JPS6290599A - Radiation image conversion panel - 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 [Field of the Invention] The present invention relates to a radiation image conversion panel used in a radiation image conversion method using a stimulable phosphor.

[Technical Background of the Invention] As a method for obtaining radiation images as images, so-called radiography has conventionally been used, which uses a combination of a radiographic film having an emulsion layer made of a silver salt photosensitive material and an intensifying screen. There is. Recently, an alternative method to the radiographic method mentioned above has been developed.
As one example, a radiation image conversion method using a stimulable phosphor, as described in, for example, Japanese Unexamined Patent Publication No. 55-12145, has attracted attention. This radiation image conversion method uses a radiation image conversion panel (
This panel uses a stimulable phosphor sheet (a stimulable phosphor sheet), which absorbs the radiation that passes through the subject or the radiation emitted from the subject, and then absorbs the stimulable phosphor into visible light. By exciting the stimulable phosphor in a time-series manner with electromagnetic waves (excitation light) such as infrared rays, the radiation energy accumulated in the stimulable phosphor is released as fluorescence (stimulated luminescence), and this fluorescence is photoelectrically generated. read and obtain electrical signals,
The obtained electrical signals are converted into images.

This radiation image conversion method has the advantage that it is possible to obtain a radiation image with a rich amount of information with a much lower exposure dose than when using conventional radiography. Therefore, this radiation image conversion method has a very high utility value especially in direct medical radiography such as X-ray photography for the purpose of medical diagnosis.

The radiation image conversion panel used in the above radiation image conversion method has a basic structure consisting of a support and a phosphor layer provided on one side of the support.

Note that the surface of this phosphor layer on the opposite side of the support (the surface not facing the support) is generally provided with a transparent protective film made of a polymeric substance, and the phosphor layer is It protects the layer from chemical alteration or physical impact.

The phosphor layer consists of a stimulable phosphor and a binder that contains and supports the stimulable phosphor in a dispersed state. After absorbing radiation such as X-rays, the stimulable phosphor absorbs visible light and When irradiated with electromagnetic waves (excitation light) such as infrared rays, it emits light (
It has the property of exhibiting (stimulated luminescence). Therefore, the object was penetrated. Alternatively, the radiation emitted from the subject is absorbed by the phosphor layer of the radiation image conversion panel in proportion to the radiation dose, and the radiation image of the subject or subject appears on the radiation image conversion panel as an image of accumulated radiation energy. It is formed. This accumulated image can be emitted as stimulated luminescence by time-series excitation with the electromagnetic waves, and by photoelectrically reading this stimulated luminescence and converting it into an electrical signal, the accumulated image of radiation energy can be imaged. It becomes possible to convert into

The radiation image conversion method is a very right-handed image forming method as mentioned above, but the radiation image conversion panel used in this method is also highly sensitive, similar to the intensifying screen used in conventional radiography. It is desired that the image quality (sharpness, graininess, etc.) be excellent. In particular, in medical radiography of the human body, it is desired to obtain images with excellent image quality by reducing the exposure dose as much as possible. Furthermore, in industrial radiography used for non-destructive inspection of materials, it is desired to improve inspection accuracy by obtaining images with good image quality.

x & I irradiated to the subject during radiography
The - part of the radiation such as i is scattered by the object.

This scattered radiation also enters the radiation image conversion panel in the same way as the radiation that has passed through the subject (direct radiation & ia) and contributes to the accumulation of radiation energy in the image formation, so the image quality such as resolution of the obtained image deteriorates. It tends to be.

Until now, in order to remove scattered radiation from the subject, a grid-shaped scattered radiation removal plate (Lisholm Prende) has been placed between the radiation source and the subject to remove the scattered radiation. , in this method of removing scattered radiation, the structure of the device (imaging system)
However, it was not necessarily an efficient method because it was complicated and a portion of the direct radiation was also removed at the same time.

[Summary of the Invention] An object of the present invention is to provide a radiation image conversion panel that can efficiently remove scattered radiation.

Another object of the present invention is to provide a radiation image conversion panel that provides images with excellent image quality, especially resolution.

