JPS59500583A - Large-scale array of discrete ionizing radiation detectors multiplexed using fluorescent optical converters - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

[Detailed description of the invention] Background of the invention The present invention relates to a radiation transport imaging method and its apparatus, and more specifically, to columnar scintillation. This invention relates to an imaging device consisting of a combination of a detector and a fluorescent optical converter.

Radiation and radionuclide imaging devices have entered an era of rapid growth and development over the past 10 years. It broke in. Much of this movement is due to computerized tomography technology and new We are indebted to the introduction of advanced imaging equipment and image transport methods.

An example of a conventional imaging device is the Anga scintillation camera (U.S. Patent No. 3). ．． α11,057), which was developed in the 1950s. Since then, a wide variety of improvement plans have been proposed based on this. Also, it is relatively cheap. With the introduction of advanced high-speed computers, the image processing power of scintillation cameras improved. As a result, the clinical utility value has significantly increased.

This Unger camera uses a row of photomultipliers, e.g. Large, thin, flat scintillators such as sodium iodide (Na (11)) It is connected to the crystal via a flat light tube. scintillator (scintillator) A standard is placed in front of the ration crystal. Light transmitted through this standard The line hits the scintillator, and the spectral range is from ultraviolet to blue in the visible spectrum. It is converted into a ray that covers the area. This ray is then passed through the fiber optic filter. It passes through the pulley and enters the photomultiplier detector, where the total wave height voltage is The absorbed ionizing light photons are converted into electrical signals proportional to their energy. Shin The location of the chilling event is determined by the individual waves obtained from the photomultiplier. Calculated by mixing the high image width.

The detection object used for radioactive Mukuzo imaging must meet the following conditions. No.

1) High spatial resolution in determining the location of scintillation events 2) Confirmation and rejection of gamma photons scattered within the light source or standard (light source scattering rejection) ) and detection object scattering) confirmation and rejection of gamma photons scattered within the object itself. energy resolution, sufficient to do 3) suitable count rate and small dead time; 4) suitable gamma absorption rate (minimum reliability); issue loss).

In addition to the above conditions, even if it is desirable for an imaging device, it is difficult to obtain in reality. There are also many other interesting characteristics, some examples of which are listed below.

1) After being scattered within the scintillator, it is reabsorbed by other parts of the scintillator. 2) the ability to reject gamma photons that the ability to increase the absorption rate of incident gamma photons without degrading 3) the ability to provide digital information for computer storage and processing; 4) No movement or instability occurs over time, and both surfaces of the detection object There shall be no inhomogeneity between the edges.

The above characteristics reduce costs, simplify the work, and reduce the amount of radiation delivered to the patient. In addition to the problems of increasing efficiency (in the sense of image quality for radionuclides), several problems have been The use of alternative imaging devices has been explored throughout. One of the solutions is It is embodied in the form of a fluoroscope. This device uses a light tube to scintillators are coupled to one row of photomultipliers, and the system used is The number of ventilators is several hundred. A similar device is a scintigraphy plane. such as those configured as array or ring cameras for positron emission tomography imaging. be.

However, there are several problems with this autofluoroscope and similar devices.

One method is to send light from a scintillator to a photomultiplier via a light tube. is both inefficient and non-uniform. Therefore, the energy solution Both image quality and light source scattering rejection ability deteriorate. In addition to this, the above devices are non-structural. It always gets complicated. This is because each scintillator element has one light tube and one light transmitter. The guide must be individually and reproducibly connected to the spatula J. As a result, there are 315 scintillators for one row of 294 scintillators. This is because a light tube of For this type of equipment, medium-sized However, the number of photomultipliers required for that address is large.

” Jiang Accordingly, it is an object of the present invention to develop a new and improved scintillator array using relatively large scintillator arrays. It is an object of the present invention to provide a light beam imaging device that has the following characteristics. Another objective is high spatial resolution, high gamma It has photon absorption efficiency, high light source, detection object rejection ability, and does not require expensive photomultipliers. Using low-cost solid-state optoelectronic devices instead of chipliers Therefore, it is an object of the present invention to provide a detection object whose cost is significantly lower than that of conventional products. In addition, Other objects, features and advantages will be apparent from the following description and the appended claims. .

