JPH11265035A - Cassette for x-ray radiography - Google Patents

Abstract

PROBLEM TO BE SOLVED: To accurately place a shielding member in the case of division photographing, and to perform photographing at an accurate division position and to fix a photographic section in the case of multiple division by providing a mark for division photographing on the X-ray radiation surface of a case. SOLUTION: Such a mark for division photographing 920 that the front surface(surface of a case main body 901: X-ray radiation surface) of a cassette is quadrisected is recorded on the front surface. Namely, the mark 920 is recorded at a position where a radiation picture conversion plate in the cassette is quadrisected. The mark 920 is constituted of a paint whose X-ray absorption is small and which does not hinder X-ray radiography. In the case of division photographing, for example, bisected photographing, a shielding plate 1100 is placed to be aligned with the mark 920 on the cassette, so that the division photographing is performed at the accurate photographing position in the case of division photographing. In the case of quadrisected photographing, the division photographing is executed by covering the 3/4 area with the shielding plate 1100.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an X-ray imaging cassette accommodating a radiation image information recording medium, and more particularly to an X-ray imaging cassette suitable for divided imaging.

[0002]

2. Description of the Related Art Radiation (X-ray, α-ray,
When irradiated with β-rays, r-rays, ultraviolet rays, etc.), a part of the radiation energy is accumulated in the phosphor. It is known that when this phosphor is irradiated with excitation light such as visible light, the phosphor emits stimulated emission according to the stored energy. Phosphors exhibiting such properties are called storage phosphors or stimulable phosphors.

A stimulable phosphor (radiation image conversion plate such as a stimulable phosphor plate) in which radiation image information of a human body or the like is once provided on a sheet by utilizing the stimulable phosphor.
The radiation image conversion plate is scanned with excitation light such as laser light to generate stimulated emission light, and the obtained stimulated emission light is photoelectrically read to obtain an image signal. .

[0004] As another method, a plurality of pixels are 2 pixels.
There is also a method of obtaining radiation image information by using radiation detectors arranged in a dimension. In this method, electric charges corresponding to the intensity of irradiated radiation are generated in a photoconductive layer, electric charges generated by two-dimensionally arranged microplates are read out and accumulated, and image data is stored based on the accumulated electric charge. Is generated and read.

[0005] In the above-described case, a plurality of images are printed by using an area of one radiation image conversion plate by dividing it into a plurality of areas by an imaging technique called divisional imaging.

[0006]

In the case of performing such a divisional photographing, conventionally, the photographing has been performed in a state where a lead plate for blocking X-rays is superposed on a cassette.

[0007] For this reason, the position of the dividing line is not accurately determined, so that each divided photographing is different. Also,
In the case of multi-segmentation, it is not determined which section is the photographing area. That is, in the case of four-division three-division photography in which the entire cassette is divided into four parts, and three parts are photographed, it is not determined which division is to be used for photographing and which division is not used for photography.

As a result, it is necessary to perform complicated division pattern recognition processing on the reading device side or to input photographing area information to the reading device. The present invention has been made in view of the above-described problems, and an object of the present invention is to perform divided photographing at an accurate divided photographing position at the time of divided photographing, and to fix a photographing section in the case of multiple division. An object of the present invention is to provide an X-ray imaging cassette.

[0009]

Accordingly, the invention as a means for solving the problem is described below. (1) The invention according to claim 1 has a case for accommodating a radiation image information recording medium, and a mark for divisional imaging is provided on an X-ray irradiation surface of the case. Cassette.

In this cassette for radiography, the X
Since the line irradiation surface is provided with the mark for divided photographing, the shielding member can be accurately placed at the time of divided photographing, and divided photographing can be performed at an accurate divided photographing position. Further, in the case of multi-division, it is possible to fix the shooting section.

(2) The invention according to claim 2 comprises a case for accommodating a radiation image information recording medium, and an X-ray shielding member, wherein the X-ray is movable in an X-ray irradiation surface of the case. Shielding means configured to cover a part of the irradiation surface,
A cassette for X-ray imaging characterized by having:

In this cassette for X-ray imaging, the shielding means is configured to cover a part of the X-ray irradiation surface while being movable on the X-ray irradiation surface of the case. Thus, the shielding member can be accurately moved, and the divided photographing can be performed at the determined divided photographing position.

(3) The invention according to claim 3 is characterized in that (2) X
In the radiographic cassette, a mark for divisional radiography is provided on the X-ray irradiation surface of the case. This X
In the X-ray cassette, the shielding means covers a part of the X-ray irradiation surface in a state where it can be moved on the X-ray irradiation surface of the case, and a mark for divisional imaging is provided on the X-ray irradiation surface. Therefore, by aligning with the divisional photographing mark, the shielding member can be accurately moved at the time of the divisional photographing, and the divisional photographing can be performed at an accurate divisional photographing position. Further, in the case of multi-division, it is possible to fix the shooting section.

(4) The invention according to claim 4 is characterized in that in the cassette for X-ray imaging according to (1) or (3), the mark for divisional imaging indicates a division of imaging at the time of divisional imaging. And

In this cassette for radiography, the X
Since the line irradiation surface is provided with a division photographing mark indicating a division of the division photographing, the shielding member can be accurately placed at the time of the division photographing, and the division photographing can be performed at an accurate division photographing position. . Further, in the case of multi-division, it is possible to fix the shooting section.