The purpose of the above is to provide a radiation image conversion panel having a phosphor layer on a support and a binder containing and supporting a stimulable phosphor provided on the support with dispersed IFB. This can be achieved by the radiation image conversion panel of the present invention, which has a striped or mesh-like grid made of a radiation-absorbing material on one side.

The present invention provides a grid capable of absorbing radiation such as X-rays on one surface of the radiation image conversion panel, so that in radiography, the surface of the panel on which the grid is provided is placed on the radiation irradiation side. This method simply and efficiently removes radiation scattered by the subject.

In other words, according to the present invention, since the striped or mesh-like grid made of a radiation-absorbing material is attached to one side of the panel, it is no longer necessary to add a scattered radiation removal plate to the imaging system as in the conventional case. There is no need to arrange it, and the radiography system can be simplified. Furthermore, compared to the case where a grid-like scattered radiation removal plate is arranged independently between the radiation source and the panel, in the present invention, the grid for removing scattered radiation is provided directly on the panel surface. That is, since the grating is located closer to the phosphor layer where the radiation energy accumulation image is formed, only the scattered radiation can be removed with higher efficiency than in the past. Therefore, an image with excellent image quality such as resolution can be obtained without substantially increasing the radiation dose of the subject.

Further, reading of a radiation image conversion panel is normally performed by repeatedly carrying and stacking a plurality of panels in a radiation image recording/reproducing apparatus in succession. Since one side of the panel of the present invention is provided with a striped or mesh-like lattice and has minute irregularities, it is possible to reduce the contact area with the surface of another panel when moving from lamination to conveyance.
The transportability of the panel can be improved.

In particular, when the radiation image conversion panel is configured such that the - part of the lattice made of a radiation absorbing material is embedded in the phosphor layer, the lattice exists not only on the panel surface but also in the phosphor layer. Not only can the radiation scattered by the object be removed, but also the excitation light can be prevented from spreading due to scattering in the phosphor layer, and the quality of the resulting image can be further improved.

Furthermore, if the radiation image conversion panel is configured such that a part of the grid made of a radiation-absorbing material is embedded in the support, the mechanical strength of the support can be increased, and the panel itself can be reinforced. I can do it.

[Structure of the Invention] The radiation image conversion panel of the present invention having the preferable characteristics as described above can be manufactured, for example, by the method described below.

The support used in the present invention can be arbitrarily selected from various materials used for the support of an intensifying screen in conventional radiography or known for the support of a radiation image conversion panel. You can choose. Examples of such materials include cellulose acetate, polyester,
Films of plastic materials such as polyethylene terephthalate, polyamide, polyimide, triacetate, polycarbonate, metal sheets such as aluminum foil, aluminum alloy foil, containing pigments such as ordinary paper, baryta paper, 1/zinco paper, titanium dioxide, etc. Examples include pigment paper and paper sized with polyvinyl alcohol. However, in consideration of the characteristics and handling of the radiation image storage panel as an information recording material, a particularly preferred material for the support in the present invention is a plastic film. This plastic film may be kneaded with a light-absorbing substance such as carbon black, or may be kneaded with a light-reflecting substance such as titanium dioxide.

The former is a support suitable for a high sharpness type radiation image conversion panel, and the latter is a support suitable for a high sensitivity type radiation image conversion panel.

In known radiation image conversion panels, the phosphor layer is added in order to strengthen the bonding of the phosphor layer on the support or to improve the sensitivity or image quality (sharpness, granularity) of the radiation image conversion panel. A polymeric substance such as gelatin is coated on the support surface on the side to be provided to form an adhesive layer, or a light reflective layer made of a light reflective substance such as titanium dioxide, or a light absorbing substance such as carbon black. It has also been practiced to provide a light absorption layer consisting of. The support used in the present invention can also be provided with these various layers.

Furthermore, as described in JP-A-58-200200, in order to improve the sharpness of the obtained image, the surface of the support on the phosphor layer side (the surface of the support on the phosphor layer side) When an adhesive layer, a light reflection layer, a light absorption layer, etc. are provided, fine irregularities may be uniformly formed on the surface (meaning the surface thereof).