In practicing the invention, in one embodiment, when absorbing ionizing radiation, A photodetector comprising a row of optically separated photosensitive elements, each of which has a property of emitting ・A conversion device is provided. The channel array directs the light rays emitted from the photosensitive element. absorbs and captures the beam, and transmits the beam after converting it to a longer wavelength. The array of channels is made of a material that can be It is located in An electro-optical detector that converts the transmitted light beam into an electrical signal is connected to this cham- ber. connected to the channel. Electron optics by light generated from one of the channels If one of the detected objects becomes active, this causes the sensing in the vicinity of the channel It can be seen that at least one of the optical elements has absorbed an amount of ionizing radiation.

Brief description of the drawing The present invention, including its aspects, objects, advantages and features, uses the same reference numerals to refer to similar parts. A more complete understanding may be obtained by reading the following description and referring to the accompanying drawings as indicated by the numbers. You will be able to understand it.

Figure 1 shows scintillators (detectors) arranged in rectangular rows and luminescent collectors. A scintillator-detection body array of the present invention arranged near a light (LLC) material strip FIG. 2 is an exploded perspective view of one embodiment of the invention. Made of LLC material on the top side of the scintillator row The tea bodies are aligned in a certain direction (e.g., on the X axis) and L on the bottom side of the scintillator row The LC material strips are aligned in the orthogonal direction (on the Y axis).

Figure 2 shows the luminous intensity and detection object for various components of the scintillator array shown in Figure 1. FIG. 2 is a graphical diagram showing reactivity versus wavelength.

Figures 3a and 3b are schematic diagrams showing the detector/preamplifier array for the apparatus shown in Figure 1; It is a diagram.

FIG. 4 is a block diagram showing an example of a form of signal processing for the scintillator-detector array shown in FIG. It is a lock diagram.

FIG. 5 is a partially cutaway perspective view of a modification of the present invention.

FIG. 6 is a partial plan view of a column used in a modification of FIG. 5.

FIG. 7 is a schematic diagram of a curved row.

FIG. 8 is a schematic illustration of a row with ends bent in alternating directions.

Now, referring to FIG. is constructed by housing a plurality of ordinary scintillator detection crystals 12 in a row frame 14. It is something that The flat glass plates, i.e. wA fused quartz plates 16 and 18, are each cinch A light emission condenser consisting of a detector detector 12 and a plurality of light emission condensers 25, Uminesent 1iqht collector) (LLC)) Column 20 and 22 are interposed between the ends. The light collector 25 constitutes a light conducting channel. It is a rod. The end of the scintillator-detector 12 is optically connected to one side of the plates 16 and 18. are connected to each other. facing opposite sides of plates 16 and 18, i.e. 110 rows 20 and 0.22 The side surfaces of the panels are preferably coated with an anti-reflection coating, and the plates are separated by a thin air gap. and is spaced apart from the LLC column. Plates 16 and 18 are scintillator-detecting It acts as a seal to prevent the array 10 from coming into contact with the surrounding environment.

LLC channels 25 in row 20 are aligned in the X-axis direction, and channels 25 in row 22 are aligned in the X-axis direction. They are aligned in the Y-axis direction.

In FIG. 1, each component is shown as flat and rectangular for illustrative purposes. However, these are based on positron ring cameras, emission tomography devices, and computerization. For example, as shown in Figure 7, the curved shape can be used in applications such as tomography equipment. Of course, it may also be in the form of

LLC25 absorbs light at certain wavelengths in plastic, quartz, or glass; doped or coated with one or more fluorescent dyes that emit light at longer wavelengths. It is a channel-shaped element made of a solid rod made of cloth.

It can also be constructed by filling the tube with a solvent containing the desired dye.

