7 and the second dichroic mirror 8 and is incident on the mirror 9. The laser beam 4 incident on the mirror 9 is reflected by the mirror 9, and further incident on the mirror 12 and reflected. The laser beam 4 reflected by the mirror 12 passes through the hole 13 of the perforated mirror 14 and is incident on the concave mirror 18. The laser beam 4 incident on the concave mirror 18 is reflected by the concave mirror 18 and is incident on the optical head 15. The laser beam 4 incident on the optical head 15 is reflected by the mirror 16 and focused by the aspherical lens 17 on the luminescent phosphor layer of the accumulative phosphor sheet placed on the glass plate 21 of the stage 20. Will be done. As a result, the brilliant phosphor contained in the brilliant phosphor layer formed on the accumulative phosphor sheet is excited by the laser beam 4, and the brilliant light 25 is emitted from the brilliant phosphor. .. The brilliant light 25 emitted from the brilliant phosphor is collected by the aspherical lens 17 provided in the optical head 15, reflected by the mirror 16 on the same side as the optical path of the laser beam 4, and is parallel light. It is incident on the concave mirror 18. The laser beam 4 incident on the concave mirror 18 is reflected by the concave mirror 18 and is incident on the perforated mirror 14. The fluorescence 25 incident on the perforated mirror 14 is due to the perforated mirror 14 formed by the concave mirror. Then, as shown in FIG. 2, it is reflected downward and incident on the filter 32d of the filter unit 28. Since the filter 32d has the property of transmitting only the light in the wavelength range of the brilliant light emitted from the brilliant phosphor and cutting the light of the wavelength of 640 nm, the filter 32d has the property of cutting the light of the wavelength of 640 nm, which is the excitation light. The light is cut, and only the light in the wavelength range of the extinct light passes through the filter 32d and is detected photoelectrically by the photomultiplier 30. The optical head 15 is moved on the substrate 43 in the X direction by the main scanning pulse motor 45 provided on the substrate 43 in FIG. 7, and the substrate 43 is moved by the sub-scanning pulse motor 41 in FIG. Since it is moved in the Y direction, the entire surface of the luminescent phosphor layer formed on the accumulative phosphor sheet is scanned by the laser beam 4, and emitted from the luminescent phosphor contained in the luminescent phosphor layer. By photoelectrically detecting the emitted luminescent light with the photomultiplier 30, an autoradiography image relating to the position information of the radioactive labeling substance recorded on the fluorescing phosphor layer is read and analog image data is generated. be able to. The analog image data that is photoelectrically detected by the photomultiplier 30 and generated is converted into digital image data by the A / D converter 33 and sent to the image data processing device 34. The image generator according to the present embodiment is further configured to be capable of reading a transparent original such as a developed X-ray film on which an autoradiography image is recorded, and when reading the transparent original, it is used as an image carrier 22. , A transparent original such as a developed X-ray film on which an autoradiography image is recorded is placed on the glass plate 21 of the stage 20. When a transparent document such as a developed X-ray film on which an autoradiograph image is recorded is placed on the glass plate 21 of the stage 20, the user instructs the keyboard 51 that the transparent document should be read. Is entered. The instruction signal input to the keyboard 51 is input to the control unit 50, and the control unit 50 gives an instruction. When the signal is received, a drive signal is output to the filter unit motor 52 according to a table stored in a memory (not shown), and the filter unit 28 is moved to a position retracted from the front surface of the photomultiplier 30. Next, the control unit 50 turns on the LED array 23 and outputs a drive signal to the main scanning pulse motor 45, the sub-scanning pulse motor 41, and the sub-scanning pulse motor 53. As a result, the white light 24 is emitted from the LED array 23, and the white light 24 is uniformly irradiated to the region of the transmitted document 22 corresponding to the main scanning line. The white light 24 applied to the transmission original 22 passes through the transmission original 22, enters the optical head 15, is focused on the mirror 16 by the aspherical lens 17, and is directed toward the concave mirror 18 by the mirror 16. Be reflected. The white light 24 transmitted through the transmission original 22 and reflected by the mirror 16 is further reflected by the concave mirror 18 and incident on the perforated mirror 14. The white light 24 incident on the perforated mirror 14 is reflected downward by the perforated mirror 14 formed by the concave mirror, as shown in FIG. Here, since the filter unit 28 is moved to a position retracted from the front surface of the photomultiplier 30, the white light 24 reflected by the concave mirror 27 is incident on the photomultiplier 30 and is detected photoelectrically. To. The main scanning pulse motor 45 drives the endless belt 46 in the main scanning direction, and the sub scanning pulse motor 41 moves the substrate 43 in the sub scanning direction, so that the optical head 15 is moved in the XY direction in FIG. On the other hand, the LED array 23 is moved in the sub-scanning direction by the sub-scanning pulse motor 52 in synchronization with the movement in the sub-scanning direction of the optical head 15, so that the entire surface of the transmission document 22 is moved from the LED array 23. A developed X-ray film in which an autoradiography image is recorded by photoelectrically detecting the white light 24 scanned by the emitted white light 24 and transmitted through the transmitted original 