Next, a phosphor layer is formed on the support.

The phosphor layer is basically a layer consisting of a binder containing and supporting particles of stimulable phosphor in a dispersed state.

As mentioned above, a stimulable phosphor is a phosphor that exhibits stimulated luminescence when irradiated with radiation and then irradiated with excitation light.
From a practical standpoint, it is desirable that the phosphor be a phosphor that exhibits stimulated luminescence in the wavelength range of 300 to 500 nm when excited by excitation light in the wavelength range of 400 to 900 nm. Examples of phosphors include SrS:Ce, Sm, and SrS:Eu, which are described in US Pat. No. 5S3,859,527.

Sm, Th02:Er, and La20□S:Eu,
Sm/Zn described in JP-A-55-12142
S: Cu, Pb, Babe
xAl tox :Eu (however, 0.8≦X≦
10), and M”O*xSi02 :A (However, M is Mg, Ca, Sr, Zn, Cd, or Ba, and A is Ce, Tb, Eu, Tm, Pb, TfL, B
i.

or Mn, and X is 0.5≦X≦2.5)
.

It is described in Japanese Patent Application Laid-Open No. 55-12143 (Ba
t-x-y+Mgx, Ca,)FX:aE u2°(
However, X is at least one of C1 and Br, X and y are 0, X+y≦0.6, and xy#
0 and a is 1O-6≦a≦5XIO-2), LnO described in JP-A-55-12144
X: xA (Ln is La, Y, Gd, and Lu
X is at least one of Cl and Br, A is at least one of Ce and Tb, and X is O<x<0.1), JP-A-Sho 55-12145 (B
a r-x, M''X) FX: y
A (However, M2° is at least one of Mg, Ca, Sr, Zn, and Cd (7), X is C1, Br,
and at least one of the following, A is Eu, Tb, C
e, Tm, D'y, Pr, Ho, Nd, Yb, and E
At least one of r, and X is 0≦X≦0
．． 6, y is O≦y≦0.2), JP-A-55-1
M”FXexA described in Publication No. 60078:
yLn [However, Ml is Ba, Ca, S r, Mg,
At least one of Zn and CD, A is Bed
, MgO, CaO1SrO1BaO, Z'n01A,
ol, Y2O3, La, O,, In2O3, 5i02,
TlO2, ZrO2, GeO2, 5n02, Nb2O5
, Ta205, and The2=
One kind, Ln is Eu, Tb, Ce, Tm, Dy, Pr,
at least one of Ho, Nd, Yb, Er, Sm, and Gd, or at least one of Ho, Nd, Yb, Er, Sm, and Gd, and each of X and y is 5X
A phosphor represented by the following compositional formula where 10-'≦X≦0.5 and Okuy≦0.2 is described in JP-A-56-116777 (B
a, -1, M 1B) F2 e aBaX2 :yEu
, zA [where Mll is beryllium, magnesium,
at least one of calcium, strontium, zinc, and cadmium, X is at least one of chlorine, bromine, and iodine, A is at least one of zirconium and scandium, a, x, y,
and 2 are respectively 0.5≦a≦1.25.0≦X≦1
．． 10-"≦y≦2X10-', and 0<z≦10-
A phosphor represented by the composition formula: 2.

It is described in Japanese Patent Application Laid-Open No. 57-23673 (na
+-x, M” x) F1a aBaX2:yEu, z
B[However, M" is at least one of beryllium, magnesium, calcium, strontium, zinc, and cadmium, X is at least one of chlorine, bromine, and iodine, and a, x, y, and Z are 0.5≦a≦1.25.0≦X≦1.10-6≦y, respectively
≦2×10-' and O<z≦2
+-x, M" x) F1a aBaX2:yEu,
zA[However, M" is at least one of beryllium, magnesium, calcium, strontium, zinc, and cadmium, X is at least one of chlorine, bromine, and iodine, and A is at least one of arsenic and silicon. Yes, a, x, y, and 2 are each 0
．． 5≦a≦1.25.0≦X≦1.10-6≦y≦2×
to-', and O<z≦5X10-';
X: xCe [where Ml is Pr, Nd, Pm, Sm,
Eu, Tb, Dy, Ha.