The required dye may be mixed with the physical medium constituting the LLC or applied to the 110 surface. Laser dyes such as rhodamine and coumarin structured in the form of the coating being applied. It can be used as a fee. The three surfaces of the ILc rod 25 are surrounded by diffusion repellent material. but the fourth surface facing the scintillation detection column 10 is coated with a mixture of fluorescent dyes. It's a reversal. In some cases, the scintillator may be surrounded by a dye-containing medium. It is also possible to change the wavelength. In this case, the LLC simply reflects diffusely on its three sides. It is nothing more than a tube surrounded by wood. The ends 26 of the LLC row are typically separated by a narrow air gap. connected to the reflected reflector. The other end 28 has photodiode rows 30 and 3. It is optically coupled to a suitable electro-optical element such as 2 or the like.

The light generated from the fluorescent dye is reflected by specular (total internal) reflection (to the refractive index of the LLC medium). (determined by) within the angular range defined by Snell's law. Therefore, this The captured light is conducted by successive reflections to the ends 28 of the LLC columns 2o and 22, where It is converted into an electrical signal based on the intensity of the light received by the foot diodes 30 and 32. will be replaced.

Preventing optical crosstalk between each scintillator in the scintillator row 10 and the detection crystal 12 , as well as improving the ability to extract light from each detection crystal. This can be achieved by disposing it on the surface or coating it on the surface. this purpose Barium sulfate or magnesium oxide diffuse reflectors are suitable for this purpose. cinch The end of the detector detector 12 facing the LLC channel 25 is polished. When combined with glass or fused silica plates 16 and 18, the row 10 is sealed. can be done. These plate members are preferably coated with an anti-reflection coating, and The LC channel 25 is separated from the neighboring plate members 16 and 18 by a narrow gap. It is better to be Occurs when the scintillator-detector 12 absorbs the radiation derivative The emitted light first reaches the end of the scintillator-detector, and then passes through the glass end plate 16 and and 18, enter the 110 rows 20 and 22, and after being absorbed there, the longer wave Re-emitted in long form. Alternatively, this wavelength conversion of light can be performed using scintillator detection. By surrounding the wavelength conversion medium around the scintillator-detecting body, It can also be done. In other words, the light whose wavelength has been converted in this way is sent to the LLC rod. , it is also possible to absorb light here.

110 channels (channels) 25 are normally connected to the detection body 12 used in column 1o. They have the same width and are each aligned with a row of scintillator-detectors. Furthermore, Shin The surface of the 110 strips 25 on the side facing the chiller row 10 is a special dielectric object. It is preferable that the scintillator is coated with a scintillator. (short wavelength optical radiation) can enter into the 110-striped body 25, and this 110-striped body After being re-emitted in the form of longer wavelength light by said dye within the (See Figure 2). Therefore, within the 110th article 25 Since the absorbed and re-emitted light is captured within these 110 stripes, the scintillator - cannot return to column 10; In addition, 1 on the side not facing the scintillator row Around the surface of the 10-strip body, there is a diffuse reflection material such as the scintillator coating described above. All materials are provided.

Figure 2 shows the light emitted from the scintillator (assumed to be NaI (Ti)). interspectral properties, absorption and emission spectra of LLC dyes, scintillator column sealing Therefore, the reflectance of the dielectrics interposed between the LLG and the plate member, and the photodiode The sensitivity of is illustrated. The device of the present invention optimizes the relationship between these various spectra. It is designed to be optimized. That is, in this device, the scintillator-1 The selection of the electroscope, LLC dye, and photodetector eliminates wasted radiation from the scintillator. The dye in the LLC channel can be easily and efficiently captured and transferred to the photodetector. The structure is designed to maximize the reactivity of the photodetector to the light emitted from the source. This is done on the basis of matching.

Tight backing of LLC channels and rows at LLC25 ends To avoid overcrowding of the electro-optical detectors at 30 and 32, the ends of the LLC channels are , for example, as shown in FIG. 8, it can be changed to a curved or bent shape.

In this case, the electro-optical detectors are located above and below the plane formed by the LLC channel. could be arranged in alternating fashion.

The light absorbed within the 110 stripes (i.e. LLC channel) is detected by the electro-optical detector 30. and 32, but this detector absorbs this light and converts it into a scintillator. converts the photons into an electrical signal proportional to the number of photons generated by the sensor.

The detector can be arranged in a compact array and can be Cooling by cooling module 36 (see Figure 3b) to further reduce noise. You can also do it.

