JPS6290600A - 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, a radiation image conversion method using a stimulable phosphor, as described in Japanese Patent Application Laid-Open No. 55-12145, has been attracting attention as an alternative method to the above-mentioned radiographic method. became. 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 radiation image conversion method described in L has a basic structure consisting of a support and a phosphor layer provided on one side of the support.

Note that a transparent protective film made of a polymeric substance is generally provided on the opposite surface of the support (the surface not facing the support) of the phosphor layer. protects it 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 radiation transmitted through the subject or emitted from the subject is absorbed by the phosphor layer of the radiation image conversion panel in proportion to the amount of radiation, and the radiation image of the subject or subject is displayed on the radiation image conversion panel. is formed as an accumulated image of radiation energy. This accumulated image can be emitted as stimulated luminescence by time-series excitation with distributed electromagnetic waves, and by photoelectrically reading this stimulated luminescence and converting it into an electrical signal, the accumulated image of radiation energy can be obtained. It becomes possible to create an image.

The radiation image conversion method is a very advantageous 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, granularity, etc.) of the image is 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.

During radiography, some of the radiation such as X-rays irradiated to the subject is scattered by the subject, and 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). Since the accumulated radiation energy interferes with image formation, the quality of the resulting image, such as resolution, tends to deteriorate.

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 can prevent excitation light from spreading in a phosphor layer.

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

The purpose of item 2 is to provide a radiation-absorbing material in a radiation image storage panel having a support and a phosphor layer formed on the support and a binder containing and supporting a stimulable phosphor in a dispersed state. This is achieved by the radiation image conversion panel of the present invention, characterized in that at least a portion of a striped or mesh-like lattice made of a substance is embedded in the phosphor layer, and the lattice does not protrude from the panel surface. be able to.

The present invention firstly provides a phosphor layer of a radiation image conversion panel with xi
By embedding at least a portion of a grid capable of absorbing radiation such as, radiation scattered by a subject during radiography can be easily and efficiently removed.

That is, according to the present invention, since the striped or mesh-like grid made of a radiation-absorbing material is embedded in the phosphor layer of the panel, it is not necessary to photograph the scattered radiation removal plate again as in the conventional method. The radiation imaging system can be simplified since there is no need to place it in the system. In addition, 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 exists directly in the phosphor layer. That is, since a lattice exists in the phosphor layer itself in which an image of accumulated radiation energy is formed, only scattered radiation can be removed more efficiently than before.

Therefore, without increasing the radiation dose of the subject,
Images with excellent image quality such as resolution can be obtained.

Second, since the phosphor layer is divided into stripes or meshes by the above-mentioned lattice, it is possible not only to remove the radiation scattered by the subject, but also to read out the accumulated radiation energy image as photostimulated light. It is possible to prevent the excitation light from spreading in the phosphor layer due to scattering, etc., and the quality of the obtained image can be further improved.

Furthermore, if the striped or mesh-like grid is made of metal such as lead, the mechanical strength of the phosphor layer can be increased and the panel itself can be reinforced.

If a part of the above-mentioned grid extends into the protective film provided on the phosphor layer, the radiation is normally irradiated from the protective film side of the panel, so scattered radiation can be removed even more efficiently. It is also possible to increase the mechanical strength of the protective film.

[Structure of the Invention] The form of the radiation image conversion panel of the present invention in which a striped or mesh-like lattice made of a radiation-absorbing material is embedded will be described with reference to the accompanying drawings. In addition, Fig. 1 and f5
FIG. 2 is a sectional view showing an example of the structure of a panel according to the present invention.

In FIG. 1, the radiation image conversion panel is composed of a support 12, a phosphor layer 13 and a protective film 14, and a lattice 11 made of a radiation absorbing material is present in the phosphor layer 13.

In FIG. 2, the radiation image conversion panel is composed of a support 22, a phosphor layer 23, and a protective film 24, and a grating 21 made of a radiation absorbing material has a phosphor layer 23 and a protective film 24.
Exists in 1!24.

These embodiments show examples of the structure of the radiation image storage panel of the present invention, and the present invention is not limited to the above embodiments. may be present in, however,
In that case, it is preferable to irradiate the radiation from the support side.Also, this grating does not have to have the same thickness as the phosphor layer and may be thinner than that, but in that case, the radiation irradiation It is preferable that the grid be closer to the side of the panel surface (usually the phosphor layer surface or the IS surface).