At least one trivalent metal selected from the group consisting of Er, Tm, Yb, and Bi, and X is C1 and Br.
Either or both of these, and X is 0
A phosphor represented by the composition formula <x<0.1], B described in JP-A No. 58-206678
a+−xMx/2LX/2FX:
y E u ”” [However, M is Li, Na, R
h, and at least one alkali metal selected from the group consisting of Cs; L represents Sc, Y, La, Ce;
, Pr, Nd, Pm, Sm, Gd, Tb, Dy, Ho,
Er, Tm, Yb, Lu, AM, Ga, In,
and at least one trivalent metal selected from the group consisting of Ti; X represents at least one halogen selected from the group consisting of C1, Br, and ■: and X represents 10-2≦X≦0 .5, y is Okuy≦0.1
A phosphor represented by the composition formula: BaF described in JP-A-59-27980
X*xA:yEu"° [where X is at least one halogen selected from the group consisting of C1, Br, and 10-6≦X≦0.1, y is o<
y≦0.1] A phosphor represented by the composition formula: BaF described in JP-A No. 59-47289
Xe xA : yEu” [However, X is C1, B
r, and at least one halogen selected from the group consisting of I; A is from the hexafluoro compound group consisting of monovalent or divalent metal salts of hexafluorosilicic acid, hexafluorotitanic acid, and hexafluorozirconic acid; is a fired product of at least one selected compound; and X is 10-6≦X≦o, i, y are o<y
≦0.1], BaFXex described in Japanese Patent Application Laid-Open No. 59-56479
NaX'+aEu'' [where x and X' are each at least one of Cl, Br, and
A phosphor represented by the composition formula:
FX@xNaX':yEu”: zA [However, ME
is at least one alkaline earth metal selected from the group consisting of Ba, Sr, and Ca;
'l*, SohSolnCfL, B r.

At least one type (7) selected from the group consisting of
/%1 El Genchi; A is V, Cr, Mn, F
at least one transition metal selected from e, Co, and Ni; and X satisfies 0<x≦2. 7 is o<y
≦0.2, and Z is O<z≦10-2].
FX@aM'X' * bM"X"2・c M"
X"'x ・, xA : yEu" [However, Ml
is at least one alkaline earth metal selected from the group consisting of Ba, Sr, and Ca; MI is Li, N
a, Rh, and Cs1Hn; M' is at least one divalent metal selected from the group consisting of Be and Mg; MI is A, is at least one trivalent metal selected from the group consisting of Ga, In, and one sentence;
A is a metal oxide; X is at least one halogen selected from the group consisting of C1, Br, and ■;
X', x'', length xl, F, C1°Br, and I
at least one kind of halogen selected from the group consisting of; and a is O≦a≦2, b is O≦b≦10-2,
C is O≦C≦10-2 and a+b+c≧10-6; X is 0<x≦0.5, y is o<y≦0.2]
A phosphor represented by the composition formula is described in Japanese Patent Application No. 193161/1983 filed by the applicant.
"[However, MW is at least one alkaline earth metal selected from the group consisting of Ba, Sr, and Ca;
X and X' are at least one kind of haloken selected from the group consisting of C, Br and ■, and X≠X゛; and a is 0.1≦a≦10.0, and X is 0< x
≦0.2], M"FXe aM'X' : xEu2° [where Mm is Ba , Sr and Ca; Ml is at least one alkali metal selected from the group consisting of Rb and Cs; X is from the group consisting of CfL, Br and I; at least one selected halogen;
X l is at least one halogen selected from the group consisting of F, C1, Br, and engineering; and a and X are 0≦a≦4.0 and O<x≦0.2, respectively]. A phosphor represented by .

M'X:xBi [where Ml is at least one alkali metal selected from the group consisting of Rb and Cs; X is C or is at least one halogen selected from the group consisting of Br and I; and X is 0
Examples include a phosphor represented by the following compositional formula, which has a numerical value in the range <x≦0°2.