Therefore, when a certain scintillator-detector 25 generates a certain pulsed light, This light reaches two adjacent LLC channels and is absorbed by these channels. and regenerated at the wavelength captured in the LLC channel.

This wavelength-converted light is sent to the end of the LLC channel 25 and placed here. The electro-optical detectors 30 and 32 are operated. Therefore, certain electro-optical If the ejected object detects pulsed light, the position of the scintillator that is the source of the light is The measurements sent from the electro-optical detector are encoded as The number of electrical pulses completed is proportional to the energy of the initial gamma photon.

One of the main advantages of the above configuration is that it provides compact, low-cost solid-state electro-optical inspection. It is possible to use a photomultiplier tube instead of a photomultiplier tube, which is much more expensive than a photomultiplier tube. Ru.

It confines the light generated from the scintillator into a narrow LLC channel. This is because it can be placed in A low-noise detection object is no longer required, and instead a small, low-noise individual detector with a small active area is used. This is because the element can be used. Furthermore, this solid state detector is can be designed to incorporate electro-optical elements necessary for signal amplification, analysis and encoding. There are also advantages.

The device described above is improved by using individual scintillator elements. It has now become possible to obtain spatial resolution that was previously impossible to achieve. Also, scintillation The light emitted from the sensor is directed toward the photodetector with amazingly high efficiency (approximately 50-60%). The energy of the incident gamma photon can therefore be measured accurately. and thus became able to reject confusion. Furthermore, a certain cinch The gamma photons scattered within the scintillator are scattered by the continuous scintillator in the same column If absorbed, the resulting signal can be rejected.

This is because a larger number of electro-optical detectors than the allowable number will respond.

This ability to reject detector scattering makes it possible to use thick scintillation crystals. This can be done without much deterioration in image quality. Therefore, the The gamma photon absorption efficiency is higher than that of conventional equipment, and this high absorption It is possible to detect radionuclides of various energies without significantly changing the image quality. while producing clinically useful images in the least amount of time and with the least amount of radiation to the patient. It can be formed by rays.

The second configuration was arranged in an orthogonal manner but placed on the same side of the scintillator array. It uses two group LLC channels. In this case, the first group The channels absorb most of the radiation generated by the scintillator, and The remaining portion is placed immediately after the first group's LLC channel. or transmit a portion of the radiation to the second group as radiation with a longer wavelength. It can be designed so that it can recur into a loop. Advantages of this configuration In addition to making the entire device more compact, this method also enables gamma photon scintillation. Eliminates the need for LLC channel groups to prevent transmission into the data row. Ru. However, the big problem in this case is that it is more difficult to prevent crosstalk between LLC channels. scintillator, and therefore the loss of light generated by the scintillator is greater. This is a possibility.

The third configuration includes one group of LLC channels at the bottom of scintillator row '10. 25 and place an electro-optical element at one end of each LLC channel. This is what I did. This is an X-ray directed perpendicular to the long axis of the LLC channel. The fan beam essentially determines one of the position coordinates of the scintillator-detector 12. This takes advantage of the fact that The preferred use of this configuration is for CA T-scans and digital radiography are contemplated.

In the example of a radionuclide imager, the scintillator array has 16,384 individual crystals. It is best to make it by combining crystals. Each scintillator has a size of 2 x 2 x 2 5mm, and a diffuse reflective material separated from the crystal through a narrow gap. By using this, it is possible to optically separate adjacent scintillators.

Such scintillators are most conveniently made by extrusion. scintillator The tar is arranged in a 128 x 128 matrix and is approximately 254 x 254 mm. (10 x 10 inches) in the form of a block with a thickness of 25.4 mm (1 inch) It is configured. The LLC channel is an optically transparent thin-walled glass. , the light emitted from the scintillator is confined in a narrow channel, making it difficult to operate. Using a photodetector with a very small surface area (preferably less than 25 mm2) I can do it. The smaller the detection object area is, the smaller the detection object noise will be. Ru. However, solid-state photodetectors still often and the noise is relatively high, making it unsuitable. Small PIN silicon photo die Ord is dark current and! Low sound, therefore 110 connected to the end of the channel By doing so, it can be used directly, usually without cooling treatment.

