JPS61234651A - Device for reading radiographic image information - Google Patents

Abstract

PURPOSE:To miniaturize a radiographic image information reading device and to improve its condensing and transmitting efficiency of accelerated phosphorescent light, by reading the accelerated phosphorescent light which are excited by accelerated exciting light with an optical fiber bundle composed of optical fibers of >=0.3 apertures. CONSTITUTION:An optical beam 23 from a laser 14 which is an accelerated exciting light source are irradiated in the main scanning direction Z of a conversion panel 11 while it is deflected by an optical deflector 20. Since the panel 11 is equipped with an accelerated phosphor layer, on which radiographic image information is recorded, the panel is acceleratedly caused to emit light. The light is led to a photoelectric converter 13 through a light condensing and transmitting body 12 consisting of a optical fiber bundle composed of optical fibers of >=0.3 apertures. Then the panel 11 is shifted in the auxiliary scanning direction Y and the image information on the panel 11 is read. When such constitution is used, the light condensing and transmitting body 12 can be fabricated to a suitable form and the device can be miniaturized and, at the same time, the light condensing and transmitting efficiency can be improved.

Description

Detailed Description of the Invention (Industrial Application Field) The present invention provides a radiation image conversion panel (hereinafter abbreviated as a conversion panel) having a photostimulable phosphor layer that is stimulated with t-stimulation excitation light. , relates to radiation image information reading, in which radiation image information recorded on the conversion panel is read by detecting stimulated luminescence from the conversion panel with a photoelectric converter. This will be related to light collection and transmission to efficiently guide stimulated luminescence from the panel to the photoelectric converter. ,(
Prior art) When exposed to high-energy radiation such as X-rays, a part of the energy is stored, and when visible light or heat is added to this, the stored energy is released in the form of fluorescence, so-called stimulable phosphors. be. A conversion panel is formed by uniformly forming such a material into a panel shape, and a radiographic image is recorded on this conversion panel.
-\Nuclear transmutation panel is stimulated with photostimulation excitation light such as a laser 1
~ The radiation image information recorded on the conversion panel can be read by detecting the emitted stimulated luminescence.

The radiation image information reading method is a method of reading the recorded information of this conversion panel, and as shown in FIG.
radiation (generally X-rays) that passes through the object 2.
is absorbed into the conversion panel 1, and then the conversion panel on which this radiation image is recorded is stimulated 17 with a photostimulation excitation light beam to radiate the radiation energy accumulated in the photostimulable phosphor. 1. Emit stimulated luminescence and obtain radiographic image information by detecting this stimulated luminescence. It is something that Figures 16 to 8 are diagrams showing examples of conventional methods and devices of this type. FIG. 6 shows that the stimulated excitation light beam emitted from the stimulated excitation light source 64 passes through the entire dichroic filter 65 and is irradiated onto the conversion panel 11 I2, and the stimulated luminescence emitted at that time is received by the dichroic filter 65. After the reflected light is focused by a lens 61, only the fluorescent component (stimulated luminescence) is extracted by a filter 62, and image information is detected as an electrical signal by a photoelectric converter 63. (For example, US Pat. No. 3,859,527). Such methods and devices have the following disadvantages.

(2) The photostimulation excitation light beam is attenuated by the dichroic ink filter 65.

■ Since stimulated luminescence emits light in a diffuse manner, the reflection efficiency at the dichroic filter section is considerably reduced.

■ When trying to scan the photostimulation excitation light beam over the entire width of the conversion panel 11, the lens 61° filter 62
and that the dimensions of the photoelectric converter 630 become larger in the scanning direction.

■ It is not possible to obtain a large acceptance solid angle for stimulated luminescence.

FIG. 7 shows a photostimulation excitation light beam emitted from a photostimulation excitation light source (not shown), which is received by all the mirrors 71, and the reflected light is reflected by a conversion panel 11 (the same parts as in FIG. 6 are given the same reference numerals. ．．
Shown. The same applies hereinafter), and the stimulated luminescence emitted at that time is guided to the photoelectric converter 6: through the filter 62, and the photoelectric converter 63 detects the image information as an electric signal L2. Yes. This method and apparatus have the following 1';

■ Because of the mirror 71, the component near the normal direction of the conversion panel 11, which has the strongest stimulated luminescence, cannot be used in the image signal 17 (the component near the normal direction cannot be used by the mirror 71).
(The photoelectric converter 63 cannot be reached because it is blocked by the

(2) When attempting to scan the stimulated excitation light beam '17, it is necessary to use filters 62 and photoelectric converters 63 with similar dimensions in the scanning direction.