(5) The invention according to claim 5 is characterized in that, in the cassette for X-ray imaging according to (1) or (3), the marks for divided imaging indicate the order of imaging in the divided imaging. And

In this cassette for X-ray photography, the X
Since the line irradiation surface is provided with the divisional imaging mark indicating the order of the divisional imaging, the shielding member can be accurately placed at the time of the divisional imaging, and the divisional imaging can be performed in the correct order. Further, in the case of multi-segment, it is possible to fix the photographing section and photograph in the correct order.

(6) In the invention according to claim 6, in the X-ray imaging cassette according to (1) or (3), the divisional imaging mark is constituted by a dividing line parallel to a case periphery. It is characterized by the following.

In this cassette for radiography, the X
Since the line irradiation surface is provided with the mark for divisional imaging by the divisional line parallel to the edge of the case, the shielding member can be accurately placed at the time of divisional imaging.

(7) In the invention according to claim 7, in the cassette for X-ray photography according to (1) or (3), the mark for divided photography is asymmetrically constituted by a division line parallel to the periphery of the case. It is characterized by having.

In this cassette for radiography, the X
Since the line-irradiated surface is provided with a divisional imaging mark asymmetrically formed by a division line parallel to the edge of the case, divisional imaging can be performed in an accurate order.

(8) In the X-ray imaging cassette according to (1) or (3), the divisional imaging mark is divided into a plurality of areas according to the divisional imaging. A portion corresponding to at least one region is displayed differently from a portion corresponding to the remaining region.

In this cassette for X-ray photography, it is possible to accurately place the shielding member at the time of divided photography, to perform divided photography at an accurate divided photography position, and to fix the photography section in the case of multiple division. It becomes possible to do.

(9) The invention according to claim 9 is characterized in that:
(8) In the X-ray imaging cassette, the radiation image information recording medium is a radiation image conversion plate having a stimulable phosphor.

In this cassette for X-ray imaging, a radiation image conversion plate having a stimulable phosphor is accommodated as a radiation image information recording medium, and a shielding member can be accurately placed at the time of divided imaging. In other words, divided photographing can be performed at an accurate divided photographing position, and in the case of multi-segment photographing, the photographing section can be fixed.

(10) The invention according to claim 10 is characterized in that (1)
(8) In the cassette for radiography described in (8), the radiation image information recording medium is a radiation detector in which a plurality of pixels are two-dimensionally arranged.

In this cassette for X-ray imaging, a radiation detector in which a plurality of pixels are two-dimensionally arranged is accommodated as a radiation image information recording medium, and a shielding member is accurately placed at the time of divided imaging. This makes it possible to perform divided photographing at an accurate divided photographing position, and in the case of multiple division, it is possible to fix the photographing section.

[0028]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS A radiographic cassette and a radiographic image recording and reading apparatus using the radiographic cassette as an embodiment of the present invention will be described with reference to the drawings.

<1. Cassette> The cassette 9 of this embodiment will be described in detail with reference to FIG. A cassette containing a radiation image conversion plate or a radiation detector in which a plurality of pixels are two-dimensionally arranged is configured as shown in FIGS. 1 and 2 and FIGS. 3 to 10.

Here, FIG. 1 is a perspective view schematically showing a state in which a shielding plate is placed on a cassette to execute divided photographing, and FIG. 2 is a schematic view showing an X-ray irradiation surface (front surface) of the cassette. FIG. 3 is a perspective view showing a state where the radiation image conversion plate is stored in the cassette, FIG. 4 is a perspective view showing a state where the radiation image conversion plate is pulled out from the cassette, FIG. 5 is a plan view of the cassette, 6 is a plan view showing a state where the radiation image conversion plate is stored in the cassette, FIG. 7 is a side view of the cassette, FIG. 8 is a cross-sectional view taken along a cutting line CC in FIG. 5, and FIG. 9 is a cross-sectional view taken along a cutting line DD in FIG. FIG. 10
FIG. 6 is a sectional view taken along section line EE in FIG. 5.

First, the outline of the cassette 9 will be described mainly with reference to FIGS. In these figures, the cassette 9 is integrated with a case half 900 on the back surface and a case half 901 on the front surface (X-ray irradiation surface) by tightening the periphery with screws 902.

As shown in FIG. 4, an opening 903 is formed on one side of the cassette 9, and the radiation image conversion plate 12 can be pulled out of the opening 903 by a cap 907.

The radiation image conversion plate 12 has a stimulable phosphor layer, and the stimulable phosphor layer accumulates energy according to the radiation transmittance distribution of the object with respect to the amount of radiation irradiated from the radiation source. To form a latent image. The radiation image conversion plate 12 is provided with a stimulable phosphor layer by vapor deposition or coating. The stimulable phosphor layer is shielded or covered by a protective member in order to prevent adverse effects and damage due to the environment.

The radiation image conversion plate 12 is a plate having a stimulable phosphor. The stimulable phosphor accumulates energy in accordance with the radiation transmittance distribution of the subject with respect to the amount of irradiation radiation from the radiation source to form a latent image. The stimulable phosphor is preferably a stimulable phosphor.