To further enhance the performance of these detectors, a low noise preamplifier 38 (see Figure 3a) can be used. and 3b) directly onto the photodiode silicon chip 40. It is preferable to cool the chip using a thermal lightning (Beltier) module 36.

It is also desirable to arrange the photodiodes in large arrays on a single chip; As a result, it is possible to reduce costs and simplify combining multiple LLC channels. I can do it. The specifications of the detection object in one embodiment of the scintillator array are as follows. Ru.

Photodiode active area 2.1x 2.1mm Photodiode dark current (Room temperature) 0.8 nA photodiode dark current (-50℃> 6 DA photo Diode, number of 7 rows: 16 Number of photodiode rows in a group Total number of photodiodes in 6 groups 128 preamplifier gain approximately 1000 The scintillator quantum quantity increases with temperature, and the relaxation time decreases with temperature. Therefore, it is best to heat the scintillator inside the column. In the case of the present invention, It is possible to heat the scintillator and cool the photodetector at the same time. because , because both are separated from each other by an LLC channel. temperature By controlling in this way, the performance of the device of the present invention can be improved by keeping the entire device at ambient temperature. It has become possible to significantly improve the performance compared to when operating.

The signal generated by the electro-optical element (detector) can be detected in the usual way, for example as illustrated in FIG. It can be processed using the following method. Each detector in the array is equipped with a preamplifier and , other electronic devices for signal processing arranged in groups, e.g. Reference numerals 30a and 32a correspond to detector arrays 30 and 32 in FIG. The device can be equipped with the following. From LLC 20 and detection object 30a The signal generated is transmitted by a matching circuit 40 to the scintillator column 10 located on the other side. from an electro-optic detector 32a coupled to a second group of LLC channels 22 It is checked whether it matches the generated pulse. In addition, the matching circuit 40 , if two or more scintillators generate a signal at a certain time, this signal is Reject. Once this match and mismatch check has been performed, the electro-optical device The signals generated from 30a and 32a are summed and pulse summed/pulse adjusted. It is amplified in the shape circuit 42 to form the peak of the scintillator event. child The wave height applied to the double discriminator 44 is within a certain range. If the activated scintillator is given in the form of the X and Y coordinates of the activated detector, The position of the element is in digital format, Δ, N D gate 4G and digital gate ・Sent to either the recording device or the display device 11 or both via the buffer 50 It will be done. Detector/amplifiers 30a and 32a are connected to column multiplexer 52 and group The signals are individually multiplexed or extracted by multiplexer 54.

Devices of the type described above can be designed to perform a variety of functions. for example , the array is curved to form a ring, and the LLC is arranged adjacent to the sensing element of the curved array. as emission tomography, digital radiography, or computerized tomography. When used for layer photography, it is possible to use multiple projectors without physically moving each object to be detected. Scanning can be performed without simultaneously collecting information from.

Alternatively, the scintillator may be a single group of LLC rods aligned in a single direction. The X It can also be exposed to a fan beam of lines. In this case, for a single group The LLC rods (channels) alone are sufficient to absorb the radiation received by the elements in the array. Can be analyzed and evaluated.

Now, another application of the device of the invention is in cardiac and respiratory scanning devices, i.e. radioactive It is used as a device to monitor the rapidly changing spatial distribution of nuclide-labeled materials. . Furthermore, the present invention can also be applied to fluoroscopy. i.e. standard radiation x-ray It can also be used to monitor film exposure to obtain the optimum exposure. be.

5 and 6 show an example in which the present invention is applied to exposure adjustment of X-ray film. There is. In FIG. 6, a matrix 58 of rods or LLC channels 60 is shown in FIG. arranged in crossed rows, i.e. parallel with one group spaced apart channels are aligned in the “X direction” and the spaced apart parallel channels The channels are aligned in the "Y-axis direction." At the intersection between channels 60, a small amount A powder or thin plastic scintillator 62 is placed closest to the radiation. It is arranged on the top surface of the channel where it is placed. The scintillator 62 receives a small amount of incident ionization. Converts radiation into pulses of light. Note that this light pulse is located at the position of the blocked light beam. L　L　C channel to the photodetector 64 positioned at the end of the channel for identifying Sent by Nell.