□ In Figure 8, the photostimulation excitation light beam emitted from the photostimulation excitation light source 64 is taken from directly above in the main scanning direction using a deflector 82.
Conversion panel IIK irradiation 1-1 The stimulated luminescence emitted at that time is guided to a photoelectric converter 63 by a sheet-like photoconductor 81 made of a light-guiding sheet material (for example, as described in
No. 5-87970). Such a sheet-like original conductor 81
By using ▲, it is possible to increase the detection efficiency when scanning the light beam.

However, this method and device have the following drawbacks.

■ It is extremely difficult to fully process one end of the sheet material to match the shape of the photoelectric converter.

Example: When processing an evaporated polymethyl methacrylate plate using heat, bubbles, scratches, etc. are likely to occur in the resin plate.

■ As mentioned above, processing of the sheet material is difficult, so the area of the light-receiving surface of the photoelectric converter becomes large □, which not only makes the photoelectric converter expensive, but also deteriorates the uniformity of the light-receiving surface, resulting in poor radiographic images. When reading information, shading increases and image deterioration occurs.

■ Sheet-shaped photoconductor is photoconductive due to stimulated luminescence □
When light enters from a certain point on the body's light-converging surface, it exits from a localized point on the transmission surface, so the light receiving surface of the photoelectric converter □
Immediately after being affected by niformity, seeding becomes large when reading radiographic image information, resulting in significant image deterioration.

■ Since the sheet-shaped photoconductor is not flexible, fine adjustment of the installation position is difficult, and a large installation space is required, resulting in an increase in the size of the device.

(Objective of the Invention) Based on the previous situation, the object of the present invention is to read radiation image information: (1) High light collection efficiency of stimulated luminescence < improved S/N ratio (2) The reading device with small shading using a charging converter with a small light receiving surface with good uniformity, (3)
It is an object of the present invention to provide an entire reading device that can be miniaturized.

(Structure of the Invention) In a radiation image information reading device that reads radiation image information recorded on a radiation image conversion panel having a photostimulable phosphor layer using a light collecting and transmitting means VC, the light collecting and transmitting means has a numerical aperture of 0. This is achieved by the radiation image information reading device tK, which is characterized in that it is composed of an original fiber bundle made up of three or more original fibers.

The present invention also provides that the numerical aperture of the optical fibers forming the original fiber bundle used in the light condensing/transmitting means is 0.35 or more, that the original fibers are plastic optical fibers, and that the optical fiber bundle is condensed. A light surface is provided along the stimulated excitation light scanning line on the conversion panel surface, and a transmission surface of the optical fiber bundle facing the light receiving surface of the photoelectric converter is formed to match the shape of the light receiving surface. A preferred embodiment is provided by arranging the shape so that it is adjacent to the .

Hereinafter, the present invention will be described in detail with reference to the drawings.

FIG. 1 is a perspective view showing an embodiment of a radiation image information reading device using a photoelectric converter having a circular light-receiving surface.

In the figure, IO is a movable table capable of linear movement on a plane, and a conversion panel 11 is attached to the surface of the movable table 10. A light collecting and transmitting means filter surface 12m, which is a light collecting and transmitting means, is arranged close to the conversion panel 11, and the transmitting surface 12b of the light collecting and transmitting body 12 separates stimulated excitation light and stimulated luminescence. The other surface of the filter n is placed in close contact with the light receiving surface of the photoelectric converter 13. A light beam 23Fi that is photostimulation excitation light,
It is repeatedly swung in the main scanning direction (two directions in the figure) K by the addition of an optical deflector.

The operation of the device configured as described above will be explained as follows.

A light beam n from a laser 14, which is a stimulated excitation light source, is irradiated in the main scanning direction while being deflected by an optical deflector. The flexible panel 11 irradiated with the light beam emits stimulated light. This stimulated luminescence is guided to a photoelectric converter 13 by a condenser/transmitter 12. In this case, the condensing surface 12m is installed close to the conversion spring 11 with the scanning line of the light beam B as the center. The stimulated luminescence incident on the photoelectric converter 13 is photoelectrically converted and then subjected to image processing and image reconstruction in a processing device (not shown).