It is preferable that the stimulable phosphor plate has a stimulable phosphor layer provided on a support by vapor deposition or coating. The layer of the stimulable phosphor is preferably shielded or covered by a protective member in order to prevent adverse effects or damage due to the environment.

Preferred stimulable phosphors include:
For example, the following stimulable phosphors are exemplified, but not limited thereto. [1] _{M'X · aM "X 2 · bM} '" X 5: stimulable phosphor represented by cA (where, M' is Li, Na, K, of at least one selected from Rb and Cs M ″ is B
e, Mg, Ca, Sr, Ba, Zn, Cd, Cu and N
It is at least one kind of divalent metal selected from i.
M ′ ″ is Sc, Y, La, Ce, Pr, Nd, Pm, S
m, Eu, Gd, Tb, Dy, Ho, Er, Tm, Y
It is at least one kind of trivalent metal selected from b, Lu, Al, Ga and In. X, X ₂ and X ₅ represent halogen. A is Eu, Tb, Ce, Tm, Dy, Pr, H
o, Nd, Yb, Er, Gd, Sc, Lu, Sm, Y,
It is at least one metal selected from Tl, Na, Ag, Cu and Mg. A is a numerical value in the range of 0 <a <0.5, b is a numerical value in the range of 0 ≦ b ≦ 0.5, and c is a numerical value in the range of 0 <c ≦ 0.2. )
A specific example is described in JP-A-61-72087.

[2] (Ba _1-xy Mg _x Ca _y ) FX: e
A stimulable phosphor represented by Eu (where X is at least one of Br and Cl, and x, y and e are respectively 0 <x + y <0.6, 10
It is a number that satisfies ⁻⁶ ≦ e ≦ 5 × 10 ⁻² . A specific example is described in JP-A-55-12143.

[3] BaFX: a stimulable phosphor represented by xCe, yA (where X is at least one of ClBr and I,
A is at least one of In, Tl, Gd, Sm and Zn, and x and y are each 0 <x ≦ 2 × 10 ⁻¹
And 0 <y <5 × 10 ⁻² . A specific example is described in JP-A-55-84389.

[4] BaSO ₄ : A _x (where A is at least one of Dy, Tb and Tm, and x is a number satisfying 0.001 ≦ x ≦ 1) Examples are described in JP-A-48-80487.

[5] SrSO ₄ : A _x (where A is at least one of Dy, Tb and Tm, and x is a number satisfying 0.001 ≦ x ≦ 1) Examples are described in JP-A-48-80489.

[6] Li ₂ O. (B ₂ O ₂ ) _x : Cu (where x is a number satisfying 2 ≦ x ≦ 3) A specific example is described in JP-A-53-39277. It is described in the gazette.

[7] Li ₂ O · (B ₂ O ₂ ) _x : Cu, Au (where x is a number satisfying 2 ≦ x ≦ 3) A specific example is disclosed in No. 47883.

[8] SrS: Ce, Sm A specific example is described in US Pat. No. 3,859,527.

[9] SrS: Eu, Sm A specific example is described in US Pat. No. 3,859,527.

[10] La ₂ O ₂ S: Eu, Sm A specific example is described in US Pat. No. 3,859,527. [11] (Zn _1-x Cd _x ) S: A, X (where A is at least one metal selected from Cu, Ag, Au, and Mn. X represents halogen. X
Indicates a number satisfying 0 ≦ x ≦ 1. Note that a specific example is
U.S. Pat. No. 3,859,527 or JP-A-5-15-1
No. 60078 describes this.

[12] (Zn _1-x Cd _x ) S: A (where A is at least one metal selected from Cu, Ag, Au, Mn and Pb. X is 0 ≦ x ≦ 1
Indicates a number that satisfies Incidentally, specific examples are described in JP-A-55-12142 or JP-A-5-160078.

[13] Stimulable phosphor represented by MO.xSiO ₂ : A (where M is at least one kind of divalent metal selected from Mg, Ca, Sr, Ba, Zn and Cd). A is E
It is at least one metal selected from u, Tb, Ce, Tm, Pb, Tl, Bi and Mn. A is 0
<A <0.5, where x is 0.5 ≦ x ≦
It is a number that satisfies 2.5. A specific example is described in JP-A-55-12142.

[14] LnOX: stimulable phosphor represented by xA (where Ln is at least one kind of trivalent metal selected from Y, La, Gd and Lu. X is selected from Cl and Br) At least one type of halogen, wherein A is T
At least one metal selected from b and Ce. X is a number satisfying 0 <x <0.1. A specific example is described in JP-A-55-12144.

[15] Stimulable phosphor represented by (Ba _1-x M _x ) FX: yA (where X is at least one of I, Br and Cl, and A is In, Tl , Gd, Sm, and Zr, and x and y are numbers satisfying 0 <x <0.6 and 0 ≦ y ≦ 0.2, respectively.) It is described in JP-A-55-12143.

