RADIATION IMAGE INTENSIFIER TUBES

Abstract: A multistage, radiation image intensifier tube having improved performance characteristics and more rugged construction. The tube has a scintillator assembly (22) comprising a first ceramic, cellular substrate (26) defining an array of hexagonally shaped cells. The cell walls taper to an edge and are coated with a conductive material (28) such as aluminum. The cells are filled with a scintillation material (30) such as cesium iodide. A first flat photocathode (24) is provided adjacent the first substrate. An intermediate assembly (34) spaced from the scintillator assembly (22) is provided comprised of a second ceramic, cellular substrate (36) similar to the first. The cell walls are coated with a conductive material (38) such as aluminum. A support layer (40) is mounted to the substrate (26) on an end opposite the scintillator assembly (22). A first flat phosphor display screen (42) is mounted to the support layer (40) on a side internal the second substrate (36). A second photocathode (46) is provided adjacent the second substrate (36). An output assembly (48) spaced from the intermediate assembly (34) is provided and is comprised of a third ceramic cellular substrate (50) which is similar to the first and second substrates (26 and 36). The cell walls are coated with a conductive material (52) such as aluminum. A second flat phosphor display screen (58) is mounted to the third substrate (50) on an end opposite the second substrate (36). An output window (56) mounted to the tube envelope (12) and adjacent the second display screen (58) is provided. Means (62) are provided for applying separate electrostatic potentials between the various substrates (26, 36, 50).

Description: This invention relates to radiation image intensifier tubes, more particularly to x-ray image intensifier tubes of the proximity type suitable for medical x-ray diagnostic use. In US-A-4,255,666 a two-stage, proximity type image intensifier tube is described. This device incorporated two stages of amplification in an effort to provide improved gain over that of a single-stage device described in US-A-4,140,900. The two stage device described in US-A-4,255,666 incorporates a flat scintillator screen, an output display screen and an amplification means intermediate to the scintillator screen and the output display screen. The two stage image intensifier tube comprises a metallic vacuum tube envelope and a metallic, inwardly concave input window. In operation, an x-ray source generates a beam of x-rays which passes through a patient's body and casts a shadow onto the input window of the tube. The x-ray image passes through the input window and impinges upon the flat scintillation screen which is deposited on an aluminum substrate. The scintillation screen converts the x-ray image into a light image. This light image is "contact transferred" directly to an immediately adjacent first photocathode layer which converts the light image into a pattern of electrons. The scintillation screen and photocathode layer comprise a complete assembly. A first phosphor display screen is mounted on one face of a fiber optic plate which is suspended from the tube envelope by means of insulators. On the opposite face of the fiber optic plate a second photocathode is deposited. The fiber optic plate is oriented in a plane substantially parallel to the plane of the scintillation screen. A second phosphor display screen is deposited on an output window. A high voltage power supply is connected between the first phosphor display screen and the first photocathode as well as between the second photocathode and the second phosphor display screen. The power supply provides approximately 15 kV to each stage (approximately 30 kV total). The first display screen and the second photocathode are connected together and operate at the same potential. In operation, the electron pattern on the negatively charged first photocathode layer is accelerated towards the first, positively charged (relative to the photocathode layer) phosphor display screen by means of the electrostatic potential supplied by the high voltage source connected between the display screen and the photocathode screen. The electrons striking the display screen produce a corresponding light image which passes through the fiber optic plate to impinge on the second photocathode. The second photocathode then emits a corresponding pattern of electrons which are accelerated toward the second phosphor display screen to produce an output light image which is viewable through the output window. While the two-stage device described above did achieve fundamental performance improvements in gain as well as other parameters over the single-stage device, it still did not achieve the performance of conventional inverter type x-ray image intensifiers. Performance of the two-stage device is found to fall short in three distinct areas: brightness gain, contrast ratio and limiting resolution. The two-stage device has a conversion brightness of approximately one-third that of conventional inverter type tubes. This difference is due in part to the fact that the two-stage device is a unity magnification device while conventional inverter type tubes are typically X10 demagnification devices. This difference translates directly to a 100 fold increase in conversion gain. The image size of the inverter type tube is however only 1/10th that of the two-stage device. The two-stage device did achieve a