The radiation image storage panel of the present invention having the above-mentioned preferable characteristics 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, etc., metal sheets such as aluminum foil, aluminum alloy foil, regular paper, baryta paper, resin coated paper, pigments such as titanium dioxide, etc. Examples include paper sized with polyvinyl alcohol, 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, a phosphor layer is provided 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 surface of the support on the side to be coated to form an adhesion imparting 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. A light absorption layer is also provided.8 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 adhesion-imparting layer, a light-reflecting layer, a light-absorbing layer, etc. are provided on the surface (meaning the surface thereof), fine irregularities may be uniformly formed thereon.

Next, a phosphor layer is formed on the support.

The phosphor layer is basically a layer made of a binder that contains and supports particles of stimulable phosphor in a dispersed state.9 In the present invention, this phosphor layer has striped or All or part of the grid is embedded.

A grating made of a radiation-absorbing material, which is a characteristic feature of the present invention, has the shape of a stripe made up of a plurality of parallel lines or a mesh shape in which a plurality of lines intersect. 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 IL.
The lattice spacing is in the range 10 to 5004 m. Further, the thickness (height) of the grating is usually 50% or more of the layer thickness of the phosphor layer, and therefore is generally in the range of 20 p, m -1 mm, although it varies depending on the layer thickness of the phosphor layer. Preferably, the thickness is the same as or thicker than that of the phosphor layer. However, in the present invention, the grating is embedded in the panel centering around the phosphor layer and does not protrude from the panel surface.

Examples of the radiation-absorbing material used in the 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.

In addition, as mentioned above, stimulable phosphors are phosphors that exhibit stimulated luminescence when irradiated with radiation and then irradiated with excitation light. It is desirable that the phosphor be a phosphor that exhibits stimulated luminescence in a wavelength range of 300 to 500 nm when subjected to a certain excitation light. Examples of stimulable phosphors used in uninvented radiation image storage panels include SrS:Ce, Sm, and SrS:Eu as described in U.S. Pat. No. 3,859,527.

Sm, Th02:Er, and La20zS:Eu,
Sm, ZnS described in JP-A-55-12142
:Cu, Pb, BaO*xAR20, :Eu (however,
0.8≦X≦IO), and M'0-xsi02:A
(However, M is Mg, Ca, Sr, Zn, Cd, or Ba, and A is Ce, Tb, Eu, Tm, Pb, T
I, Bi, or Mn, and X is 0.5≦X≦2.
5), described in JP-A-55-12143 (Ba
, -, -, , Mgx, Cay) FX: aEu2f (where X is CA and Brc7), x8 and y are 0, X+y≦0.6, and xy
≠0, and a is 1O-6≦a≦5X10-2), LnO described in JP-A-55-12144
X+xA (Ln is La, Y, Gd, and Lu
At least one of them, X is C! ; at least one of L and Br, A is at least one of Ce and Tb, and X is o<x<o, 1), as described in JP-A-55-12145. ing(
Bat-x, M”x) FX: yA (However.

M2° is at least one of Mg, Ca, Sr, Zn, and CD; X is at least one of C1, Br, and ■; A is Eu, Tb, Ce, Tm, Dy, and P.
At least one of r, Ha, Nd, Yb, and Er, where X is 0≦X≦0.6, and y is O≦y≦0
．． 2), M”FXe xA : yLn [However, 1MI is Ba, Ca, Sr, Mg, Zn, and Cd
At least one of them, A is Bed, MgO, CaO
, 5rO1Bad, ZnO1AfL20. ,Y.

01, La2O3, I n203, S io2, TlO
2, ZrO2, GeO2, 5n02, Nb2O6, T
a 205, and at least one of T h O2 (7), and Ln is Eu, Tb, Ce, or Tm.

Dy, Pr, Ho, Nd, Yb, Er, S
m, and at least one of Gd, and X is C! ;L
, Br, and I, and X and y are respectively 5X10-8≦X≦0.5, and O
y≦0.2] A phosphor represented by the composition formula (
Bat-x + M' II) F2'' a B
& X 2 :yEu, zA [However, Ml is beryllium, magnesium, calcium, strontium, zinc.

and at least one of cadmium, X is chlorine,
At least one of bromine and iodine, A is at least one of zirconium and scandium, and a, x, y, and 2 are each 0.5≦a≦1
．． 25.0≦X≦1, io-'≦y≦2XIO-', and O<z≦10-2.