[16] M "FX.xA: stimulable phosphor represented by cLn (where M" is Mg, Ca, Sr, Ba, Zn and Cd
At least one type of divalent metal selected from A is BeO, MgO, CaO, SrO, BaO, ZnO, A
l ₂ O ₂ , Y ₂ O ₂ , La ₂ O ₂ , Nd ₂ O ₂ , In ₂ O ₂ , Si
O ₂ , TiO ₂ , ZrO ₂ , GeO ₂ , SnO ₂ , ThO ₂ ,
It is at least one selected from Nb ₂ O ₅ and Ta ₂ O ₅ . X represents at least one halogen selected from I, Br and Cl. Ln is Eu, Tb, Ce, Tm, D
y, Pr, Ho, Nd, Yb, Er, Gd, Sc, L
u, Sm, Y, Tl, Na, Ag, Cu, and at least one metal selected from Mg. A is 0 <
a is a numerical value in the range of <0.5, b is a numerical value in the range of 0 ≦ b ≦ 0.5, and c is a numerical value in the range of 0 <c ≦ 0.2. A specific example is described in JP-A-55-160078.

[17] A stimulable phosphor represented by xM ₃ (PO ₄ ) ₃ .NX ₃ .yA (where M and N are Mg, Ca, Sr, Ba,
It is at least one kind of divalent metal selected from Zn and Cd. X and X ₂ each represent at least one kind of halogen selected from F, Cl, Br and I. A is E
u, Tb, Ce, Tm, Dy, Pr, Ho, Nd, Y
It is at least one metal selected from b, Er, Sb, Tl, Mn and Sn. Further, x is a number satisfying 0 <x ≦ 6, and y is a number satisfying 0 ≦ y ≦ 2. A specific example is described in JP-A-59-38278.

[18] A stimulable phosphor represented by M ₃ (PO ₄ ) ₃ .yA (where M is Mg, Ca, Sr, Ba, Zn and Cd
At least one type of divalent metal selected from A is Eu, Tb, Ce, Tm, Dy, Pr, Ho, Nd, Y
It is at least one metal selected from b, Er, Sb, Tl, Mn and Sn. Y is a number satisfying 0 ≦ y ≦ 2. A specific example is described in JP-A-59-38278.

[19] nReX_Three・ MAX '_Three: With xEu
A stimulable phosphor represented by the formula (where Re is a small number selected from La, Gd, Y and Lu).
X and X 'are F, Cl, Br and I
Wherein A is from Ba, Sc and Ca
At least one alkaline earth metal selected, x
Is 1 × 10^-Four<X <3 × 10^-1Indicates a number that satisfies n
And m are 1 × 10^-3<N / m <7 × 10 ^-1Number that satisfies
Is shown. A specific example is described in JP-A-59-155487.
It is listed.

[20] nReX ₃ · MAX ' ₃ : xEu,
Stimulable phosphor represented by ySm (where Re is at least one selected from La, Gd, Y and Lu, and X and X 'are F, Cl, Br and I
A is at least one alkaline earth metal selected from Ba, Sc and Ca, and x
And y are 1 × 10 ⁻⁴ <x <3 × 10 ⁻¹ and 1 respectively.
The number satisfies × 10 ^-4 <y <1 × 10 ^-1 . n and m
Indicates a number satisfying 1 × 10 ⁻³ <n / m <7 × 10 ⁻¹ . A specific example is described in JP-A-59-155487.

[21] MX.aMX '_Two: Expressed by xEu
Stimulable phosphor (where M is at least selected from Ca, Sr and Ba)
Is also a divalent metal. X, X ' Are different from each other
It represents a halogen selected from Cl, Br and I. Also,
a is a number satisfying 0.1 ≦ a ≦ 10, and x is 1 × 10
^-Four≦ x ≦ 1 × 10 ^-2Is a number that satisfies Incidentally, a specific example is disclosed in Japanese Patent Application Laid-Open No. 60-84381.
It is described in JP-A-63-27588.

[22] Stimulable phosphor represented by Ba ₂ X: Eu (where X represents a halogen.) Specific examples are given in the proceedings of the 51st Annual Meeting of the Japan Society of Applied Physics ( 1990 Fall), p. 1086.

As the stimulable phosphor, the following stimulable phosphors are particularly preferred. [23] Rb (Br _x , I _1-x ): a stimulable phosphor represented by yTl (where x is a number satisfying 0 ≦ x ≦ 1, and y is 1 × 1)
It is a number that satisfies 0 ⁻⁶ ≦ y ≦ 1 × 10 ⁻² . [24] BaF (Br _x , I _1-x ): a stimulable phosphor represented by yEu (where x is a number satisfying 0 ≦ x ≦ 1, and y is 1 × 1)
It is a number that satisfies 0 ⁻⁴ ≦ y ≦ 1 × 10 ⁻² . As a radiation detector in which a plurality of pixels are arranged two-dimensionally, a radiation detector having a configuration disclosed in Japanese Patent Application Laid-Open No. 6-342098 is used. This detector uses amorphous selenium,
Using a photoconductive layer such as lead oxide or cadmium sulfide, electron-hole pairs corresponding to the intensity of the irradiated radiation are generated, and two-dimensionally arranged on a dielectric substrate such as glass. The generated charges are read out and accumulated by a large number of microplates using thin films, and image data is generated based on the accumulated charge amount.

The radiation image conversion plate 12 is a cassette 9
A pair of locking pins 905 fixed to an inner rigid tray 904 and corresponding to portions other than the area where an image is recorded.
Is provided on the tray 904, and the pair of locking pins 905
Penetrates the tray 904 of the radiation image conversion plate 12. A guide plate 9 is attached to the pair of locking pins 905.
A guide hole 906 a is provided so as to be slidable, and a cap 907 that covers the opening is attached to the guide plate 906.