threefold increase in gain over the single-stage device by the incorporation of the fiber optic element. This element, however, added significantly to the cost of the device, increased its overall weight and reduced its ruggedness as well. Further increases in gain have not been achieved due to the prohibitive cost of providing additional stages of amplification of the inability to further optimize the efficiency of the various layers which comprise the two-stage device. Image contrast of the two-stage device has also been found inferior to the conventional inverter type tubes. Typically large area contrast ratios for the inverter tubes are better than 20:1 while the two-stage device exhibits a 15:1 contrast ratio. The loss of image contrast in the two-stage device is primarily due to reflected light and backscattered electrons within the space between the photocathode and phosphor layers. In inverter type tubes the same problems exist but to a lesser degree since the large space between the single photocathode and phosphor layers allow for a substantial amount of dispersion. Attempts to improve the performance of the two-stage device through the incorporation of anti-reflection layers and optimization of the aluminum layer coatings on the phosphor screens have rarely achieved the 20:1 contrast of the inverter type tubes. Resolution is a measure of how faithfully an optical device reproduces detail. In this respect, the two-stage device suffers in performance by up to 30% due largely to the extreme sensitivity of its proximity focussing technique to the surface texture of the cesium iodide scintillator. This degradation is compounded by optical and x-ray scattering within the scintillator. Thinner scintillators or scintillators composed of finer crystals could offer improvements. However, thinner crystals reduce scintillator efficiency and gain while a finer crystal structure further roughens the surface. It is an object of this invention to overcome the above referenced problems and others by providing an improved multi -stage radiation image intensifier tube whose performance is comparable to that of conventional inverter type tubes. According to the present invention there is provided a multistage radiation image intensifier tube wherein at least one stage comprises a substrate of substantially non-secondary electron emitting material which defines a plurality of cells which extend through the substrate and are substantially aligned with the path of the radiation or electrons incident on that stage, the walls of the cells tapering continuously to a sharp edge throughout the thickness of the substrate, the taper being towards the side of the substrate on which the radiation or electrons is/are incident. Preferably the cell walls have a coating of electrically conductive material, e.g. aluminum, vapour deposited to a thickness of 10⁻⁴mm. The substrate is suitably of ceramic material and formed by etching. The cells are suitably hexagonal and form a honeycomb structure. One particular intensifier tube according to the invention comprises: a tube envelope; an input window in the tube envelope; a scintillator stage mounted in the envelope for converting impinging radiation into a first pattern of liberated electrons; means for accelerating said first pattern of electrons along a first path; an intermediate stage mounted in the envelope along said first path and spaced from the scintillator stage for receiving said first electron pattern and converting said first pattern into a second pattern of liberated electrons; means for accelerating said second pattern along a second path; and an output stage mounted in the envelope along said second path and spaced from the intermediate stage for receiving and converting said second pattern into a visual image pattern; at least one of said scintillator, intermediate and output stages incorporating a said substrate defining a said plurality of cells. In one such particular tube the scintillator stage comprises a said substrate defining a said plurality of cells whose walls are coated with a conductive, reflective layer; scintillator material filling the space between the walls of said cells; and a flat photocathode layer mounted substantially parallel and immediately adjacent to the substrate. The intermediate stage suitably comprises: a said substrate defining a said plurality of cells whose walls are coated with a conductive layer; a support layer mounted to one end of the substrate; a phosphor layer applied to the support layer on the side adjacent the substrate; and a photocathode layer substantially parallel and immediately adjacent the support layer mounted on the side opposite the phosphor layer. The output stage suitably comprises: a said substrate defining a said plurality of cells whose walls are coated with a conductive layer; an output window mounted to one end of the substrate; and a phosphor layer applied to the output window on the side adjacent the substrate. The particular tube according to the invention comprising scintillator, intermediate and output stages of the above specified form suitably further includes electrostatic potential means for applying separate electrostatic potentials between the substrates of the scintillator and intermediate stages on the one hand and between the substrates of the intermediate and output stages on the other hand to accelerate electrons from said photocathode layers of said scintillator and intermediate stages respectively onto said