A photomultiplier tube is suitable as the photoelectric converter 13 because it detects weak stimulated luminescence.

Next, details of the light condensing/transmitting body 12 are shown in FIG. 2. The condensing surface 12&, which is one end surface, is linear and is made to match the shape of the transmission surface 12bij, which is the other end surface, and the photoelectric converter 13. 121 is an optical fiber bundle, 122-9
= A base for forming and holding the condensing surface of the optical fiber bundle in a linear shape, 123 a base for forming and holding the optical fiber bundle in the shape of the light receiving surface of the photoelectric converter, and 124 an optical fiber bundle. This is a cover such as cloth that protects the 121.

Figure 3(a) shows a partially enlarged view of the Fi condensing surface 12m,
FIG. 3(b) shows an enlarged view of the transmission surface 12b. In the figure, each 1211J Fi optical fiber bundle 121 is the original fiber wire, and 1211J is arranged in a close-packed manner to reduce loss when concentrating stimulated luminescence, and also to improve photoelectronization. This is preferable because the light receiving surface of the converter 13 is also small.

The optical fiber according to the present invention can be any type of optical fiber, such as a step index type or a graded index type used for optical communication, but the stimulated luminescence is close to completely diffused light, and the light condensing and transmitting body The light-receiving solid angle of the light-converging surface 12m is required to be large.

Generally, the solid angle of reception of an optical fiber is determined by the numerical aperture of 4, and it is practical if the numerical aperture is 0.3 or more.

1 to 0.035 or more in the present invention, more preferably 0.4 or more.

Note that the numerical aperture (NA) and the solid angle of light reception (θ) are given by the following equations, assuming that the refractive indexes of the core material and sheath material constituting the optical fiber are nl and n2, respectively.

NA=L[厘[θ=28in″-' (NA) =28in-' (m
) Therefore, the material and structure of the original fiber according to the present invention can be applied to the present invention as long as it satisfies the numerical aperture described above.

Light guiding plastics are materials that provide optical fibers with large numerical apertures, including polyacrylic resin, polystyrene resin, soft vinyl chloride resin, vinylidene chloride resin, transparent polyamide resin, polycarbonate resin, polyester resin, epoxy resin, fluororesin, polyethylene resin etc., and are used in combination with resins for the core material and sheath material based on nl and n.

Plastic optical fibers also have the advantage of being inexpensive and easy to process.

Examples of optical fibers with large numerical apertures other than the plastic optical fibers include composite optical fibers made of the light-guiding plastic and quartz glass, multicomponent quartz optical fibers made of multicomponent quartz glass, and the like.

In the present invention, the larger the ratio (φ1/φ) of the outer diameter φ1 of the core material of the optical fiber to the outer diameter φ of the sheath material, the greater the incident loss of stimulated luminescence at the light collecting surface of the light collecting/transmitting body. A decrease of 1-1 is preferable because the light collection efficiency is improved. φl/φ, is φ1/φ, ≧0
．． If it is 64, there is no practical problem, and φI/φ Mayuzushi ≧0.7
If so, it would be even more preferable.

The diameter φ2 of the optical fiber (equal to the outer diameter of the sheath material) is 0.05 to 4 mm, preferably 0.1 to 211 m, and the diameter of the optical fiber is the same as that of the light collecting/transmitting body. It is preferable that the surface thickness d is 0.4 or less.

In addition, when photostimulating excitation with light energy in the method of the present invention, it is necessary to separate the reflected light of the photostimulable excitation light from the stimulated luminescence emitted from the photostimulable phosphor layer, and A photoelectric converter that receives stimulated luminescence emitted from a phosphor layer generally has a high sensitivity to original energy with a short wavelength of 600 nm or less. It is desirable for stimulated luminescence to have a spectral distribution in the short wavelength region as much as possible.1. (□, 300nm~50
A photostimulable phosphor having a photostimulated emission wavelength range of 0 nm is generally used. In order to efficiently transmit the stimulated luminescence from such a stimulable fluorophore, it is necessary to reduce the transmission loss of the light 27' fiber in the range of 300nrh to 500nm. It can be used if the transmission loss is 28 dB/m or less at the maximum wavelength of the stimulated emission spectrum of the body. Preferably, it is below 11) dB/m.