A lock mechanism 908 is built in the cap 907, and the lock of the lock mechanism 908 can be released from the lock hole 909. Also, the cap 907 has
A pair of levers 910 are provided.
0, the cap 907 is opened and closed, and the radiation image conversion plate 12 together with the tray 904 is pulled out from the cassette 9 or stored.

Table 1 shows an example of the type of the cassette 9 and the cassette size.

[0060]

[Table 1]

An identification sticker 9 is provided on the back surface of the cassette 9.
11 is affixed, and identification information in white and black is recorded on the identification sticker 911.
By detecting the identification information, the type and size of the cassette 9 and the erroneous insertion into the cassette stacker unit 3 are detected.

Further, the identification direction of the cassette 9 and the front and back sides are determined by the identification seal 911. The vertical direction mark 912 is a mark that indicates the direction in which the cassette 9 is inserted into the cassette stacker unit 3.
The insertion direction may be specified by inserting the cassette 9 into the cassette stacker unit 3 with 07 as the lower side.

On the back surface of the cassette 9, a medical record clip 913 is provided on the case half 900, and around the medical record clip 913, a concave portion 900 a is formed in the case half 900. The medical record and the like are held by the medical record clip 913.

The schematic configuration of the cassette 9 has been described above. Next, referring to FIGS. 1 and 2, marks for divided photographing of the cassette 9 will be described. As shown in FIGS. 1 and 2, the front surface of the cassette 9 (the surface of the case half 901:
On the (X-ray irradiation surface), a division photographing mark 920 that divides the front surface into four is recorded. That is,
A divisional imaging mark 920 is recorded at a position where the radiation image conversion plate 12 accommodated in the cassette 9 is divided into four parts. Note that the divisional imaging mark 920 is made of a paint or the like that has a small X-ray absorption and does not hinder X-ray imaging.

When performing divided photographing, a shielding plate 1000 is placed on the cassette 9 as shown in FIG. 1 on the front surface of the cassette 9 shown in FIG. In this case, by placing the shielding plate 1000 in alignment with the divisional photographing mark 920, the divisional photographing can be performed at an accurate divisional photographing position at the time of the divisional photographing. Although FIG. 1 shows a case of two divisions, in the case of four divisions, division photographing is performed so that a の region is covered with a shielding plate 1000.

It is to be noted that an “L” -shaped symbol shown in FIG.
Various modifications are conceivable other than the symmetrical divided photographing mark 920 indicating four sections in combination. Here, various modified examples of the divided photographing mark 920 on the surface of the case half 901 are shown in FIG.

That is, a mark indicating the division itself for divisional photographing (FIG. 11)
(A)), a combination of "L" shaped marks at the center (FIG. 11)
(B)),-A mark with a "+" mark at the center and a "-" mark at the periphery (FIG. 11C).
(D)).

In addition to indicating the sections to be divided and photographed, the order of the divided photographing can be indicated.
In other words, if the starting section is known in the case of four divisions and three shootings,
Divided shooting becomes easy. In this case, the mark is asymmetric.

That is, a mark which is obtained by changing the color or density in the order of photographing for the section to be divided and photographed (FIG. 11 (e)); combining an "L" -shaped mark at the center; Marks with different colors, densities, and thicknesses (Fig. 11 (f)).-A "+" mark is added at the center, and a "-" mark is displayed at the periphery by changing the color, density, and thickness in the order of photographing. (See FIG. 11)
(G)), a section in which a section to be divided and photographed is divided by a mark in which the color, density, and thickness are changed in the photographing order (FIG. 11 (h)).

By using such a divisional photographing mark, when performing four-partitioning and three-part photographing, it is possible to clarify a place where one to three photographing is performed and a place where no photographing is performed, and as shown in FIG. When placing the plate 1000, no error occurs. That is, it is possible to perform divisional photographing at an accurate divisional photographing position, and to fix a photographing section in the case of multi-division.

FIG. 12 is a perspective view showing another example of the configuration of the cassette 9 suitable for divided photographing. FIG. 12 shows a case half 901 composed of an X-ray shielding member.
It is characterized by having a shielding plate 1101 configured to cover a part of the X-ray irradiation surface (a section not to be photographed) so as to be movable on the (X-ray irradiation surface).

It should be noted that in FIG.
However, if the shielding plate 1101 has a size suitable for divided photographing (for example, half the size of the entire area), it is not necessary to provide the divided photographing mark 920.

FIG. 13A is a right side view of FIG. As described above, the shielding plate 1101 is slidably arranged on the X-ray irradiation surface. When reading, the shield plate 1101 can be removed.

The light shielding plate 1101 is made of a composite material of a metal such as lead, tungsten, antimony or the like or a multi-metal, or a material obtained by coating them with plastic, synthetic rubber, cloth or the like, and has a radiation shielding ability of 0.1 to 0.1. 2.
Desirably, it is 0 mmPb (lead equivalent). The same applies to the following embodiments.

FIG. 14 is a perspective view showing still another example of the configuration of the cassette 9 suitable for divided photographing. This FIG.
Is composed of an X-ray shielding member, and the case half 9
01 (X-ray irradiation surface), and has a double shielding plate 1110 so as to cover a part of the X-ray irradiation surface (a section not photographed) while being movable on the X-ray irradiation surface.