phosphor layers of said intermediate and output stages respectively along substantially straight trajectories. In DE-A-3325035 there is described a multistage radiation image intensifier tube including a scintillator stage incorporating a cellular substrate the cells of which are filled with a scintillator material . However, this specification is primarily concerned with providing that the cells are inclined to the path of the radiation to reduce shadowing by the cell walls rather than the relative dimensions of the cell width and length. In US-A-4100445 there is described a multistage radiation image intensifier tube in which an output stage comprises juxtaposed crystal rods of scintillator material and an intermediate stage, between the output stage and an input stage, comprising a microchannel plate, i.e. an apertured plate of active material whose channel walls produce secondary electrons when struck by electrons from the input stage to produce an electron amplified image of the pattern of radiation incident on the input stage. One radiation image intensifier in accordance with the invention will now be described, by way of example, with reference to the accompanying drawings in which:- Figure 1 is a diagrammatic illustration of the intensifier; Figure 2 is a vertical , sectional view of a portion of the intensifier; and Figures 3A, 3B and 3C are enlarged, vertical, sectional views of portions of the portion of the intensifier shown in Figure 2. Referring to Figures 1 and 2, a panel shaped proximity type radiation image intensifier tube 10 according to the present invention is illustrated. It should be noted at the outset that while the invention is described in terms of sensitivity to x-rays, it is not intended to limit the applicability of the invention to x-ray detection. The invention has equal utility in detecting gamma radiation or other penetrative radiation. The image intensifier tube 10 comprises a metallic, typically type 304 stainless steel, vacuum tube envelope 12 and a metallic, inwardly concave input window 14. The window 14 is made of a specially chosen metal foil or alloy metal foil in the family of iron, chromium, and nickel, and in some embodiments additionally combinations of iron or nickel together with cobalt or vanadium. It is important to note that these elements are not customarily recognized in the field as a good x-ray window material in the diagnostic region of the x-ray spectrum. By making the window thin, down to 0.1 mm in thickness, the applicant was able to achieve high x-ray transmission with these materials and at the same time obtain the desired tensile strength. In particular, a foil made of 17-7 PH type of precipitation hardened chromium-nickel stainless steel is utilized in the preferred embodiment. This alloy is vacuum tight, high in tensile strength and has very attractive x-ray properties, e.g., high transmission to primary x-rays, low self-scattering, and reasonably absorbing with respect to patient scattered x-rays. The window 14 is concaved into the tube like a drum head. The use of materials which are known for high x-ray transmission such as beryllium, aluminum and titanium for example cause the undesirable scattering which is present in some prior art proximity type, x-ray image intensifier devices. One purpose of having a metallic window 14 is that it can be quite large in diameter with respect to the prior art type of convex, glass window without affecting the x-ray image quality. In one embodiment, the window measures 0.1 mm thick, 25 cm by 25 cm and withstood over 689.47 kN/m² of pressure. The input window can be square, rectangular, or circular in shape, since it is a high tensile strength material and is under tension rather than compression. In operation, an x-ray source 16 generates a beam of x-rays 18 which passes through a patient's body 20 and casts a shadow or image onto the face of the tube 10. The x-ray image passes through the input window 14 and impinges upon a scintillator assembly 22 which converts the x-ray image to a light image. This light image is contact transferred directly to an immediately adjacent, first flat photocathode layer 24 which converts the light image into a first pattern of electrons. Referring also to Figure 3A, the scintillator assembly 22 is preferably comprised of a cellular plate substrate 26, a conductive, reflective coating 28, scintillator material 30, a first photocathode layer 24 and reflective conductive layer 32. The cellular plate substrate 26 is a low cost, pattern etched ceramic plate available from Corning as part of their Fotoform®/Foroceram® (both registered trade marks) precision photosensitive glass material product line. Fotoform and Fotoceram products are described in more detail in Corning product brochure No. FPG-4. It should be noted that these cellular plates are not micro-channel plates. The cellular plate of the present invention is approximately 23cm in diameter and about 0.625mm thick. In the preferred embodiment, the plate is etched with a pattern of hexagonally shaped through holes or cells that are typically 0.1mm wide and are arranged to produce uniform 0.025 mm walls between the holes. The etched array is similar to a honeycomb structure. As a result of the etching process, straight angular walls result which taper to a virtual knife's edge. This tapering is apparent in Figure 3A. The cellular plate substrate 26 is oriented within the tube envelope 12 such that the tapered edges face toward the input