22 by the photomultiplier 30. Any transparent document can be scanned to generate analog image data. The analog image data that is photoelectrically detected by the photomultiplier 30 and generated is converted into digital image data by the A / D converter 33 and sent to the image data processing device 34. In the present embodiment, the image generator is further configured to be accumulating in the luminescent phosphor layer formed on the accumulating phosphor sheet so that the remaining radiation energy can be eliminated. When the radiation energy accumulated in the phosphorescent phosphor layer formed on the accumulative phosphor sheet and the remaining radiation energy is erased, the accumulative phosphor sheet is extinguished on the glass plate 21 of the stage 20. The sex phosphor layer is placed so that it faces upward. When the accumulative phosphor sheet is placed on the glass plate 21 of the stage 20, it is accumulated by the user on the keyboard 51 in the brilliant phosphor layer formed on the accumulative phosphor sheet and remains. An instruction signal indicating that the radiation energy is to be erased is input. The instruction signal input to the keyboard 51 is input to the control unit 50, and when the control unit 50 receives the instruction signal, the filter unit motor 52 and the main scan are performed according to a table stored in a memory (not shown). The drive signal is not output to the pulse motor 45 and the sub-scanning pulse motor 41, the LED array 23 is turned on while the photomultiplier 30 is held in the off state, and the drive signal is output to the sub-scanning pulse motor 53. As a result, the white light 24 is emitted from the LED array 23, and the white light 24 is uniformly irradiated to the region of the brilliant phosphor layer corresponding to the main scanning line, and is contained in the brilliant phosphor layer. Radiation energy is emitted from the luminescent phosphor. Since the LED array 23 is configured to be moved in the sub-scanning direction by the sub-scanning pulse motor 53, the entire surface of the brilliant phosphor layer formed on the accumulative phosphor sheet is formed from the LED array 23. Scanned by the emitted white light 24, accumulated in the luminescent phosphor layer, and the remaining radiation energy is emitted. Will be done. The scanning of the luminescent phosphor layer by the white light 24 emitted from the LED array 23 is repeated a predetermined number of times. According to this embodiment, the image generator is subordinate to the optical head 15 above the stage 20 in addition to the first laser excitation light source 1, the second laser excitation light source 2, and the third laser excitation light source 3. Since the LED array 23 that is moved in the sub-scanning direction in synchronization with the movement in the scanning direction is provided, an electrophoretic image of the denatured DNA labeled with the fluorescent dye is carried on the glass plate 21 of the stage 20. A first laser excitation light source 1, a second laser excitation light source 2, and a second laser excitation light source 1 and a second laser excitation light source 2 are placed on which a storage phosphor sheet carrying an autoradiography image regarding the position information of a gel support or a transfer support or a radioactive labeling substance is placed. Selectively activate any of the laser excitation light sources 3 of 3 to excite the fluorescent dye or the bright fluorescent material contained in the bright fluorescent material layer, and the fluorescent 25 or the bright fluorescent light emitted from the fluorescent dye is used. An electrophoretic image or accumulative phosphor sheet of denatured DNA labeled with a fluorescent dye recorded on a gel support or a transfer support by photoelectrically detecting the extinct light 25 emitted from the fluorescent phosphor. Not only can an autoradiography image regarding the position information of the radioactive labeling substance recorded on the fluorescee phosphor layer provided in the above be generated, but also the autoradiography image is recorded on the glass plate 21 of the stage 20. A transparent original such as an X-ray film that has been developed has been placed, the LED array 23 is turned on, white light 24 is emitted, and the optical head 15 is moved in the main scanning direction and the sub-scanning direction. Autoradiography recorded on a transmissive document by photoelectrically detecting the white light 24 transmitted through the transmissive document while moving the LED array 23 in the sub-scan direction in synchronization with the movement of the sub-scanning direction of 15. An image such as an image can be generated, and therefore the usefulness of the image generation device can be improved. Further, according to the present embodiment, in addition, the accumulative phosphor sheet is placed on the glass plate 21 of the stage 20 to perform LE. By turning on the D array 23 and moving the LED array 23 in the sub-scanning direction, it is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet, and the remaining radiation energy is released and eliminated. Therefore, it is not necessary to have a radiation energy erasing device in addition to the image generator, and the installation space can be significantly reduced. FIG. 10 is a schematic front view of an image generator according to another preferred embodiment of the present invention. As shown in FIG. 10, the image generator has a cooled CCD camera 71, a dark box 72 and a personal computer 73, which includes a CRT 74 and a keyboard 75. FIG. 11 is a schematic vertical sectional view of the cooled CCD camera 71. As shown in FIG. 11, the cooling CCD camera 71 includes a CCD 76, a heat transfer plate 77 made of a metal such as aluminum, a Pertier element 78 for cooling the CCD 6, and a shutter arranged in front of the CCD 76. 