In addition, M'' X2e aM'
The u2+ phosphor contains the following additives M”X
It may be contained in the following proportions per mole of 2.aM"X'2.

bMIX'' described in Japanese Patent Application No. 59-22169 filed by the present applicant (where Ml is Rh and C
at least one alkali metal selected from the group consisting of s, X'' is at least one halogen selected from the group consisting of F, C1, Br and I, and b
is o<b≦1, , O); Patent application 1977-77225
bKX”・cMgx”2ad described in the specification of the No.
MIX'', (where M is at least one trivalent metal selected from the group consisting of Sc, Y, La, Gd and Lu, and X'', xl and X'' are all F, Cf
At least one halogen selected from the group consisting of L, Br and I, and G, c and d each satisfy 0≦b≦2°O10≦C≦2.0.0≦d≦2.0. and 2X10-"≦l)+C+d); yB(
However, y is 2 X 10-4≦y≦2 It is a kind of oxide, and b is 10-'≦b≦2X10-');
bsfo (
However, b is o<b≦3×10−2); bSn described in Japanese Patent Application No. 59-240454
X"2 (where X" is at least one halogen selected from the group consisting of F, (, Q, Br and I,
b is o<b≦10-');
sX”ecsnX”°2 (where, X” and
are o<b≦l0.0 and 10-6≦C≦2, respectively.
x10-2); and #intercondylar60 by the applicant
-bCsX “°Φ described in specification No. 78035
yLn'◆(However,
b, DV, Ho, Er, Tm, Yb and Lu, and b and y are o<b≦io, o and 1, respectively.
O-6≦y≦1.8X10-').

etc. can be mentioned.

Among the stimulable phosphors listed in L, divalent europium-activated alkaline earth metal halide phosphors and rare earth element-activated rare earth oxyhalide phosphors are particularly preferred because they exhibit high-intensity stimulated luminescence. The N-exhaustive phosphor used in the present invention is not limited to the phosphor mentioned above, but when irradiated with radiation and then irradiated with excitation light,
Any phosphor that exhibits IR exhaust emission may be used.

Examples of binders for the phosphor layer include proteins such as gelatin,
Polysaccharides such as dextran, or natural polymeric substances such as gum arabic; and polyvinyl butyral, polyvinyl acetate, nitrocellulose, ethyl cellulose, vinylidene chloride, vinyl chloride copolymer, polyalkyl (meth)acrylate, vinyl chloride-vinyl acetate copolymer -7-, polyurethane, cellulose acetate butyrate, polyvinyl alcohol, linear polyester, and other synthetic polymeric materials. Particularly preferred among such binders are nitrocellulose, linear polyesters, polyalkyl (meth)acrylates, mixtures of nitrocellulose and linear polyesters, and mixtures of nitrocellulose and polyalkyl (meth)acrylates. be.

Note that these binders may be crosslinked with a crosslinking agent.

The phosphor layer can be formed on the support by, for example, the following method.

First, the binder on the stimulable phosphor described above is added to a suitable solvent and mixed thoroughly to prepare a coating solution in which the phosphor particles are uniformly dispersed in the binder solution. Examples of solvents for preparing coating solutions include lower alcohols such as methanol, ethanol, n-propanol, and n-butanol; chlorine-containing hydrocarbons such as methylene chloride and ethylene chloride; acetone, methyl ethyl ketone, and methyl isobutyl ketone. Ketones; esters of lower fatty acids and lower alcohols such as methyl acetate, ethyl acetate, and butyl acetate; ethers such as dioxane, ethylene glycol monoethyl ether, and ethylene glycol monomethyl ether; and mixtures thereof.

The mixing ratio between the binder and the stimulable phosphor in the coating/liquid is as follows:
Generally speaking, the mixing ratio between the binder and the phosphor is in the range of 1:1 to 1:10'0 (weight ratio), although it varies depending on the characteristics of the radiation image conversion panel to be used and the type of phosphor. It is particularly preferable to select from the range of 1:8 to 1:40 (weight ratio).