window 14. It should be noted that there is very little reduction in conversion efficiency due to the dead space created by the cell walls. Since the walls are tapered structures that approach zero thickness at the x-ray input surface, the effective open area for this structure is greater than 90%. It should also be noted that it is possible to alter the particular cell shape of a given cellular plate. Geometrics of almost any size and shape can be etched into the ceramic plate. Likewise the plates can be square, rectangular or circular in shape. The walls of each cell of the cellular plate 26 are coated with a reflective, conductive layer 28. The layer 28 should be highly reflective to the light and is formed by vacuum depositing aluminum to a thickness of approximately 10⁻⁴mm (1000 angstroms) in a known manner. After coating, the voids between the cell walls are filled with a scintillator material 30 preferably cesium iodide (CsI(Na)). In the preferred embodiment the scintillator material 30 is vacuum evaporated onto the cell walls until the material completely fills the voids. The overall thickness of the scintillator material 30 is chosen to be approximately the same as the cellular plate 26. On the input side of the scintillator assembly 22 (side adjacent to the input window 14), an additional reflective, conductive layer 32 is preferably applied. The layer 32 is aluminum vacuum deposited to a thickness of several ten-thousandths of a millimetre. A wide variation of aluminum thickness, ranging from 2 x 10⁻⁴ to 0.1mm (a few thousand angstroms up to a few mils), provides acceptable performance. While application of layer 32 is preferred it is not necessary for the operation of the present invention. On the output side of the scintillator assembly 22, a first photocathode layer 24 is deposited to a thickness of approximately 5 x 10⁻⁶mm (50 angstroms). The photocathode material is well known to those skilled in the art, being On the output side of the scintillator assembly 22, a first photocathode layer 24 is deposited to a thickness of approximately 5 x 10⁻⁶mm (50 angstroms) cesium and antimony (Cs₃Sb) (industry photocathode types S-9 or S-11) or multi-alkali metal (combinations of cesium, potassium and sodium) and antimony. In operation, x-rays entering the tube 10 pass through the thin, conductive layer 32 and are absorbed in the scintillator material 30 within each cell of the substrate 26. The scintillator material 30 releases photons which travel directly or through internal reflection to the first photocathode layer 24. Photons striking the photocathode layer 24 cause the release of a first pattern of electrons which is accelerated to an intermediate assembly 34. The manner in which the first electron pattern is accelerated is described in more detail below. The use of a cellular plate as a substrate for the scintillator assembly 22 results in separation of the individual cesium iodide crystals into predetermined structures. This configuration offers a fundamental improvement over the prior art two-stage device by enabling precise control of this critical first conversion layer which is the limiting factor in the detection sensitivity of the entire device. In the prior art two-stage device, the scintillation screen is a vacuum deposited, mosaic grown crystal. However, tradeoffs in crystal size, smoothness, and thickness of the scintillation material lead to a compromise in the two-stage device's ability to reproduce detail. The cellular structure of the present invention enables independent control of these parameters. The thickness of the cesium iodide in the present invention is increased 2X over that of the two-stage device. This increased thickness improves x-ray absorption and reduces the loss of K fluorescent x-rays. Better coupling of photons to the first photocathode layer 24 is achieved due to better cesium iodide transparency. Transparency is higher since the cesium iodide can now be annealed without the worry of cells growing together. Annealing is the process of heat treating a material to remove internal stress and non-uniformities. In cesium iodide, clarity of the evaporated material is greatly reduced by stress and non-uniformity which causes light scattering and absorption. Annealing at temperatures of a few hundred degrees centigrade greatly improves this condition. Without the cellular structure, however, the crystals of cesium iodide would "grow" together during the annealing process to form crystals that are too large for good resolution. The cellular plate prevents this from occurring. Through the use of the cellular plate, the final annealed cesium iodide crystal size is no greater than the cell size of the cellular plate. Also since the cells are independent and also captured within the cellular structure, roughened surfaces for adhesion control or resulting from crystal growth constraints of the prior art devices are no longer necessary. Thus a flat and smooth surface can now be maintained thereby improving resolution. Lateral transmission or crosstalk between the cells is also eliminated by the cell walls thus improving contrast. The use of the cellular structure as a substrate also eliminates the need for the intervening aluminum substrate used in the prior art devices. In the prior art device, x-rays must first pass through the aluminum substrate before absorption in the cesium iodide. Elimination of this aluminum substrate reduces the weight of the overall device and increases the conversion