79, an A / D converter 80 that converts analog image data generated by CCD76 into digital image data, and an image data buffer 81 that temporarily stores image data digitized by the A / D converter 80. It is equipped with a camera control circuit 82 that controls the operation of the cooling CCD camera 71. The opening formed between the dark box 2 and the dark box 2 is closed by a glass plate 85, and heat dissipation fins 86 for dissipating heat generated by the Peltier element 78 are provided around the cooling CCD camera 71 in the longitudinal direction. It is formed over the entire surface. A camera lens 87 having a lens focus adjustment function is mounted in a dark box 72 on the front surface of the glass plate 85. FIG. 12 is a schematic vertical sectional view of the dark box 72. As shown in FIG. 12, a transparent stage 90 on which the image carrier unit 22 can be placed is provided in the dark box 72, and excitation light having an emission wavelength center of 470 nm is emitted diagonally above the stage 90. A first red LED light source 91 and a second red LED light source 92 that emit light are provided. First red LED light source 91 and second red LED light source A filter 93 and a filter 94 are attached to the front surface of the 92, respectively. The filters 93 and 94 have a property of cutting light harmful to the excitation of a fluorescent substance other than the wavelength of the excitation light and transmitting only the light of the wavelength of the excitation light. A filter 95 that cuts the excitation light is detachably provided on the front surface of the camera lens 87. As shown in FIG. 12, an array of white light sources 96 is provided inside the stage 90, and a diffuser plate 97 is provided on the stage 90. FIG. 13 is a block diagram around the personal computer 73. As shown in FIG. 13, the personal computer 73 includes a CPU 100 that controls the exposure of the cooled CCD camera 71, an image data transfer means 101 that reads the image data generated by the cooled CCD camera 71 from the image data buffer 81, and image data. An image that displays a visible image on the screen of the CRT 74 based on the image data processing device 102 that performs image processing, the image data storage means 103 that stores the image data, and the image data stored in the image data storage means 103. It is equipped with a display means 104. The first red LED light source 91 and the second red LED light source 92 are controlled by the light source control means 105, and the light source control means 105 receives an instruction signal from the keyboard 75 via the CPU 100. It is configured in. The CPU 100 is configured to be able to output various signals to the camera control circuit 82 of the cooled CCD camera 71. In the image generator according to the present embodiment, an autoradiography image and an autoradiography image relating to the position information of the radioactive labeling substance recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet were recorded. It is made of a material that can transmit light, such as a developed X-ray film, and is configured to be able to read a transmissive document on which an image is recorded, and is also accumulated in the luminescent phosphor layer of the accumulative phosphor sheet. , It is configured so that the remaining radiation energy can be released and eliminated. Brightness formed on the accumulative phosphor sheet When reading an autoradiography image of the position information of the radioactive labeling substance recorded on the exhaustive phosphor layer, the user first turns on the first red LED light source 91 and the second red LED light source 92, and the camera Lens focusing is performed using the lens 87. Next, a storage phosphor sheet as an image carrier 22 is placed on the diffuser plate 97 of the stage 90 so that the bright fluorescent layer is facing upward, and the dark box 72 is closed. After that, when the user inputs an exposure start signal to the keyboard 75, the light source control means 105 turns on the first red LED light source 91 and the second red LED light source 92, and the excitation light is directed toward the image carrier 22. Emitted. At the same time, the exposure start signal is input to the camera control circuit 82 of the cooled CCD camera 71 via the CPU 100, the shutter 79 is opened by the camera control circuit 82, and the exposure of the CCD 76 is started. In the excitation light emitted from the first red LED light source 91 and the second red LED light source 92, the wavelength components other than the light of the wavelength of the excitation light are cut by the filters 93 and 94, and as a result, the first red color is obtained. The excitation light emitted from the LED light source 91 and the second red LED light source 92 excites the brilliant phosphor contained in the brilliant phosphor layer formed on the accumulative phosphor sheet, and shines. The light is emitted. The bright light emitted from the bright phosphor contained in the bright phosphor layer is incident on the photoelectric surface of the CCD76 of the cooled CCD camera 71 through the filter 95 and the camera lens 87, and is incident on the photoelectric surface. To form an image. The CCD76 thus receives the light of the image formed on the photoelectric surface and stores it in the form of electric charges. Since the filter 95 cuts the light having the wavelength of the excitation light, only the brilliant light emitted from the brilliant phosphor contained in the brilliant phosphor layer is received by the CCD 76. When the predetermined exposure time elapses, the CPU 100 outputs an exposure completion signal to the camera control circuit 82 of the cooled CCD camera 71. When the camera control circuit 82 receives the exposure completion signal from the CPU100, the camera control circuit 82 receives the CCD76. The analog image data accumulated in the form of electric charge is transferred to the A / D converter 80, digitized, and temporarily stored in the image data buffer 81. At the same time as outputting the exposure completion signal to the camera control circuit 82, the