Here, a first shielding portion 1111 for shielding one-half of the entirety, a second shielding portion 1112 for shielding one-fourth of the entirety, and a one-fourth of the entirety are shielded. A shielding plate 1110 is configured by the third shielding portion 1113.

FIG. 13B is a right side view of FIG. In this way, each of the first shielding portion 1111 to the third shielding portion 1113 is slidably arranged on the X-ray irradiation surface. At the time of reading, this shielding plate 1110
It is possible to remove the whole at once.

It is also possible to use a folded shield plate 1120 in place of the movable shield plate as described above. That is, the perspective view of FIG.
As shown in the side view of FIG. 6, the shielding plate 1120 is configured to alternately shield the two sections by the shaft 1123 supported by the pressing members 1121 and 1122 so as to be along the division line of the division photographing.

By sliding or folding as described above, the shielding means is configured to cover a part of the X-ray irradiation surface while being movable on the X-ray irradiation surface of the case. In this case, it is possible to accurately move the shielding member, and it is possible to perform divided photographing at a fixed divided photographing position.

Further, when the above-mentioned shielding member is provided, by using a mark indicating a photographing section and a photographing order together, the usability in divided photographing is further improved. <2. Schematic Configuration of Radiation Image Recording / Reading Apparatus> Here, a schematic configuration of the radiation image recording / reading apparatus for reading the cassette 9 of the present embodiment will be described.

FIG. 17 is a perspective view of the radiation image recording / reading apparatus in a state where the cassette 9 is being set, FIG. 18 is a front view of the radiation image recording / reading apparatus in a state where a plurality of cassettes 9 are set, and FIG. 18 is a left side view,
FIG. 20 is a right side view of the radiation image recording and reading apparatus in FIG.

The cassette stacker unit 3 and the display / operation unit 7
Are arranged side by side in a substantially horizontal direction above the radiation image recording and reading apparatus. That is, the cassette stacker unit 3 is disposed on the right side of the upper part of the radiation image recording and reading apparatus 1,
The display / operation unit 7 is disposed on the left side when viewed from above the radiation image recording and reading apparatus.

The cassette stacker section 3 has a loading section 300 provided for every five slots. The display / operation unit 7 includes a CRT display unit 70 as a display unit and a CRT
A touch panel 71 as an operation unit provided on the display surface of the display unit 70 is provided. Operation such as examination reservation and patient registration, status display / setting of each unit of the apparatus, and read images are displayed on the CRT display unit 70. Is displayed.

The CRT display unit 70 has, for example, a 15-inch C
An RT display device (24-bit color, monochrome 256 gradations, resolution 1024 × 768) is used, and an operation input is performed on a CRT display unit 7.
This is performed by the touch panel 71 on the “0”.

The touch panel 71 of the present embodiment is
A light system that reacts by blocking light, for example, infrared light, was used. The input section 300 includes an input guide section 301 and a storage section 302. The insertion guide portion 301 extends in a groove shape toward the storage portion 302, and is formed so as to guide the cassette 9 to the storage portion 302 in a vertical state. The cassette 9 is stored and held in the storage section 302 with a predetermined gap.

[0086] The cassette 9 is vertically inserted with the cassette long side being horizontal, with the front side of the apparatus as a reference.
At the same time as the cassette 9 is inserted, the light-blocking shutter 303 provided at the opening of the storage section 302 is closed for each slot to prevent light leakage from the opening.

The cassette 9 can be removed from each slot, and an LED lamp 304 is provided to indicate that the cassette 9 is being read so that the cassette 9 is not accidentally removed.
FIG. 1 is a schematic block diagram showing a schematic configuration of a radiation image recording and reading apparatus.

The apparatus main body 2 of the radiation image recording / reading apparatus 1 is provided with a cassette stacker section 3, a plate transport section 4, an image reading section 5, a system control section 6, a display / operation section 7, and a power supply section 8. .

A cassette 9 accommodating radiation image conversion plates as a plurality of types of media can be set in the cassette stacker unit 3, and the cassette 9 accommodating the radiation image conversion plate is loaded into the cassette stacker unit 3. . When a predetermined operation is performed from the display / operation unit 7, the radiation image conversion plate 12 is pulled out from the cassette 9 by the plate transport unit 4.

The extracted radiation image conversion plate 12
Is transported by the plate transport unit 4 toward the image reading unit. In the image reading section 5, the radiation image conversion plate 1
2 is fixed, and reading by laser scanning is started. Radiation image conversion plate 1 that has been read by image reading unit 5
2 is stored in the original cassette 9 following the same route. The erasing operation of the image on the radiation image conversion plate 12 is performed by the erasing unit 13 when the image is stored in the cassette 9. That is, the radiation image conversion plate 12 is stored in the cassette 9 of the cassette stacker unit 3 while erasing the image.

Next, an outline of control of the radiation image recording and reading apparatus 1 will be described. FIG. 22 is a control block diagram of the radiation image recording and reading apparatus. The cassette stacker unit 3 provided in the apparatus main body 2 of the radiation image recording and reading apparatus 1 is provided with a cassette stacker unit mechanism / drive unit 30 and a cassette stacker unit control unit 31, and a cassette containing a plurality of types of radiation image conversion plates. 9 can be set. When the cassette stacker unit mechanism / drive unit 30 is driven based on the control of the cassette stacker unit control unit 31 and the cassette 9 containing the radiation image conversion plate is loaded,
Set to a predetermined state.