The coating liquid also contains a dispersant to improve the dispersibility of the phosphor in the coating liquid, and a dispersant to improve the bonding force between the binder and the phosphor in the phosphor layer after formation. Examples of dispersants used for such purposes include phthalic acid, stearic acid, caproic acid, lipophilic surfactants, etc. I can do it. Examples of plasticizers include phosphate esters such as triphenyl phosphate, tricresyl phosphate, and diphenyl phosphate; phthalate esters such as diethyl phthalate and dimethoxyethyl phthalate; ethyl phthalyl ethyl glycolate, butyl phthalyl glycolate, etc. and polyesters of polyethylene glycol and aliphatic dibasic acids, such as polyesters of triethylene glycol and adipic acid and polyesters of diethylene glycol and succinic acid.

The coating solution containing the binder on the phosphor produced as described above is first uniformly applied to the surface of the support to form a coating film of the coating solution. This coating operation can be carried out using a conventional coating means such as a Dr.Frede coater, a roll coater, a knife coater, and the like.

The formed coating film is then dried by gradually heating to complete the formation of the phosphor layer on the support. The thickness of the phosphor layer depends on the characteristics of the intended radiation image conversion panel,
Although it varies depending on the type of phosphor, the mixing ratio of the binder and the phosphor, etc., it is usually 20 pm to 1 mm. however,
The layer thickness is preferably between 50 and 500 gm.

Note that the phosphor layer does not necessarily have to be formed by directly applying the coating liquid onto the support as described above; for example, the coating liquid can be separately applied onto a sheet such as a glass plate, metal plate, plastic sheet, etc. and then dried. After forming the phosphor layer by doing this, it may be pressed onto the support, or it may be bonded to the phosphor layer on the support by using an adhesive or the like.

In a typical radiation image conversion panel, a transparent protective film for physically and chemically protecting the phosphor layer is provided on the surface of the phosphor layer opposite to the side that contacts the support. It is preferable to provide such a transparent protective film also in the radiation image conversion panel of the present invention.

The transparent protective film may be made of, for example, a cellulose material such as cellulose acetate or nitrocellulose; or a synthetic polymer material such as polymethyl methacrylate, polyvinyl butyral, polyvinyl phorbul, polycarbonate, polyvinyl acetate, or vinyl chloride-vinyl acetate copolymer. It can be formed by coating the surface of the phosphor layer with a solution prepared by dissolving a transparent polymeric substance in an appropriate solvent. Alternatively, it can also be formed by a method such as adhering a transparent thin film separately formed from polyethylene terephthalate, polyethylene, polyvinylidene chloride, polyamide, etc. to the surface of the phosphor layer using a suitable adhesive. The thickness of the transparent protective film formed in this way is
Preferably, it is about 0.1 to 20 lm.

Next, on one side of the radiation image conversion panel manufactured in this manner, a striped or mesh-like lattice (grid) made of a radiation-absorbing material, which is a characteristic feature of the present invention, is provided.

The grid made of a radiation absorbing material may be provided on either the phosphor layer side surface of the panel (i.e., the phosphor layer surface or support surface) or the support side surface. However, in radiography, X Irradiation of radiation such as lines is performed from the side where this grating is provided.

DESCRIPTION OF THE PREFERRED EMBODIMENTS The form of a radiation image conversion panel provided with a grating according to the present invention will be explained with reference to the accompanying drawings. In addition, Figures 1 to 4
FIG. 1 is a sectional view showing an example of the structure of a panel according to the present invention.

In FIG. 1, a grid 11 made of a radiation-absorbing material is provided on the surface of a protective film of a panel composed of a support 12, a phosphor layer 13, and a protective film 14.

In the figure m2, a grid 21 made of a radiation-absorbing material is provided on the support surface of a panel composed of a support 22, a phosphor layer 23, and a protection [924].

In FIG. 3, a lattice 31 made of a radiation absorbing material is provided on the surface of the phosphor layer of a panel composed of a support 32 and a phosphor layer 33, and a part of the lattice 31 is embedded in the phosphor layer 33. There is.