CPU 100 outputs the data transfer signal to the image data transfer means 101 to read the image data from the image data buffer 81 of the cooling CCD camera 71, and image. Input to the data processing device 102. If necessary, the image data processing device 102 performs image processing on the image data and stores the image data in the image data storage means 103. After that, when the user inputs an image generation signal to the keyboard 75, the image display means 104 reads out the image data stored in the image data storage means 103, and based on the image data, the auto radio is displayed on the screen of the CRT 74. A graphic image is displayed. On the other hand, when reading a transparent original such as a developed X-ray film on which an autoradiography image is recorded, the filter 95 is first removed, and then the user turns on the white light source 96 and the camera lens 87. Is used to focus the lens. Next, as the image carrier 22, the transparent original is placed on the stage 90 diffusion plate 97, and the dark box 72 is closed. After that, the white light source 96 is turned on, and white light is applied to the transmitted document placed on the transparent stage 90. Since the diffuser plate 97 is provided on the stage 90, the white light emitted from the white light source 96 is uniformly applied to the transmitted original. Since the white light applied to the transmitted original is formed of a material capable of transmitting light, the transmitted original is transmitted through the transmitted original and is incident on the photoelectric surface of the CCD76 of the cooled CCD camera 71 via the camera lens 87. Then, an image is formed on the photoelectric surface. The CCD76 thus receives the light of the image formed on the photoelectric surface and stores it in the form of electric charges. When the predetermined exposure time elapses, the CPU 100 outputs an exposure completion signal to the camera control circuit 82 of the cooled CCD camera 71. The camera control circuit 82 receives an exposure completion signal from the CPU 100. Then, the analog image data accumulated by the CCD 76 in the form of electric charges is transferred to the A / D converter 80, digitized, and temporarily stored in the image data buffer 81. At the same time as outputting the exposure completion signal to the camera control circuit 82, the CPU 100 outputs the data transfer signal to the image data transfer means 101 to read the image data from the image data buffer 81 of the cooling CCD camera 71, and image. Input to the data processing device 102. If necessary, the image data processing device 102 performs image processing on the image data and stores the image data in the image data storage means 103. After that, when the user inputs an image generation signal to the keyboard 75, the image display means 104 reads out the image data stored in the image data storage means 103, and based on the image data, the transparent original is displayed on the screen of the CRT 74. Images such as the autoradiography image recorded in are displayed. In the present embodiment, it is further configured so that it can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet, and the remaining radiation energy can be released and eliminated, and the accumulative property can be obtained. The first red LED light source 91 and the second red LED light source 92 and the cooled CCD camera are used to release and eliminate the remaining radiation energy accumulated in the luminescent phosphor layer of the phosphor sheet. The 71 is held in the off state, and the accumulative phosphor sheet is placed on the diffuser plate 97 of the transparent stage 90 with the bright fluorescent layer facing downward. When the accumulative phosphor sheet is placed on the transparent stage 90, the white light source 96 is turned on and white light is applied to the luminescent phosphor layer of the accumulative phosphor sheet. Since the diffuser plate 97 is provided on the stage 90, the white light emitted from the white light source 96 is uniformly irradiated to the luminescent phosphor layer of the accumulative phosphor sheet. As a result, it is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet, and the remaining radiation energy is released. After a predetermined time elapses, the white light source 96 is turned off and the radiation energy erasing operation is completed. This implementation According to aspects, the image generator comprises an array of white light sources 96 in addition to a first red LED light source 91 and a second red LED light source 92, and an excitation mounted on the front surface of the camera lens 87. Since the optical cut filter 95 is removable, an accumulative phosphor sheet is placed on the diffuser plate 97 of the stage 90 so that the luminescent phosphor layer faces upward, and the excitation light cut filter 95 is placed. The first red LED light source 91 and the second red LED light source 92 are turned on, and the brilliance formed on the accumulative phosphor sheet by the red excitation light. The bright phosphor contained in the phosphor layer is excited, the excitation light is cut by the excitation light cut filter 95, and the bright light emitted from the bright phosphor is photoelectrically transmitted by CCD76. By detecting and generating image data, it is possible not only to generate an autoradiography image regarding the position information of the radioactive labeling substance recorded on the brilliant phosphor layer formed on the accumulative phosphor sheet. With the excitation light cut filter 95 removed from the camera lens 87, a transmitted original such as a developed X-ray film on which an autoradiography image is recorded is placed on the diffuser 97 of the stage 90. The array-shaped white light source 95 is turned on, white light is irradiated to the transmitted original, and the white light transmitted through the transmitted original is photoelectrically detected by CCD76 to generate image data, thereby forming