efficiency of the device. The conductive reflective coating 28 applied to the individual cell walls creates a conductive matrix. The matrix permits the use of a photocathode layer that has a high sensitivity. It is known that by increasing the sensitivity of photocathode, a tradeoff in conductivity will result. In the prior art devices conductivity of the photocathode was critical. The conductivity of the intermediate cesium iodide layer in the prior devices was very poor, therefore, the conductivity of the photocathode must be kept sufficiently high to replenish charge to prevent positive charging of the photocathode (charging disrupts the image and can destroy the photocathode). Typically, in the prior art, photocathodes are 2X thicker than is desirable because of the necessity to maintain good conductivity over a large (X 23cm diameter) area. In the present invention, the photocathode 24 is connected to the conductive matrix at each cell. The conductive matrix connects to the high voltage as explained in more detail below. Therefore, the low conductivity of the cesium iodide is not critical since the conductive matrix provides for conduction directly. As a result, a thinner photocathode can be used since charge must be replenished only over the area of a single cell, instead of a 230mm (9") diameter area. Therefore, thinner photocathode layers can be used with an increase in sensitivity. Better coupling of photons to the photocathode is also achieved due to the independent control of cell reflectivity and improved transparency of the cesium iodide crystals. Referring again to Figure 1 and 2 and in particular Figure 3B, an intermediate assembly 34 is provided. The intermediate assembly 34 is spaced from the scintillator assembly 22 on a side opposite the input window 14. The intermediate assembly 34 is preferably comprised of a cellular plate 36 as a substrate material, a conductive coating 38, a second photocathode layer 46, support layer 40, a first phosphor screen 42 and reflective aluminum layer 44. Substrate 36 is made of the same material and is of similar dimension as is substrate 26 used in the scintillator assembly 22. The walls of the substrate 26 are again tapered to an edge. The substrate 26 is oriented within the tube envelope 12 such that the tapered edges face toward the input window 14. A conductive layer 38 is deposited on the walls of the cells in the same manner as layer 28. The output end of the plate 36 is sealed off with a light transparent support layer 40 such as potassium silicate. The sealing process involves spreading a thin layer of potassium silicate dissolved in water on a smooth, flat substrate and then pressing the cellular plate against the substrate. After drying, the substrate is removed leaving the potassium silicate behind on the cellular plate. This process produces a thin, transparent "window" at the end of each cell. The thickness of the potassium silicate layer thus applied is typically 0.05 to 0.1mm (a few thousandths of an inch). On the input side of the transparent support layer 40 (side internal to the plate 36), a first phosphor screen 42 is deposited followed by the application of a light reflective aluminum layer 44. The light reflective aluminum layer 44 is formed in the same manner as layer 32. Since layer 44 must be highly transmissive to electrons, rather than to x-rays it is only a 2 to 5 x 10⁻⁴mm (a few thousand angstroms) thick. The first phosphor screen 42 can be of the well known zinc-cadmium sulfide type (ZnCdS(Ag)) or zinc sulfide (Zns(Ag)) or a rare earth material like yttrium oxysulfide (Y₂O₂S(Tb)) or any other suitable high efficiency blue and/or green emitting phosphor material. The phosphor screen 42 is deposited in a known manner to a thickness of 5 to 50 x 10⁻³mm (5 to 50 microns). On the output side of the transparent support layer 40, a second photocathode layer 46 is formed. The type thickness and the manner in which the second photocathode layer 46 is formed is the same as the first photocathode layer 24. In operation, the first pattern of electrons released from the first photocathode layer 24 is accelerated by high voltage toward the intermediate assembly 34. Of these electrons, the majority enter the intermediate assembly 34, are directed toward and pass through the aluminum layer 44 and are absorbed predominately in the first phosphor screen 42. Some electrons strike the cell walls and are absorbed. Of the electrons striking the phosphor layer 42 the majority are absorbed but a significant portion are backscattered (see figure 3B). The electrons absorbed by the phosphor layer 42 release photons which pass into the transparent support layer 40 either directly or by first reflecting back from the aluminum layer 44 coating the first phosphor screen 42. The photons that are transmitted through the transparent layer are subsequently absorbed in the second photocathode layer 46 which in turn releases a second pattern of electrons toward the output assembly 48. The use of a cellular plate for the intermediate assembly greatly reduces contrast losses due to effective control of the above mentioned backscattered electrons. In the prior art devices, backscatter electrons experience a retarding electric field and thus follow looping trajectories back toward the scintillator and return to the phosphor display screen mounted on the fiber optic plate. Contrast is lost because the return strikes are displaced from the initial strike point by up to a few