An alternative to the above configuration is to use a single group of 11-C channels. It is possible. That is, at only one location on each LLC channel, a small amount of powder A thin plastic scintillator 62 is placed near the light beam. placed on the top surface of the channel. As in the case of the above configuration, the photodetector is connected to each LLC channel. The advantage of this configuration is that it provides fast reactions and , it is possible to take a wider exposure position.

In FIG. 5, the matrix 58 is attached to a conventional X-ray film and screen device 70. are adjacently disposed and exposed to x-ray radiation. Furthermore, this ray is The device 70 is configured to collide with the device 70. disposed at the end of the LLC channel 60 The signals generated from the photodiodes are multiplexed to the X and Y groups. Determine the source of the pulse sent from channel 60 and collect the information. It is sent to microprocessor 72 for encoding and recording. microprocessor 72 is tested and sorted by an algorithm given to it by the calibrator 74. Recordings at various intersections of LLC channels across the X-ray film of device 70 If the desired distribution of rays is confirmed, it will automatically generate a signal to Stop exposure.

Alternatively, the exposure control device may include a single row of LLC rods aligned in a single direction. channel), but in this case, the scintillator It is possible to extract the entire area to be monitored by positioning it in different parts over a long period of time. Do it like this. In general, this method requires only the required number of LLC channels and photodetectors C. This is not desirable as it results in a large number of parts, but only a very limited number of parts can be extracted. This may be appropriate if the exposure received by the X-ray film can be accurately measured at This is a very sad method. A dimension sequence also includes a second seat formed by the fan-shaped scanning beam. It is also possible to extract by mark.

The present invention is useful for thin layer chromatograms and electrophoresis in the biological and chemical research fields. It can be used to scan moving gels or strips of compounds called radioactive. can. Other uses include X-ray telescopes, mass spectrometers, X-ray fluorescence spectrometers, and flight Row-time spectrometers, or those that benefit from column processing of ionizing radiation or particles. There is a wide range of equipment used in pond equipment. The present invention is suitable for large-scale arrays and Since it can use digital processing technology, it is highly versatile.

It is possible to modify and change the specifications according to the actual operating conditions and usage environment. It will be obvious to those skilled in the art that the present invention is limited to the scope chosen for illustrative reasons. The present invention is not limited to examples, and may be implemented without departing from the true spirit and scope of the invention. This includes all changes and modifications.

Kure 3a map Copy and translation of written amendment) Submission form 1. Viewing patent applications PCT/υ583100556 2. Name of the invention multiplexed using a fluorescent optical converter Large-column discrete ionizing radiation detector 3. Patent applicant Address: Town, Westboat, CT 06880, United States Crya Rain 5 Names Koslow Chikunorosies Corporation Representative Person Koslow, Engineering Van Yi.

4. Agent 2-14-1 Shimogo, Shinjuku-ku, Tokyo Scope of request [Received by the International Bureau on September 30, 19133: Amendments to paragraphs 1 to 9 of the original claims Correct, original claims 10 to 22 are not amended. ]1. Radiation stimulator a row of optically separated individual radiation-sensing elements that absorb and emit light; It receives and captures the light rays emitted from the sensing element array and directs the light rays along itself. a row of elongated (and parallel) channel members arranged to convey coupled to at least one end of the channel for converting the carrier beam into an electrical signal. , each of the electrical signals causes at least one of the radiation sensing elements to detect the radiation stimulator. a row of electro-optical elements configured to indicate absorption; A radiation detection/conversion device consisting of.

2. The channel arrays are arranged in at least two groups orthogonally. channels, each of said radiation sensing elements being connected to at least one of said orthogonal channels. is also located in one vicinity, and the ends of said orthogonal channels are located in one vicinity of said electro-optical element. optically coupled with one or more of the The operation of the electro-optical element changes the position of the radiation sensing element that has absorbed the ionizing radiation of a certain ink. 2. Apparatus as claimed in claim 1, adapted to encode the position of the user.