the transmitted original. Images such as recorded autoradiography images can be generated, and therefore the usefulness of the image generator can be improved. Further, according to the present embodiment, in addition, an accumulative phosphor sheet is placed on the diffuser plate 97 of the stage 90 so that the exhilarating phosphor layer faces downward, and an array of white light sources 95 By irradiating the luminescent phosphor layer of the accumulating phosphor sheet with white light for a predetermined time, the luminescent phosphor layer of the accumulating phosphor sheet is accumulated and remains. Since it is possible to release and erase the radiation energy that is being emitted, it is possible to use an image generator. Separately, it is not necessary to have a radiation energy erasing device, and the installation space can be significantly reduced. The present invention is not limited to the above embodiments, and various modifications can be made within the scope of the invention described in the claims, and these are also included in the scope of the present invention. Needless to say. For example, in the embodiments shown in FIGS. 1 to 9, the LED array 23 is used as the white light source, but other white light sources such as fluorescent lamps may be provided instead of the LED array 23. .. Further, in the embodiment shown in FIGS. 1 to 9, the LED array 23 movable in the sub-scanning direction allows the region of the transmissive document corresponding to the main scanning line or the luminescent phosphor of the accumulating phosphor sheet. The area of the layer is configured to irradiate white light, but a light source capable of irradiating white light to the entire transmitted original or the entire luminescent phosphor layer of the accumulative phosphor sheet is used as a light source. It can also be kept stationary. Further, in the embodiment shown in FIGS. 1 to 9, the stage 20 on which the image carrier 22 is placed is held in a stationary state, the optical head 15 is moved in the X and Y directions, and the laser beam 4 is used. Is configured to scan the entire surface of the image carrier 22 by moving the optical head 15 in either the X or Y direction and moving the stage 20 in either the Y or X direction. The laser beam 4 can be configured to scan the entire surface of the image carrier 22 by moving it to, and further, the optical head 15 is held stationary and the stage 20 is moved in the X and Y directions. Moved to Although used, other white light sources such as fluorescent lamps can be provided in place of the LED array 23. Further, in the embodiment shown in FIGS. 1 to 9, the LED array 23 movable in the sub-scanning direction allows the region of the transmissive document corresponding to the main scanning line or the luminescent phosphor of the accumulating phosphor sheet. The area of the layer is configured to irradiate white light, but a light source capable of irradiating white light to the entire transmitted original or the entire luminescent phosphor layer of the accumulative phosphor sheet is used as a light source. It can also be kept stationary. Further, in the embodiment shown in FIGS. 1 to 9, the stage 20 on which the image carrier 22 is placed is held in a stationary state, the optical head 15 is moved in the X and Y directions, and the laser beam 4 is used. Is configured to scan the entire surface of the image carrier 22 by moving the optical head 15 in either the X or Y direction and moving the stage 20 in either the Y or X direction. The laser beam 4 can be configured to scan the entire surface of the image carrier 22 by moving it to, and further, the optical head 15 is held stationary and the stage 20 is moved in the X and Y directions. Moved to Although used, other white light sources such as fluorescent lamps can be provided in place of the LED array 23. Further, in the embodiment shown in FIGS. 1 to 9, the LED array 23 movable in the sub-scanning direction allows the region of the transmissive document corresponding to the main scanning line or the luminescent phosphor of the accumulating phosphor sheet. The area of the layer is configured to irradiate white light, but a light source capable of irradiating white light to the entire transmitted original or the entire luminescent phosphor layer of the accumulative phosphor sheet is used as a light source. It can also be kept stationary. Further, in the embodiment shown in FIGS. 1 to 9, the stage 20 on which the image carrier 22 is placed is held in a stationary state, the optical head 15 is moved in the X and Y directions, and the laser beam 4 is used. Is configured to scan the entire surface of the image carrier 22 by moving the optical head 15 in either the X or Y direction and moving the stage 20 in either the Y or X direction. The laser beam 4 can be configured to scan the entire surface of the image carrier 22 by moving it to, and further, the optical head 15 is held stationary and the stage 20 is moved in the X and Y directions. Moved toBy setting the image carrier 22, the entire surface of the image carrier 22 can be scanned by the laser beam 4. Further, in the embodiment shown in FIGS. 1 to 9, the image generator is a gel support or a gel support in addition to the image of the radioactive labeling substance recorded on the bright fluorescent layer of the accumulative fluorescent sheet. Although the image of the fluorescent dye contained in the transfer support is configured to be readable, it is not always necessary that the image of the fluorescent dye be readable, and the second laser excitation light source 2 and the third laser excitation are performed. The light source 3 and the filter members 31a, 31b, and 31c can be omitted. Further, in the embodiment shown in FIGS. 1 to 9, a semiconductor laser light source that emits a laser light 4 having a wavelength of 640 nm is used as the first laser excitation light source 1, but a laser light 4 having a wavelength of 640 nm 4 is used. A He-Ne laser light source that emits a laser