The plate transport section 4 is provided with a plate transport section mechanism / drive section 40 and a plate transport section control section 41. Based on a command from the cassette stacker section control section 31, the plate transport section control section 41 controls the plate transport section. The section mechanism / drive section 40 is controlled. Plate transport section mechanism / drive section 40
Pulls out the radiation image conversion plate 12 from the cassette 9 and conveys the extracted radiation image conversion plate 12 toward the image reading unit.

The image reading section 5 is provided with a sub-scanning section mechanism / drive section 50 and a main scanning section 51. The main scanning section 51 is transported in the sub-scanning direction by the sub-scanning section mechanism / drive section 50, and the main scanning is performed. The image reading by the laser scanning of the unit 51 is performed.

The system control unit 6 includes a main CPU 60
And a reading section control image input control section 61.
The main CPU 60 is connected to a system disk 62 storing a system program, image disks 63 and 64 storing image information, and is connected via a board 65 to a host computer 66, a diagnostic device 67 and a patient registration terminal 68. You. The main CPU 60 performs overall control, image processing, output control, and image management. The reading unit control image input control unit 61 controls the cassette stacker unit control unit 31, the sub-scanning unit mechanism / drive unit 50, and the main scanning unit 51 to perform image reading of the radiation image conversion plate 12,
This image information is sent to the main CPU 60.

The display / operation section 7 has a CRT display section 7 as a display section for displaying an image read by the image reading section 5.
0, and a touch panel 71 as an operation unit provided on the display screen of the CRT display unit 70. Command information from the touch panel 71 is sent to the main CPU 60, and the main CPU 60 performs control based on an input command. .

<3. System control unit> System control unit 6
Is provided with a main CPU 60 and a reading unit control image input control unit 61, and is configured as follows.

(1) System control unit The system control unit performs moire removal and various corrections. It is also used for image transfer with an image control board (ICU). X
GA-24bit color image display is possible.

As a hard disk, a system disk 62 storing a system program and image disks 63 and 64 storing image information are connected. Image data output can be switched between host computer output priority and hard copy priority by user setting.

(2) Image Processing The software of the system control unit sets the image processing conditions based on the analysis result of the image data, and performs image processing.

As this image signal, gradation processing for outputting an image with a density and contrast suitable for diagnosis is always performed stably regardless of the patient's body shape and irradiation dose. In addition, frequency processing for controlling the sharpness of the image, dynamic range compression processing for keeping the entire image in a density range in which the entire image can be easily viewed while maintaining the contrast of the fine structure, and the like are performed.

(2-1) Gradation Processing In gradation processing, a gradation conversion curve representing the correspondence between original image data (input) and gradation processed image data (output) based on the analysis result of image data. Is determined, and gradation conversion is performed using the harmful bird conversion curve. As a method of creating a gradation conversion curve, for example, based on histogram analysis of image data, Japanese Patent Application Laid-Open No. 55-116340,
-272529 and JP-A-63-262141 may be used. Further, as shown in JP-A-3-218578, a method of setting an image area corresponding to a desired portion of a subject and determining based on image data in the area may be used. The gradation conversion curve may be created each time for each image.
As shown in JP-A-9-83149, a desired gradation conversion curve may be obtained by modifying a reference curve selected from several kinds of reference curves created in advance.

If the irradiation field recognition processing for detecting the irradiation field area of the radiation is performed prior to the gradation conversion, various image processing conditions are set by using the image data in the recognized irradiation field area. This is preferable because image processing of an image portion required for diagnosis can be appropriately performed. As a method of this irradiation field recognition processing, for example,
No. 259538, JP-A-5-7579, and JP-A-7-181609 can be used.

(2-2) Frequency processing In the frequency processing, for example, a non-sharp mask processing shown in Japanese Patent Publication No. 62-62373 and Japanese Patent Publication No. 62-62376 and a method disclosed in Japanese Patent Application Laid-Open No. 9-44645 are disclosed. The sharpness of an image can be controlled by a technique such as a multi-resolution method.

(2-3) Dynamic Range Compression Processing In the dynamic range compression processing, for example,
The dynamic range of an arbitrary signal area can be compressed by using the technique described in Japanese Patent No. 66318.

In determining the image processing conditions for the above-described various types of image processing, instead of using the image data itself, the image data is executed on the thinned image data obtained by performing the thinning reduction processing on the image data. It is preferable to reduce the time.

In determining the image processing conditions for the above-described various types of image processing, it is assumed that the image processing conditions are determined not only based on the analysis results of the image data but also on the basis of the information relating to imaging, such as radiation irradiation conditions and imaging body position conditions. Is also good. If the information required here has been entered at the time of the appointment,
By using such information, it is possible to easily set the image processing conditions.

Further, the setting of the various image processing conditions may be performed based on information relating to the type of the image output device. (3) Image data storage The hard disks of the image disks 63 and 64 can be stored.

(4) Patient Registration As a patient input method, it is possible to input by a Japanese syllabary table displayed on the CRT display unit 70, and it is also possible to automatically input by an ID number. Furthermore, input is possible from the patient registration terminal.