3. The channel rows are arranged at an angle to each other, i.e. at 90 degrees to each other. A claim consisting of at least two groups of channels in the direction of ° Apparatus according to scope 1.

4. The channel rows are aligned at opposite ends of the radiation sensing element row. 2. The device according to claim 2.

5. The plurality of channel groups are located on the same side as the radiation sensing element row. The Brennel of the first group is immediately adjacent to the radiation sensing element. absorbs only a portion of the light rays emitted from the radiation sensing element array. without, the majority of the light emitted from the radiation sensing elements in this row is in the said channel. Claims 2 or 3 which are made transparent to the second group of equipment.

6. Each channel in the channel row has a reflective material over the area on its periphery. An apparatus according to claim 1, comprising:

7. Absorbing light rays emitted from the channel array or the radiation sensing element and convert the absorbed rays into longer wavelength rays that are captured within the channel. 2. A device according to claim 1, comprising a fluorescent dye medium.

8. A dye medium is interposed between the radiation sensing element and the channel array. A device according to claim 1.

9. A portion of the channel row facing the radiation sensing element row is connected to the radiation sensing element row. Selective light transmission is performed at the wavelength emitted by the radiation sensing element, and the wavelength emitted by the fluorescent dye is transmitted selectively. 8. A device according to claim 7, which provides efficient reflection at long distances.

10. The channel comprises a stream comprising a solvent containing one or more fluorescent dyes. 8. The device of claim 7, wherein the device is a thin-walled tube containing a body.

11. The channel is made of plastic, glass, quartz or other transparent material The material is coated with a fluorescent dye medium that absorbs light at short wavelengths and emits light at longer wavelengths. 8. The device according to claim 7.

12. The channels absorb light at short wavelengths and emit light at longer wavelengths. The claim consists of a solid rod with a transparent medium containing a photodye. Apparatus according to paragraph 7.

13. The channel is a long thin strip having approximately the same width as the elements of the radiation sensing element array. 9. The device according to claim 7 or 8, which is a body.

14. Curving or bending the ends of the channel and alternating the channel bends. The electron optics are tightly wrapped around the channel by lower placement and are coupled to the ends of the channel. Claim 7 or Apparatus according to paragraph 8.

15. One or more channels of the channel row may be curved. The device according to item 1 of the scope of demand.

16. The device according to claim 1, wherein the radiation sensing element is a scintillator. Place.

17. The elements of the radiation sensing element row are C3I (Tg, ), Na I (Tl i>, Cs I (Na), bismuth germanate, plastic thin Chylator-1 Organic scintillator 1 Liquid scintillator-1 and heavy metal compound included liquid scintillator. equipment.

18. The electro-optical element is a solid metal having a working surface area of less than 25 mm2. Claim 1 or 2 which is a state PIN silicon photodiode. Equipment described in Section.

19. The electro-optical element is exposed to ionizing radiation in several channels. It is possible to encode the position of the channel through which the light rays generated by the elements of the ray-sensing element array are transmitted. 3. A device according to claim 1 or 2, wherein the device is coupled in such a manner that the

20, the elongated parallel channel rows are spaced apart and arranged in a predetermined pattern; The radiation sensing element array is positioned in the predetermined pattern, and the channel array is arranged in the predetermined pattern. Combine the pattern with the X-ray film to be exposed and monitor the exposure state of the X-ray film. 2. The device according to claim 1, which is capable of controlling

21. Each row of the radiation sensing element, the channel and the electro-optical element is a curved row. Apparatus according to claim 1.

22. Each row of the radiation sensing element, channel and electro-optical element is ring-shaped. 2. The device according to claim 1, wherein the device is a column.