beam 4 having a wavelength of 633 nm or a semiconductor laser light source that emits a laser beam 4 of 635 nm may be used instead of the semiconductor laser light source that emits the light. Further, in the embodiment shown in FIGS. 1 to 9, a photomultipler 30 is used as a photodetector to photoelectrically detect fluorescence or radiant light emitted from the image carrier unit 22. However, the photodetector used in the present invention may be any photodetector as long as it can detect fluorescence or brilliant light photoelectrically, and other photodetectors such as CCD can be used, not limited to the photomultiplier 30. .. Further, in the embodiments shown in FIGS. 10 to 13, the first red LED light source 91 and the second red LED light source 92 are included in the brilliant phosphor layer of the accumulative phosphor sheet. The bright LED is excited, but if the bright LED contained in the bright fluorescent layer of the accumulative phosphor sheet can be efficiently excited, the excitation light source can be arbitrary. It can be selected, and it is not always necessary to use the first red LED light source 91 and the second red LED light source 92. Further, in the embodiment shown in FIGS. 10 to 13, the diffuser plate 97 is provided on the transparent stage 90, but the diffuser plate 97 is provided. It is not always necessary to provide 97. Further, in the embodiment shown in FIGS. 10 to 13, heat radiating fins 86 for radiating heat generated by the Peltier element 78 are formed around the CCD camera 71 over approximately half of the longitudinal direction. However, the heat radiating fins 86 may be provided in all directions in the longitudinal direction, and the extent to which the heat radiating fins 86 are provided around the CCD camera 71 can be arbitrarily determined. Further, in the embodiment shown in FIGS. 10 to 13, the cooled CCD camera 71 is used, but a CCD camera without cooling means can also be used. Further, in the embodiment shown in FIGS. 10 to 13, the cooled CCD camera 71 is used, but instead of the CCD camera 71, a CID (charge injection element), a PDA (photodiode array), and a MOS type image sensor are used. Other solid-state image sensors that function as a two-dimensional area sensor, such as an element, can also be used. Further, in the embodiment shown in FIGS. 10 to 13, the image is reproduced on the screen of the CRT74, but instead of the CRT74, a flat panel display such as a liquid crystal display or an organic EL display is used. Can also be used. Further, in each of the above embodiments, the electrophoretic image of the gene using the Southern blot hybridization method is formed on the accumulative phosphor sheet according to the autoradiography image detection system. The case of recording on a phosphor layer and scanning photoelectrically has been described, but the present invention is not limited to reading and producing such a radiographic image, for example, thin layer chromatography of protein (TLC). ), And recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet. Autoradiography image, polyacrylamide gel electrophoresis to separate, identify, or evaluate the molecular weight and properties of the protein. Autoradiography images recorded on the luminescent phosphor layer formed on the accumulative fluorophore sheet, administration substances in experimental mice, etc. Formed on accumulative phosphor sheets such as autoradiography images recorded on the exfoliating phosphor layer formed on the accumulative phosphor sheet to study the pathways, states, etc. of metabolism, absorption, excretion, etc. In addition to reading and generating other autoradiography images recorded on the luminescent phosphor layer, it was generated using an electron microscope and recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet. An electron beam transmission image or an electron beam diffraction image of a metal or non-metal sample, an electron microscope image of a biological tissue, or a luminescent phosphor formed on a storage phosphor sheet such as a metal or non-metal sample. It can also be widely applied to reading and generating a radiation diffraction image recorded on a layer, a chemically luminescent image recorded on a fluoresce fluorescence layer formed on a storage fluorescence sheet, and the like. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. In order to study, etc., it is recorded on the luminescent phosphor layer formed on the luminescent phosphor sheet, such as an autoradiography image recorded on the luminescent phosphor layer formed on the accumulative fluoresce sheet. In addition to reading and generating other autoradiography images, electron beam transmission of metal or non-metal samples generated using an electron microscope and recorded on the fluorescee phosphor layer formed on the accumulative fluorescence sheet. Images, electron beam diffraction images, electron microscope images such as biological tissues, and radiation diffraction images recorded on a fluoresce fluorescence layer formed on a storage fluorescence sheet such as a metal or non-metal sample, storage. It can also be widely applied to reading and generating a chemically luminescent image recorded on a luminescent phosphor layer formed on a fluorescent phosphor sheet. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. In order to study, etc., it is recorded on the luminescent phosphor layer formed on the luminescent phosphor sheet, such as an autoradiography image recorded on the luminescent phosphor layer formed on the accumulative fluoresce sheet. In addition to reading and generating other autoradiography images, electron beam transmission of metal or non-metal samples generated using an electron microscope and recorded on the fluorescee phosphor layer formed on the accumulative fluorescence sheet. Images, electron beam diffraction images, electron microscope images such as biological tissues, and radiation diffraction images recorded on a fluoresce fluorescence layer formed on a storage fluorescence sheet such as a metal or non-metal sample, storage. It can also be widely applied to reading and generating a chemically luminescent image recorded on a luminescent phosphor layer formed on a fluorescent phosphor sheet. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. Using an electron microscope as well as reading and generating other autoradiography images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet such as the autoradiography image recorded on the optical body layer. An electron beam transmission image, an electron beam diffraction image, an electron microscope image of a biological tissue, etc. of a metal or non-metal sample recorded on a luminescent phosphor layer formed on a generated and accumulative phosphor sheet, and further. Radiation diffraction images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet such as a metal or non-metal sample, and chemistry recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet. It can be widely applied to the reading and generation of luminescent images and the like. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. Using an electron microscope as well as reading and generating other autoradiography images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet such as the autoradiography image recorded on the optical body layer. An electron beam transmission image, an electron beam diffraction image, an electron microscope image of a biological tissue, etc. of a metal or non-metal sample recorded on a luminescent phosphor layer formed on a generated and accumulative phosphor sheet, and further. Radiation diffraction images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet such as a metal or non-metal sample, and chemistry recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet. It can be widely applied to the reading and generation of luminescent images and the like. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. In addition to reading and generating graphic images, electron beam transmission images and electron beam diffraction of metal or non-metal samples generated using an electron microscope and recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet. For images, electron microscopic images of biological tissues, radiation diffraction images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet such as a metal or non-metal sample, and the accumulative phosphor sheet. It can also be widely applied to the reading and generation of chemically luminescent images recorded on the formed luminescent phosphor layer. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. In addition to reading and generating graphic images, electron beam transmission images and electron beam diffraction of metal or non-metal samples generated using an electron microscope and recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet. For images, electron microscopic images of biological tissues, radiation diffraction images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet such as a metal or non-metal sample, and the accumulative phosphor sheet. It can also be widely applied to the reading and generation of chemically luminescent images recorded on the formed luminescent phosphor layer. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. Radiation diffraction images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet such as a sample, chemiluminescent images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet, etc. It can also be widely applied to reading and generating. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. Radiation diffraction images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet such as a sample, chemiluminescent images recorded on the luminescent phosphor layer formed on the accumulative phosphor sheet, etc. It can also be widely applied to reading and generating. Further, in the above-described embodiment, the case where the radiation energy is accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and the remaining radiation energy is released to be eliminated has been described. The present invention is not limited to the case where it is accumulated in the luminescent phosphor layer of the accumulating fluorescence sheet and the remaining radiation energy is released to be eliminated, and the present invention is not limited to the case where the accumulating fluorescence is emitted. It can also be widely used when it is accumulated in the luminescent phosphor layer of the body sheet and the remaining light energy or electron beam energy is released and erased. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. The present invention is not limited to the above, and the present invention is also widely used in the case where the light energy or electron beam energy accumulated in the luminescent phosphor layer of the accumulative phosphor sheet is emitted and eliminated. Can be used. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light. The present invention is not limited to the above, and the present invention is also widely used in the case where the light energy or electron beam energy accumulated in the luminescent phosphor layer of the accumulative phosphor sheet is emitted and eliminated. Can be used. Further, in each of the above-described embodiments, the transmission document is read by using the LED array 23 that emits white light and the array-shaped white light source 96, and the light is accumulated in the brilliant phosphor layer of the accumulative phosphor sheet. The remaining radiation energy is emitted and erased, but it is recorded on the transmitted original by photoelectrically detecting the light transmitted through the transmitted original made of a material capable of transmitting light. A light source that emits light that can read and reproduce images and that can be accumulated in the luminescent phosphor layer of the accumulative phosphor sheet and efficiently emit the remaining radiation energy. It is sufficient, and it is not always necessary to use a white light source that emits white light.