It is described in Japanese Patent Application Laid-open No. 57-23673 (Ba
t-x, M”x)F2・aBaX2:yEu,
zB [However, Ml is beryllium, magnesium, calcium, strontium, and zinc.

and at least one of cadmium, X is chlorine,
at least one of bromine and iodine, a,
X, y, and 2 are each 0.5≦a≦1.25.0
≦X≦1.10-'≦y≦2×10-' and 0<z
≦2
,,,M”X)F2 e aBaX2 :yEu,
zA [However, MH 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.・A species, a, x, y, and Z are each 0.5≦a≦1.25.0≦X≦1.10-6≦y
≦2×io−′, and O<z≦5×10−′]
A phosphor represented by the composition formula M”O described in JP-A No. 58-69281
X: xCe [However, M is Pr, Nd, Pm, Sm,
Eu, Tb, ay, Ho, Er, Tm, Yb, and B
is at least one trivalent metal selected from the group consisting of i, and X is C! ;J, and any one of Br=・
or both, and X is O<x<0.1], Ba described in JP-A-58-206678
, -, MX7□Lx, 2FX: yEu" [However,
M represents at least one alkali metal selected from the group consisting of Li, Na, Rb, and Cs; L represents Sc, Y, La, Ce, Pr, Nd, Pm, Sm, G
d, Tb, Dy, Ho, Er, Tm, Yb, Lu
, represents at least one trivalent metal selected from the group consisting of An, Ga, In, and Tl; X is C9,
, Br, and at least one halogen selected from the group consisting of
．． 5, y is 0 and y≦0.1] A phosphor represented by the composition formula: BaF described in JP-A No. 59-27980
XexA: yEu2° [However, X is.

is at least one halogen selected from the group consisting of C1, Br, and ■; A is a fired product of a tetrafluoroboric acid compound; and X is 10-"≦X≦0
．． 1, y is o<y≦0.1] A phosphor represented by the composition formula: BaF described in JP-A No. 59-47289
XexA: yEu2° [where X is at least one halogen selected from the group consisting of C1, Br, and I; A is monovalent or A fired product of at least one compound selected from the group of hexafluoro compounds consisting of salts of divalent metals;
And, X is 10-"≦X≦o, and t, y are o<y≦0.
A phosphor represented by the composition formula 1], JP-A-59-
BaFX* xNa described in Publication No. 56479
X': aEu" [wherein X and X' are each at least one of C1, Br, and
X and a are respectively 0<x≦2 and 0<a≦0.
2] is a phosphor represented by the composition formula M'F described in JP-A-59-56480.
X@xNaX':yEu'': zA [However, Ml is at least one alkaline earth metal selected from the group consisting of Ba, Sr, and Ca; X and X' are C1 and Br, respectively.

and I is at least one halogen selected from the group consisting of; A is at least one transition metal selected from V, Cr, Mn, Fe, Go, and Ni;
and X is O<X≦2, y is o<y≦0.2, and 2 is O<z≦10-2], JP-A-59-75200 Listed in L/%6M
” FX * aM 'X'
* bM ' Seal X '' 2 Conflict c
M”X”3 * xA: yEu” [However, Ml
is at least one kind of alkaline earth metal selected from the group consisting of Ba, Sr, and Ca, and M1 is Li
, Na, Rh, and Cs; MI is at least one divalent metal selected from the group consisting of Be and Mg; MI is An, Ga, In , and at least one trivalent metal selected from the group consisting of Tu: A
is a metal oxide; X is at least one halogen selected from the group consisting of C1, Br, and
', x'', Oyobi ≦1
0-2, C is 0≦C≦10-2, and a+b+c≧10
-”; X is O<x≦0.5, y is 0<7≦0.2
A phosphor represented by the composition formula of at least one kind of alkaline earth metal selected from the group consisting of; X and X'' are at least one kind of halogen selected from the group consisting of C1, Br, and Yes; and a is 0.1≦a≦10.0. x is O<X≦0
．． 2] is a phosphor represented by the composition formula M"FX* aM'X' :
MI is at least one alkaline earth metal selected from the group consisting of Ba, Sr and Ca; Ml is at least one alkali metal selected from the group consisting of Rb and Cs; at least one kind of halogen selected from the group; xo is F
, C1, Br, and I; and a and X are O≦a≦4.0 and 0<x≦0.2, respectively. phosphor, patent application filed by the applicant in 1986-7
M'X:xBi described in the specification of No. 0484 [where Ml is at least one alkali metal selected from the group consisting of Rb and Cs;
Phosphor 2 is at least one kind of halogen selected from the group consisting of (1) and (1); and X is a numerical value in the range of O<x≦0°2.