centimeters. Since the backscatter electrons possess sufficiently high energy, the return strikes can be subsequently converted to light in the phosphor which in turn cause the release of electrons from a remote location. The effect is a circular glow about the point of interest. By utilizing the cellular plate substrate of the present invention, the majority of the backscatter electrons strike the cell walls and are absorbed thereby eliminating the circular glow described above. The use of the cellular plate also aids in the reduction of surface reflectivity to scattered or stray light between the scintillator assembly 22 and the intermediate assembly 34. In the prior art devices, stray light reflects to some degree as it strikes the aluminum layer coating the phosphor screen. The reflected light then falls on the photocathode of the prior stage giving rise to signals from the wrong location. The cellular plate of the present invention has a very low effective reflectivity since it traps and subsequently absorbs scattered photons within each cell (see Figure 3B). As with the scintillator assembly 22, the cellular plate used in the intermediate assembly 34 provides an exposed conductive matrix which eliminates the need to supply current to the second photocathode layer 46 over long distances. This allows a reduction in the thickness of photocathode 46 which leads to an increase in gain. The advantage of using the thinner photocathode in the intermediate assembly is much more pronounced than in the scintillator assembly since photocathode 46 must provide about 50X greater operating current. Hence the sensitivity of the prior art devices was greatly compromised to achieve the necessary conductivity. Referring to Figure 3C, an output assembly 48 is provided. The output assembly 48 is spaced from the intermediate assembly 34 on a side opposite the scintillator assembly 22. The output assembly 48 is preferably comprised of a cellular plate 50, conductive coating 52, a second phosphor screen 58, aluminum coating 60, sealing glass 54 and output window 56. A cellular plate is also used as the substrate for the output assembly 48. The cellular plate 50 is identical to the cellular plate 36 used in the intermediate assembly 34. The substrate 50 is again oriented within the tube envelope 12 such that the tapered edges face toward the input window 14. The cellular plate 50 is again coated with a conductive layer 52 in the same manner as layers 28 and 38. The second phosphor screen 58 is comprised of the same class of materials and deposited in the same manner as the first phosphor screen 42. The output side of the plate 50 is sealed using transparent sealing glass 54 which couples the plate 50 to an output window 56. The output window 56 is preferably clear glass. A second phosphor screen 58 and aluminum overcoating 60 are deposited to the input side of the sealing glass 54 in the same manner as the above described first phosphor screen 42 and aluminum layer 44 found in the intermediate assembly 34. The operation of the output assembly 48 is the same as the intermediate assembly 34 except that photons liberated from the second phosphor layer 58 pass through the sealing glass 54 and are transmitted to the output window 54 for viewing by the operator. This approach to the output assembly 48 offers the same contrast improvement benefits as cited for the intermediate assembly 34 since the same degradation mechanism exists in the output assembly of the prior art devices. Referring back to Figure 1, a high voltage power supply 62 is connected between the scintillator assembly 22 and the intermediate assembly 34 as well as between the intermediate assembly 34 and the output assembly 48. The connections to these assemblies are made via the conductive matrices 28, 38 and 52. The voltage potentials are chosen such that the potential between the scintillator assembly 22 and the intermediate assembly 34 is in the range of 5-30 kV; preferably 15 kV and the potential between the intermediate assembly 34 and the output assembly 48 is in the range of 5-40 kV; preferably 15 kV. The preferred total operating voltage is therefore approximately 30 kV. In operation, the first electron pattern on the negatively charged scintillator assembly 22 is accelerated towards the positively charged (relative to the scintillator assembly 22) intermediate assembly 34 by means of the electrostatic potential supplied by the high voltage source 62 connected between the scintillation assembly 22 and the intermediate assembly 34. The electrons striking the first phosphor screen 42 produce a corresponding light image (i.e., photons are emitted in a corresponding pattern) which pass through the transparent support layer 40 to impinge on the second photocathode 46. The second photocathode 46 then reemits a corresponding second pattern of electrons which are accelerated toward the output assembly 48 to produce an output light image which is viewable through the window 56. Although the output assembly 48 is positive with respect to the intermediate assembly 34, it is at a neutral potential with respect to the remaining elements of the tube, including the metallic envelope 12, thereby reducing distortion due to field emission. It should be noted that like the two-stage prior art device substantially no focusing takes place in the tube of the present invention. The scintillator assembly 22, the intermediate assembly 34 and the output assembly 48 are substantially parallel to one another. In