According to the radiation image recording / reading apparatus having the above-described configuration, the operation / display section 7 and the cassette stacker section 3 are arranged in a substantially horizontal direction, so that the cassette 9 is set on the cassette stacker section 3. When confirming an image on the operation / display unit, the amount of movement of the line of sight can be reduced, so that operability is good.

The CRT display section 70 of the operation / display section 7
The touch panel 71 is provided on the display screen of the CRT display section 70, the operation of the apparatus can be performed on the display screen of the CRT display section 70, and the apparatus is operated after the cassette 9 is set on the cassette stacker section 3. In addition, since the amount of movement of the line of sight is small, the operability is good.

[0111]

As described above, in the cassette for X-ray imaging according to the present invention, since the mark for divisional imaging is provided on the X-ray irradiation surface of the case, the shielding member is accurately placed at the time of divisional imaging. It is possible to place the camera at the correct position, so that divided shooting can be performed at an accurate divided shooting position. Further, in the case of multi-division, it is possible to fix the shooting section.

In the cassette for radiography of the present invention,
Since a movable shielding member for divided imaging is provided on the X-ray irradiation surface of the case, the shielding member can be accurately placed at the time of divided imaging, and divided imaging can be performed at an accurate divided imaging position. . Further, in the case of multi-division, it is possible to fix the shooting section.

[Brief description of the drawings]

FIG. 1 is a perspective view showing a state of a cassette at the time of divided photographing.

FIG. 2 is a perspective view showing a state of an X-ray irradiation surface of the cassette.

FIG. 3 is a perspective view showing a state where a radiation image conversion plate is stored in a cassette.

FIG. 4 is a perspective view showing a state where a radiation image conversion plate is pulled out from a cassette.

FIG. 5 is a plan view of the cassette.

FIG. 6 is a plan view showing a state where a radiation image conversion plate is stored in a cassette.

FIG. 7 is a side view of the cassette.

FIG. 8 is a cross-sectional view taken along section line CC of FIG. 5;

FIG. 9 is a sectional view taken along section line DD in FIG. 5;

FIG. 10 is a sectional view taken along section line EE in FIG. 5;

FIG. 11 is an explanatory diagram showing an example of divisional imaging marks on the X-ray irradiation surface of the cassette.

FIG. 12 is a perspective view showing an example of a shielding plate of a cassette at the time of divided photographing.

FIG. 13 is a side view of FIG.

FIG. 14 is a perspective view illustrating an example of a shield plate of a cassette at the time of divided photographing.

FIG. 15 is a side view of FIG. 14;

FIG. 16 is a perspective view showing an example of a shield plate of a cassette at the time of divided photographing.

FIG. 17 is a perspective view of the radiation image recording and reading apparatus, showing a state where a cassette is not set.

FIG. 18 is a front view of the radiation image recording and reading apparatus in a state where a cassette is set.

FIG. 19 is a left side view in FIG. 18;

FIG. 20 is a right side view of the radiation image recording and reading apparatus in FIG. 18;

FIG. 21 is a diagram illustrating a schematic configuration of a radiation image recording and reading apparatus.

FIG. 22 is a control block diagram of the radiation image recording and reading apparatus.

[Explanation of symbols]

 9 Cassette 900 Case half (back surface) 901 Case half (front surface) 902 Screw 903 Opening 904 Tray 905 Locking pin 906 Guide plate 906a Guide hole 907 Cap 908 Lock mechanism 909 Lock hole 910 Lever 911 Identification seal 912 Instruction mark 913 medical record clip 920 divisional imaging mark 1000 shielding plate 1101 shielding plate 1110 shielding plate 1111 first shielding portion 1112 second shielding portion 1113 third shielding portion 1120 shielding plate

Claims (10)

[Claims] An X-ray imaging cassette having a case for accommodating a radiation image information recording medium, wherein a mark for divisional imaging is provided on an X-ray irradiation surface of the case. 2. A case for accommodating a radiation image information recording medium, and an X-ray shielding member. An X-ray imaging cassette comprising: a shielding unit configured to: 3. The cassette for X-ray imaging according to claim 2, wherein a mark for divisional imaging is provided on the X-ray irradiation surface of the case. 4. The cassette for X-ray imaging according to claim 1, wherein the divisional imaging mark indicates an imaging section at the time of divisional imaging. 5. The X-ray imaging cassette according to claim 1, wherein the divisional imaging mark indicates an imaging order in the divisional imaging. 6. The X-ray imaging cassette according to claim 1, wherein the divisional imaging mark is formed by a division line parallel to a case periphery. 7. The X-ray imaging apparatus according to claim 1, wherein the divisional imaging mark is asymmetrically formed by a division line parallel to a case edge. Cassette. 8. The mark for divided photographing is divided into a plurality of regions in accordance with the divided photographing, and a display corresponding to at least one region is different from a display corresponding to a remaining region. The cassette for X-ray imaging according to any one of claims 1 to 3, characterized in that: 9. The cassette for X-ray photography according to claim 1, wherein the radiation image information recording medium is a radiation image conversion plate having a stimulable phosphor. 10. The X-ray imaging apparatus according to claim 1, wherein the radiation image information recording medium is a radiation detector in which a plurality of pixels are two-dimensionally arranged. Cassette.