Claims (1)

[Claims] 1. A row of optically separated individual cells that absorb radiation stimulators and emit light rays. a radiation sensing element for receiving and capturing the light rays emitted from the array and for transmitting the light rays; a row of elongated and parallel channel members conveyed along the coupled to at least one end of said channel to transmit said carrier beam to an electrical signal; and each of the electrical signals causes at least one of the radiation sensing elements to detect radiation. A row of electro-optical elements configured to indicate absorption of a stimulant. A radiation detection/conversion device consisting of. 2. The channel arrays are arranged in at least two groups orthogonally. channels, each of said radiation sensing elements being connected to at least one of said orthogonal channels. is also located in one vicinity, and the ends of said orthogonal channels are located in one vicinity of said electro-optical element. optically coupled to one or more of the The electro-optical element of the combination absorbs a certain amount of ionizing radiation during operation. 2. The device according to claim 1, characterized by the location of the sensor element. 3. The channel rows are arranged at an angle to each other, i.e. at 90 degrees to each other. A claim consisting of at least two groups of channels in the direction of ° Apparatus according to scope 1. 4. The channel rows are aligned at opposite ends of the radiation sensing element row. 2. The device according to claim 2. 5. The plurality of channel groups are located on the same side as the radiation sensing element row. and the channels of the first group are immediately adjacent to the radiation sensing element. absorbs only a portion of the light rays emitted from the radiation sensing element array. without, the majority of the light emitted from the radiation sensing elements in this row is in the said channel. Claims 2 or 3 which are made transparent to the second group of equipment. 6. Each channel of said channel row has a 2. The device according to claim 1, further comprising a reflective material over a wide area. 7. The channel row absorbs the light rays emitted from the radiation sensing element. and convert the absorbed rays into longer wavelength rays that are captured within the channel. a fluorescent dye-containing medium or coated with such a medium. The device according to item 1 of the scope of demand. 8. A dye medium is interposed between the radiation sensing element and the channel array. A device according to claim 1. 9. A portion of the channel 1j11 facing the radiation sensing element array, selectively transmitting light at the wavelength emitted by the radiation sensing element, and emitting light from the fluorescent dye; 8. A device according to claim 7, which provides efficient reflection at wavelengths of . 10. The channel is made of a solvent containing one or more fluorescent dyes. 8. The device of claim 7, wherein the device is a thin-walled tube containing a fluid. 11. The channel is made of plastic, glass, quartz or other transparent material The material is coated with a fluorescent dye medium that absorbs light at short wavelengths and emits light at longer wavelengths. 8. The device according to claim 7. 12. The channels absorb light at short wavelengths and emit light at longer wavelengths. The claim consists of a solid rod with a transparent medium containing a photodye. Apparatus according to paragraph 7. 13. The channel is an elongated strip having approximately the same width as the elements of the radiation sensing element array. 9. The device according to claim 7 or 8. 14. Curving or bending the ends of the channel and alternating the channel bends. The electron optics are tightly wrapped around the channel by lower placement and are coupled to the ends of the channel. Claim 7 or Apparatus according to paragraph 8. 15. One or more channels of the channel row may be curved. The device according to item 1 of the scope of demand. 16. The device according to claim 1, wherein the radiation sensing element is a scintillator. Place. 17. The elements of the radiation sensing element row are Cs1(T(ri, NaI(Tf), Cs (Na), bismuth germanate, plastic scintillator 1 Organic scintillator 1 Liquid scintillator-1 and heavy metal compound-containing liquid scintillator A device according to claim 1 selected from among five groups consisting of: . 18. The electro-optical element is a solid metal having a working surface area of less than 25 mm2. Claim 1 or 2 which is a state PIN silicon photodiode. The equipment described in section. 19. The electro-optical element is exposed to ionizing radiation in several channels. It is possible to encode the position of the channel through which the light rays generated by the elements of the ray-sensing element array are transmitted. 3. A device according to claim 1 or 2, wherein the device is coupled in such a manner that the 20, the elongated parallel channel rows are spaced apart and arranged in a predetermined pattern; The radiation sensing element array is positioned in the predetermined pattern, and the channel array is arranged in the predetermined pattern. Combine the pattern with the X-ray film to be exposed and monitor the exposure state of the X-ray film. 2. The device according to claim 1, which is capable of controlling 216 Each row of the radiation sensing element, channel, and electro-optical element is a curved row. The apparatus according to claim 1. 22. Each row of the radiation sensing element, channel and electro-optical element is ring-shaped. 2. The device according to claim 1, wherein the device is a column.