the preferred embodiment, the spacing between the output end of the scintillator assembly 22 and the input end of the intermediate assembly 34 is preferably 10mm and the spacing between the output end of the intermediate assembly 34 and the input end of the output assembly 48 is preferably 14mm. In other embodiments these spacings could range between 1 to 30 mm. Furthermore, the applied voltages across the respective gaps are 15,000 V (volts) each which are each lower than in the prior art devices. Thus, the voltage per unit of distance, i.e., the field strengths of the improved tube according to the invention are 1.5 kV/mm (first stage) and 1.1 kV/mm (second stage). By keeping the assembly spacing and the field strength within the above mentioned limits the improved tube of the present invention is not only able to achieve high gain at lowwer over-all operating voltager (on the order of 40,000-1000,000 cd-sec/m²-R), but is also able to do this with a higher resolution and contrast ratio than the highest gain (30,000-50,000 cd-sec/m²-R) two-stage proximity type tubes. Also the various feedback mechanisms, such as ions and x-rays generated at the output assembly are either eliminated or greatly dimished in their effect. The lower voltage per stage and shorter gap reduces the velocity and dispersion of the elctrons striking the display screens and therefore reduces or eliminates the number of ions and x-rays which would be generated by higher elocity electrons striking the display screens. The scintillator assembly 22 and the intermediate assembly 34 are suspended from the tube envelope 12 between the input window 14 and the output assembly 48 by several insualting posts 31. At one end high voltage feedthrus 63 are provided to allow high voltage cables 47 and 49 from power supply 62 to be inserted through the tube envelope to provide the scintillator assembly 22 and the intermediate assembly 34 with negative high potentials. The remaining parts of the intensification tube including the metallic envelope 12, are all operated at ground potential. This concept of minimizing the surface area which is negative with respect to the output assembly results in reduced field emission rate inside the tube and allows the tube to be operable at higher voltages and thus higher brightness gain. It also minimizes the danger of electrical shock to the patient or workers if one should somehow come in contact with the exterior envelope of the tube. To reduce accumulated charges, the insulating posts 31 and high voltage feedthrus 63 are coated with a slightly conductive material such as chrome oxide which bleeds off the accumulated charge by providing a leakage path. It should also be noted that through utilizing the cellular plates of the present invention, the fiber optic element of the prior art two-stage device is eliminated. The fiber optic element, while contributing to performance improvements in the two-stage device over the one-stage device, added to the manufacturing cost of the tube as well as to the overall tube weight and compromised its resistance to severe environments. By the elimination of the fiber optic element the ruggedness of the image intensifier of the present invention is improved thereby making it suitable for military applications. The essentially all metallic and rugged construction of the tube minimizes the danger of implosion. The small vacuum space enclosed by the tube represents much smaller stored potential energy as compared with a conventional tube which further minimizes implosion danger. Furthermore, if punctured, the metal behaves differently from glass and the air supply leaks in without fracturing or imploding. The invention as described modifies the three components of the prior art devices by incorporating cellular plates as the substrate material. By configuring all three components in this manner maximum performance improvement will be realized. It is to be appreciated, however, that a panel type image intensifier tube can be configured by replacing any single assembly or combination of assemblies of the prior art devices with an assembly constructed in accordance with the present invention. It must be recognized that various modifications are possible within the scope of the claims.

Claims: A multistage radiation image intensifier tube (10) wherein at least one stage (22, 34 or 48) comprises a substrate (26, 36 or 50) of substantially non-secondary electron emitting material which defines a plurality of cells which extend through the substrate and are substantially aligned with the path of the radiation or electrons incident on that stage, the walls of the cells tapering continuously to a sharp edge throughout the thickness of the substrate, the taper being towards the side of the substrate on which the radiation or electrons is/are incident. An intensifier tube (10) according to Claim 1 wherein the cell walls have a coating of electrically conductive material (28, 38 or 52). An intensifier tube (10) according to Claim 2 wherein said conductive coating (28, 38 or 52) is formed by vacuum deposition. An intensifier tube (10) according to Claim 2 or Claim 3 wherein said conductive material is aluminum. An intensifier tube (10) according to Claim 4 wherein said conductive coating (28, 38 or 52) has a thickness of substantially 10⁻⁴ mm (1000 angstroms). An intensifier tube (10) according to any one of the preceding claims wherein said substrate (26, 36 or 50) is of ceramic material. An intensifier