In addition, the M"X, .aM"X'2: ”X
It may be contained in a proportion of 21 moles or less.

bMIX" described in Japanese Patent Application No. 59-22169 filed by the present applicant (where Ml is Rb and C
at least one kind of alkali metal selected from the group consisting of s, X'' is at least one kind of halogen selected from the group consisting of F, C, Br and
is o<b≦10.0); Patent application 1987-77225
bKX''* cMgX''2e
dMIX''3 (However, MI is Sc, Y, La,
is at least one trivalent metal selected from the group consisting of Gd and Lu, and X'', X'' and X'' are all F
, C1, Br, and ■, and S, c, and d are respectively 0≦b≦2゜0, O≦C≦2.0.0≦d≦2.
VB described in Japanese Patent Application No. 59-84356 (however, y is 2 X 10-'≦y≦2XlO-
bA described in Japanese Patent Application No. 59-84358 (where A is at least one kind of fermentation product selected from the group consisting of 5i02 and P2O5,
and b is 1O-4≦b≦2X10-'); bsi described in Japanese Patent Application No. 59-240452
O (however, b is o<b≦3X10-2); 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, Cf; L, Br and I, and b satisfies o<b≦10−3); Applicant It is stated in the specification of Japanese Patent Application No. 60-78033 by
b CsX” * c S nX”2 (Start, X”
and
0 Shima≦C≦2X10-2); and b described in the specification of Japanese Patent Application No. 60-78035 filed by the present applicant.
CsX”・yLn3◆(However, X” is F, C2, Br
and Ln is at least one halogen selected from the group consisting of Sc, Y, Ce, Pr, Nd, Sm
.

Gd, Tb, Dy, Ho, Er, Tm, Yb and Lu
at least one rare element selected from the group consisting of, and b and y each satisfy o<b≦10.0.
and 10-6≦y≦1.8XIO-').

etc. can be mentioned.

Among the above-mentioned stimulable phosphors, -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. However, the stimulable phosphor used in the present invention is not limited to the above-mentioned phosphors, but any phosphor that exhibits stimulated luminescence when irradiated with radiation and then irradiated with excitation light. It may be.

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, ethylcellulose, vinylidene chloride/vinyl chloride copolymer, polyalkyl (meth)acrylate, vinyl chloride/vinyl acetate Binders typified by synthetic polymeric materials such as copolymers, polyurethanes, cellulose acetate butyrate, polyvinyl alcohol, linear polyesters, etc. may be mentioned. Particularly preferred among such binders are nitrocellulose, linear polyester,
These are polyalkyl (meth)acrylates, mixtures of nitrocellulose and linear polyesters, and mixtures of nitrocellulose and polyalkyl (meth)acrylates.

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

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

First, an old friend, a binder on a stimulable phosphor, is added to a suitable solvent and mixed thoroughly to prepare a coating solution in which 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-7'tanol; chlorine-containing hydrocarbons such as methylene chloride and ethylene chloride; acetone, methyl ethyl ketone, and methyl isobutyl ketone. Ketones such as; 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 solution varies depending on the characteristics of the intended radiation image conversion panel, the type of phosphor, etc., but in general, the mixing ratio between the binder and the phosphor is l :1 to 1:100 (weight ratio), and particularly preferably l:8 to 1:40 (weight ratio).

The coating solution also contains a dispersant to improve the dispersibility of the phosphor in the coating solution, 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., which may be mixed with various additives such as plasticizers. can. 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 prepared as described in Section L is then 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 conventional coating means such as a doctor blade, roll coater, knife coater, etc.