The radiation image information reading device of the present invention is not limited to the embodiment shown in FIG. 1, and may be a device based on the method shown in FIG. 4. It may be based on

In the present invention, a photostimulable phosphor is one that is irradiated with an initial source or high-energy radiation and then subjected to intensive (-excitation) optical, thermal, mechanical, chemical, electrical, etc.
It is a phosphor that exhibits stimulated luminescence by more than a firefly which exhibits l-9 photostimulated luminescence corresponding to the irradiation amount of the first light or high-energy radiation. As the photostimulable phosphor used in the conversion panel according to the present invention, for example, JP-A No. 48-8
Ba8'04 described in No. 0487: Ax
(However, A is at least one of Dy, Tb, 1 and Tm, and X is 0.001≦・<1 mol%.) Mg80n:Ax (However, A#iH.

or 1jDy, and 0.001≦X≦
1□ E! described in No. 80489! rsO4:AX
(However, A is at least one of Dy, 'rb, and Tm, and X is 0.001≦x (1 mol%). ni□
The listed Na, so4. Ca804, and B
A phosphor obtained by adding at least one of Mn, Dy, and Tb to aSO4, etc., 'Boo', LIF, h(gso4) described in JP-A No. 52-30487
and fluorophores such as CaF,! Fluorescent material such as Li1B40□: Cu a Ag described in JP-A No. 53-39277, LIIO・(ntO,) x : Cu (where x
u 2 (x≦3), and Ll, 08 (B20.)X
: Cu l Ag (However, L x V; j: 2 (x
≦3), etc., as described in U.S. Pat.
srs: Eu, Sm XLa1OIS: E
Examples include phosphors represented by u*Sm and (Zn,Cd)S:Mn,X (where X is halogen). ZnS published in Japanese Patent Application Publication No. 55-12142
: Cu + Pb phosphor, general formula is BaOe xA
J20. :El" (however, 1,08≦X≦10), and a barium aluminate phosphor represented by the general formula MO-x
SiO□:A (However, Mrj: Mg, Ca+8r+Zn
, Cd or Ba, and A is Ce, Tb l E
u l Tnl l Pb l T71 Bi and Mn
at least one pond among them, and xtiO,5≦x〈25
It is. ) are alkaline earth metal silicate-based phosphors. Moreover, the general formula is (Ba1-X -yMgxcay) FX : aE
u″+ (However, X is at least one of Br and Cl
, and X, y and e are each 0 (x+y≦06,
! 7 me0 and 10-6≦8≦5 % formula %: (Ln represents at least one of La, Y, Qd and Lu, xFicz and/or Brk, A represents Co and/or Tbi, x tti O< x (represents a number satisfying 0, 1) ), Japanese Patent Application Laid-Open No. 1983
The general formula described in No.-12145 is (Ba1-xMMx) FX: yA (where Ml is MgrCmlSrrZn and cd), and X is CI, Br, and I. At least one of them k, A is Eu, Tb, Ce, Tm,
At least one of Dy+Pr, HotNd, Yb, and Er'kz x and y represent numbers that satisfy the conditions 0≦X≦0.6 and O≦y≦0.2. ), the general formula of which is described in JP-A-55-84389 is BaFX:xCe.

yA (provided that at least one of 2, X Fi, CI, Br and I, A is at least one of In, Tj?, Gd, sm and Zr, ear and y are each 0 (x ≦2X10-1 and 0 < y≦5X10-
It is 1. ), Japanese Patent Application Laid-Open No. 55-160
The general formula described in No. 078 is MFX @xA: yLn (However, LM"l'l Mg, Car Ba, S
At least one of r, Zn and Cd, A is B
eO, MgO, CaO, SrO, BaO, ZnO.

AA'103 r Y*Oa, La10m y In
got + 8102 t Tjol r Zr01
+G50i lS n01 + Nb z Os r
At least one of T at Oa and The;
LnViEu+Tb, Ce, Tm, Dy, Pr, Ho,
Nd, Yb+Er.

8m and Gd, and X is (J
.