In FIG. 4, a lattice 41 made of a radiation-absorbing material is provided on the surface of a support of a panel composed of a support 42, a phosphor layer 43, and a protective film 44, and a part of the lattice 41 is embedded in the support 42. ing.

These embodiments show configuration examples of the radiation image conversion panel of the present invention, and the present invention is not limited to the above embodiments. It is sufficient if it is provided in a shape.

Moreover, the lattice made of this radiation-absorbing material has the shape of a stripe made of a plurality of lines or a mesh made of a plurality of lines intersecting each other. The width and spacing of the grating vary depending on the intended use of the radiation image conversion panel, but generally the width of the grating is in the range of 10 to 1100 kL, and the spacing of the grating is in the range of 10 to 1100 kL.
In the range of 500 pm. Also, the thickness and height of the grid)
is the thickness of the part protruding from the panel surface, generally 20
It is in the range of 1mm-1mm.

Examples of the radiation-absorbing material used in this striped or mesh-like lattice include metals with large atomic numbers such as Pb (atomic number 82). The metal may be a single metal or an alloy with other metals such as Sn.

The grid made of radiation absorbing material can be attached by, for example, adhering a separately formed grid to the surface of the panel using a suitable adhesive. Alternatively, the above-mentioned metal may be uniformly deposited on the panel surface and then subjected to a kneeling treatment to perform patterning in a striped or mesh pattern.Alternatively, a transparent plastic film or support for forming a protective film may be used. metal sheet for,
Prepare a plastic sheet etc. in which one end of the grid is embedded and the other end protrudes, and apply adhesive or the like to the surface of the phosphor layer so that the side where the grid does not protrude becomes the bonding surface. It may also be glued.

In addition, when a part of the grid is embedded in the phosphor layer, one end of the grid is uniformly embedded in the coating before the coating of the coating solution for forming the phosphor layer dries and hardens. This allows a grid to be provided. Alternatively, after placing the grid on the support, a part of the grid can be embedded in the phosphor layer by applying a coating liquid to an extent that the grid is not completely buried.

Furthermore, the gaps in the striped or mesh grid provided on the panel surface may be filled with a material that does not absorb radiation, such as a polymeric material, which can strengthen the grid and at the same time It can also function as a protective film for the panel surface.

In the present invention, by attaching a striped or mesh-like lattice made of a radiation-absorbing material to the phosphor layer-side surface or the support-side surface of the radiation image conversion panel as described above, scattered radiation from the subject can be absorbed. can be efficiently absorbed and removed to improve the quality of the resulting image.

Note that the radiation image conversion panel of the present invention is disclosed in Japanese Patent Application Laid-Open No. 55-1
It may be colored with a coloring agent as described in JP-A-63500, JP-A-57-96300, etc.
This coloring can improve the sharpness of the resulting image. Further, in the radiation image conversion panel of the present invention, white powder may be dispersed in the phosphor layer for the same purpose as described in Japanese Patent Application Laid-Open No. 146447/1983.

[Brief explanation of drawings]

FIGS. 11 to 4 are sectional views each showing an example of the configuration of a radiation image conversion panel according to the present invention. 11.21, 31, 41: Grid 12. 22, 32, 42: Support 13. 23, 33, 43: Phosphor layer 14. 24, 44: Protective film

Claims (1)

[Scope of Claims] 1. A radiation image conversion panel comprising a support and a phosphor layer provided on the support and comprising a binder containing and supporting a stimulable phosphor in a dispersed state, the panel A radiation image conversion panel characterized in that a striped or mesh-like lattice made of a radiation-absorbing material is attached to one side of the panel. 2. The radiation image storage panel according to claim 1, wherein the radiation absorbing material is a metallic material containing 50% or more of a metal having an atomic number of 82 or more. 3. The radiation image conversion panel according to claim 1, wherein the thickness of the grating is in the range of 20 μm to 1 mm. 4. The radiation image conversion panel according to claim 1, wherein the grating is provided on the surface on the side of the phosphor layer, and a part of the grating is embedded in the phosphor layer. 5. The radiation image conversion panel according to claim 1, wherein the grating is provided on the surface of the support, and a portion of the grating is embedded in the support.