A lattice made of radiation-absorbing material, e.g.

The grid can be installed by uniformly embedding a separately formed grid into the coating before the coating of the coating solution dries and hardens. Alternatively, after placing the grid on the support,
The grating can be embedded in the phosphor layer by applying the coating liquid to the extent that it is completely hidden. Or again,
It is also possible to form a lattice in advance on the support by uniformly depositing a radiation-absorbing substance such as a metal on the surface of the support and then etching it to form a striped or mesh pattern.

In addition, if the grid is embedded not only in the phosphor layer but also in the protective film, each coating solution for forming the phosphor layer and the protective film may be applied simultaneously after or before installing the grid. By coating, a phosphor layer and a protective film can be simultaneously formed on the support. Alternatively, a transparent plastic film for forming a protective film with one end of the grid embedded and the other end protruding may be prepared in advance, and the grid may be inserted before the coating of the phosphor layer dries. When the grating is embedded in the phosphor layer and the support, one end of the grating may be embedded and the other end is the bonding surface. A lattice can be provided by applying and forming a phosphor layer on the protruding side of the grating f using a protruding support.

The formed coating film is then dried by gradual heating to complete the formation of the support for the grid-embedded phosphor layer (or phosphor layer and protection 112). The thickness of the phosphor layer varies depending on the characteristics of the intended radiation image conversion panel, the type of phosphor, the mixing ratio of the binder and the phosphor, but is usually 20 pm to 1 mm. However, the thickness of this layer is preferably 50 to 500 pm.

Note that the phosphor layer (and protective film) does not necessarily need to be formed by directly applying a coating liquid onto the support as described above, but may be formed by separately applying it to a sheet If, such as a glass plate, metal plate, or plastic sheet. After forming a phosphor layer by applying a liquid and drying it, press it against a support weight, or
Alternatively, the phosphor layer on the support may be bonded to the phosphor layer using an adhesive. In this case as well, the lattice made of the radiation-absorbing material may be bonded to the phosphor layer (or the phosphor layer) in the same manner as above. can be embedded in a gI membrane or a phosphor layer and support).

A transparent protective film for physically and chemically protecting the phosphor layer may be provided on the surface of the phosphor layer opposite to the side in contact with the support.

Transparent+Ji protective films are made of, for example, cellulose derivatives such as cellulose acetate and nitrocellulose; or synthetic polymeric substances such as polymethyl methacrylate, polyvinyl butyral, polyvinyl formal, polycarbonate, polyvinyl acetate, and vinyl chloride/vinyl acetate copolymers. It can be formed by applying a solution prepared by dissolving a transparent polymer substance in a suitable solvent onto the surface of the phosphor layer. Or polyethylene terephthalate,
It can also be formed by a method such as adhering a transparent thin film separately formed from polyethylene, polyvinylidene chloride, polyamide, etc. to the surface of the phosphor layer using a suitable adhesive. The thickness of the transparent protective film thus formed is preferably about 0.1 to 20 m.

The present invention efficiently reduces scattered radiation from an object by embedding all or part of a striped or mesh-like lattice made of a radiation-absorbing material in the phosphor layer of a radiation image conversion panel as described above. It can be well absorbed and removed, and can prevent the excitation light from scattering in the phosphor layer, thereby improving the quality of the image obtained.

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]

FIG. 1 and FIG. 2 are sectional views each showing a configuration example of a radiation image conversion panel according to the present invention.

Claims (1)

[Scope of Claims] 1. A radiation image conversion panel having a support and a phosphor layer provided on the support and comprising a binder containing and supporting a stimulable phosphor in a dispersed state. 1. A radiation image conversion panel characterized in that at least a part of a striped or mesh-like lattice made of a chemical substance is embedded in the phosphor layer, and the lattice does not protrude from the panel surface. 2. The radiation image conversion 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 less. 3. The radiation image conversion panel according to claim 1, wherein the thickness of the grating is 50% or more of the layer thickness of the phosphor layer. 4. A patent claim characterized in that a protective film is provided on the surface of the phosphor layer opposite to the side on which the support is provided, and a portion of the lattice is embedded in the protective film. The radiation image conversion panel according to item 1.