At least one of Br and I, and X and y are 5X10-5≦X≦0.5 and 0<y≦0, respectively.
．． This is a number that satisfies the condition of 2. ) rare earth element-activated divalent metal fluorohalide phosphor, whose general formula is Z
nS: A, CdS: A (Zn, Cd) S
: A, ZnS: A, X and Cd8: A,
Any of the following general formula % formula % described in No. 48285: (wherein M and N are respectively Mg*CII, S
r r Ba l At least one of Zn and Cd, Xl, F, Cj? , Br and I, A is Eu, 'rb l Ce + Tm + Dy,
It represents at least one of Pr, HQINdlYb, ErlSblTJIMn, and Sn. Further, X and y are numbers that satisfy the condition O<X≦6.0≦y≦1. )
A phosphor represented by one of the following general formula % formula %: (where Re is at least one of La, Gd, Y + Lu, human is an alkaline earth metal, Ba + Sr, C
at least one of a, X and X'FiF, C1
, Br. -1, X and y are I XIO-' (x (3X10-',
lXl0-' (y (lXl0-' is a number that satisfies the condition, n / m is I
(satisfies the condition 7XIO'), and the following general formula % formula % (where M is Ll, Na, K, Rh and C1
at least one alkali metal selected from 1;
M″l is Be I Mg +Ca, Sr r Ba
, Zn, Cd, Cu and N1. Ml is 8c, Y, L
a.Ce.

Pr, Nd+Pm, Sm, Eu, Gd, Tb, Dy, H
o, Er+Tm, Yb+Lu+1! , Ga, and In. x,
x' and Xl'ViF + C1+ B r and at least one halogen selected from ■. A is Eu,
Tb, Ce, Tm+Dy, Pr+Ho+Nd, Yb+E
r+Gd+Lu, Sm.

At least one metal selected from Y, TI, Na, Ag, Cu, and Mg. Further, a is a numerical value in the range of 0≦a<05, bt is a numerical value in the range of O≦b<05, and C is an alkali halide represented by 0 (a numerical value in the range of a≦02). Examples include fluorescent materials.

However, the photostimulable phosphor used in the conversion panel according to the present invention is not limited to the above-mentioned phosphor. Any phosphor that exhibits stimulated luminescence may be used.

The stimulated excitation light source 14 and L- used in the method of the present invention are light sources that include the stimulated excitation wavelength of the photostimulable phosphor used in the conversion panel 11. In particular, when a laser beam is used, the optical system becomes simple, the intensity of the stimulated excitation light can be increased, and the directivity is large, so the stimulated luminescence efficiency can be increased, and more favorable results can be obtained. Lasers include He-N laser, Ha-Cd laser, Ar ion laser, Kr ion laser, N, laser, YAG laser and its second harmonic, ruby laser, semiconductor laser, various dye lasers, copper vapor laser. There are metal vapor lasers such as Usually, a continuous oscillation laser such as a He-Ne laser or a semiconductor laser is desirable, but a pulse oscillation laser can also be used if all the pulses are synchronized with the scanning time of one pixel on the panel. In addition, when using the separation method using the delay in light emission shown in JP-A-59-22046 without using a filter, it is better to use a pulse oscillation laser than to modulate using a continuous oscillation laser. preferable.

Among the various laser light sources mentioned above, semiconductor lasers are particularly preferred because they are small and inexpensive, and do not require a modulator.
- Yes.

(Example) Next, the present invention will be explained using examples.

Example 1 X-ray gold with tube voltage of 80 kVp for radiation image conversion panel]
(After 1 mR irradiation, the panel was attached to the radiation image information reading device of the present invention shown in FIG. 1, and the radiation image information recorded on the conversion panel was read.

The light condensing/transmitting body of the radiographic image information reading device was made by bundling plastic optical fibers (Super Esca SK-20 manufactured by Mitsubishi Rayon Co., Ltd.) whose outer diameter of the sheath material was 0.5 mm.
It's 7. Note that the numerical aperture of the optical fiber was 0.5. It was a rectangular wing with a shape of 1140011% and a thickness of Sm, and the shape of the transmission surface was a circle with an outer diameter of 5111I+.

In the photoelectric converter and 1-7 of the radiation image information reading device, a 3-inch head-on type photoelectronic cell multiplier was used in all cases, taking into account the shape of the transmission surface of the light collecting and transmitting body.

The read radiation image information is converted into an image by an image reproducing device. Reproduction 1-1 was recorded on a silver salt film.