[Effect of the invention]

According to the present invention, an image is generated by reading a radiation image, an autoradiography image, a chemiluminescence image, an electron microscope image and a radiation diffraction image of a subject recorded on the luminescent phosphor layer of the accumulative phosphor sheet. It is possible, and further, an image recorded on a light-transmitting material can be read to generate an image, and remains accumulated in the luminescent phosphor layer of the accumulative phosphor sheet. It becomes possible to provide an image generator capable of erasing the existing radiation energy, light energy, and electron beam energy.

[Simple explanation of drawings]

[Figure 1]

FIG. 1 is a schematic perspective view of an image generator according to a preferred embodiment of the present invention.

[Figure 2]

FIG. 2 is a schematic perspective view showing details of the vicinity of the photomultiplier.

[Fig. 3]

FIG. 3 is a schematic cross-sectional view taken along the AA line of FIG.

[Fig. 4]

FIG. 4 is a schematic cross-sectional view taken along the BB line of FIG.

[Fig. 5]

FIG. 5 is a schematic cross-sectional view taken along the CC line of FIG.

[Fig. 6]

FIG. 6 is a schematic cross-sectional view taken along the DD line of FIG.

[Fig. 7]

FIG. 7 is a schematic plan view of the scanning mechanism of the optical head.

[Fig. 8]

FIG. 8 is a schematic side view showing details of the vicinity of the stage 20.

[Fig. 9]

FIG. 9 is a block diagram showing a control system, an input system, and a drive system of an image generator according to a preferred embodiment of the present invention.

[Fig. 10]

FIG. 10 is a schematic front view of an image generator according to another preferred embodiment of the present invention.

[Fig. 11]

FIG. 11 is a schematic vertical cross-sectional view of the cooled CCD camera.

[Fig. 12]

FIG. 12 is a schematic vertical sectional view of the dark box.

[Fig. 13]

FIG. 13 is a block diagram around a personal computer.

[Explanation of symbols]

1 First laser excitation light source 2 Second laser excitation light source 3 Third laser excitation light source 4 Laser light 5 Collimator lens 6 mirror 7 1st dichroic mirror 8 Second dichroic mirror 9 Collimator lens 10 Collimator lens 12 mirror 13 holes 14 Perforated mirror 15 Optical head 16 mirror 17 Aspherical lens 18 Concave mirror 20 stages 21 glass plate 22 Image carrier 23 LED array 24 light 25 Fluorescent or bright light 28 filter unit 30 Photo Multiplier 31a, 31b, 31c, 31d filter members 32a, 32b, 32c, 32d filters 33 A / D converter 34 Image data processing device 35 reflective mirror 36 Convex lens 40 board 41 Sub-scanning pulse motor 42 guide 43 Movable board 44 rod 45 Main scanning pulse motor 46 Endless belt 47 linear encoder 48 slit 50 control unit 51 keyboard 52 Filter unit motor 53 Sub-scanning pulse motor 71 Cooled CCD camera 72 Dark box 73 personal computer 74 CRT 75 keyboard 76 CCD 77 Heat transfer plate 78 Peltier element 79 shutter 80 A / D converter 81 Image data buffer 82 Camera control circuit 85 glass plate 86 Heat dissipation fins 87 camera lens 90 stages 91 First red LED light source 92 Second red LED light source 93 filter 94 filter 95 filter 96 Array of white light sources 97 Diffusion plate 100 CPU 101 Image data transfer method 102 Image data processing device 103 Image data storage means 104 Image display means 105 Light source control means