tube (10) according to Claim 6 wherein said substrate (26, 36 or 50) is formed by etching. An intensifier tube (10) according to any preceding claim wherein said cells are hexagonal. An intensifier tube (10) according to Claim 8 wherein said cells form a honeycomb structure. A radiation image intensifier tube (10) according to any one of the preceding claims comprising: a tube envelope (12); an input window (14) in the tube envelope; a scintillator stage (22) mounted in the envelope (12) for converting impinging radiation into a first pattern of liberated electrons; means (62) for accelerating said first pattern of electrons along a first path; an intermediate stage (34) mounted in the envelope (12) along said first path and spaced from the scintillator stage (22) for receiving said first electron pattern and converting said first pattern into a second pattern of liberated electrons; means (62) for accelerating said second pattern along a second path; and an output stage (48) mounted in the envelope (12) along said second path and spaced from the intermediate stage (34) for receiving and converting said second pattern into a visual image pattern; at least one of said scintillator, intermediate and output stages (22, 34, 48) incorporating a said substrate (26, 35 or 50) defining a said plurality of cells. An intensifier tube (10) according to Claim 10 wherein the scintillator stage (22) comprises a said substrate (26) defining a said plurality of cells whose walls are coated with a conductive, reflective layer (28); scintillator material (30) filling the space between the walls of said cells; and a flat photocathode layer (24) mounted substantially parallel and immediately adjacent to the substrate (26). An intensifier tube (10) according to Claim 11 wherein said scintillator material is primarily an alkali halide such as cesium iodide, or sodium iodide. An intensifier tube (10) according to any one of Claims 10 to 12 wherein the intermediate stage (34) comprises a said substrate (36) defining a said plurality of cells whose walls are coated with a conductive layer (38); a support layer (40) mounted to one end of the substrate (36); a phosphor layer (42) applied to the support layer (40) on the side adajcent the substrate (36); and a photocathode layer (46) substantially parallel and immediately adjacent the support layer (40) mounted on the side opposite the phosphor layer (42). An intensifier tube (10) according to Claim 13 further including a reflective layer (44) on the side of the phosphor layer (42) opposite said support layer (40). An intensifier tube (10) according to any one of Claims 10 to 14 wherein the output stage (48) comprises; a said substrate (50) defining a said plurality of cells whose walls are coated with a conductive layer (52); an output window (56) mounted to one end of the substrate (50); and a phosphor layer (58) applied to the output window (56) on the side adajcent the substrate (50). An intensifier tube according to Claim 15 further including a reflective layer (60) on the side of said phosphor layer (58) of the output stage (48) opposite the output window (56). An intensifier tube (10) according to Claim 15 or 16 when dependent on Claim 11 and Claim 13 further including electrostatic potential means (62) for applying separate electrostatic potentials between the substrates (26, 36) of the scintillator and intermediate stages (22, 34) on the one hand and between the substrates (36, 50) of the intermediate and output stages (34, 48) on the other hand to accelerate electrons from said photcathode layers (24, 46) of said scintillator and intermediate stages (22, 34) respectively onto said phosphor layers (42, 58) of said intermediate and output stages (34, 48) respectively along substantially staight trajectories. An intensifier tube (10) according to Claim 17 wherein the tube envelope (12) is metal and the electrostatic potential means (62) supply high negative potentials to the substrate (26) of the scintillator stage (22) and the substrate (36) of the intermediate stage (34) and a ground potential to the substrate (50) of the output stage (48) and the envelope (12). An intensifier tube (10) according to Claim 18 wherein the electrostatic potential means (62) applies an electrostatic potential of 5 to 30 thousand volts between the substrate (26) of the scintillator stage (22) and the substrate (36) of the intermediate stage (34) and of 5 to 40 thousand V (volts) between the substrate (36) of the intermediate stage (34) and the substrate (50) of the output stage (48). An intensifier tube (10) according to any one of Claims 10 to 19 wherein the input window (14) is concave inwardly with respect to the tube envelope (12) and its made from type 17-7 PH stainless steel. An intensifier tube (10) according to any one of Claims 10 to 20 wherein the spacing between the photocathode layer (24) of the scintillator stage (22) and the substrate (36) of the intermediate stage (34) is 1 to 30mm and the spacing between the photocathode layer (46) of the intermediate stage (34) and the substrate (50) of the output stage (48) is 1 to 30mm. An intensifier tube according to any one of Claims 10 to 21 wherein said scintillator stage (22), said intermediate stage (34) and said output stage (48) have substantially the same diagonal dimensions.

Inventors: ENCK, RICHARD S., JR., MEADOWS, DAN F.
Applicants: PICKER INTERNATIONAL, INC.
Application year: 1987
Main classification: H01J31
IPC codes: H01J29, H01J9, G21K4, H01J31