The light collection and transmission efficiency α of stimulated luminescence of the light collection and transmission body was determined according to the magnitude of the signal and is shown in Table 1. In addition, the magnitude of shading was determined using the reproduced image recorded on the silver halide film and is also listed in Table 1.

In Table 1, the light collection/transmission efficiency α is the light collection/transmission efficiency of this example.
Assuming the transmitting body 100, the relative values are I~.

The shading is (small, medium, dog) each (○
, △, ×).

Example 2 The light condensing/transmitting body of the radiation image information reading device of Example 1 was
A plastic optical fiber (S-Riki Extra EK-20 manufactured by Mitsubishi Rayon Co., Ltd.) with a sheath material having an outer diameter of 0.5 mm was bundled and radiographic image information was read in the same manner as in Example 1 except for the following. The numerical aperture of the optical fiber is 0.47.
Met.

The radiation image information was evaluated in the same manner as in Example 1, and the results are also listed in Table 1.

Example 3 The light condensing/transmitting body of the radiation image information reading device of Example 1 was
Radiographic image information was read at 1° in the same manner as in Example 1, except that plastic optical fibers (Super Esca 5K-40, manufactured by Mitsubishi Rayon Co., Ltd.) whose outer diameter of the sheath material was about 1.0 were bundled.

The radiation image information was evaluated in the same manner as in Example 1, and the results are also listed in Table 1.

Example 4 The light condensing and transmitting body of the radiation image information reading device of Example 1 was
Radiographic image information was read in the same manner as in Example 1, except that quartz glass/plastic composite optical fibers having a sheath material with an outer diameter of 0.5 i+m and a core material with an outer diameter of 0.4 cm were bundled. The numerical aperture of the optical fiber was 0.39.

The radiation image information was evaluated as 1- in the same manner as in Example 1,
The results are also listed in Table 1.

Example 5 The light condensing and transmitting body of the radiation image information reading device of Example 1 was
Multi-component quartz optical fiber with outer diameter of sheath material of 0.5 mg and outer diameter of core material of 0.4 yxm (large diameter high NA fiber manufactured by Showa Cable and Wire Co., Ltd.) f: Same as Example 1 except that it was created by bundling. Radiographic image information was read in the same manner.

The numerical aperture of the optical fiber was 1jo, 5.

The radiation image information was evaluated in the same manner as in Example 1.
The results are also listed in Table 1.

Comparative Example 1 One end of a light-guiding plastic sheet (acrylic resin) with a thickness of 511%, a width of 400mm, and a length of 700mm was heat-processed to form a diameter In consideration of the fact that the photoelectric converter of the radiation image information reading device had a cylindrical shape of 120 mm, and the shape of the transmission surface of the condensing fist transmission body, a 5-inch head-on type photomultiplier tube was used. Radiographic image information was read in the same manner as in Example 1 except for this.

The radiation image information was evaluated in the same manner as in Example 1, and the results are also listed in Table 1.

Table 1 As is clear from Table 1, the radiation I obtained in Examples 1 to 5 of the present invention! Compared to the radiographic image obtained in Comparative Example 1, the shading is significantly smaller and superior in terms of medical diagnosis.14. It was.

This is because although the light collecting/transmitting bodies used in Examples 1 to 5 of the present invention have a light collecting surface of the same size as the light collecting/transmitting body of Comparative Example 1, the outer diameter of the transmitting surface is is less than half the outer diameter of the transmission surface of 51u+ and Comparative Example 1, and the size of the light receiving surface of the photoelectric converter can be significantly reduced, so that shading caused by the uniformity of the light receiving surface can be reduced. It's for a reason.

In addition, since the light condensing/transmitting bodies used in Examples 1 to 5 are highly flexible, 11. It is possible to slightly move the positions of the light condensing surface and the transmission surface independently, which not only makes it easy to set the light condensing position of the light condensing surface, but also allows the light converging and transmitting body to be long enough to The distance of the transmission surface can be shortened, and the shape of the reading device can be made smaller. On the other hand, since the condensing Φ transmitting body of Comparative Example 1 is made by heating a rectangular plastic sheet, it is not only impossible to independently move the positions of the condensing surface and the transmitting surface. If an attempt is made to shorten the length of the light collecting and transmitting body, it will be difficult to heat the transmitting surface, and the reading device will become bulky and large.

Example 6 The light condensing/transmitting body of the radiation image information reading device of Example 1 was
The outer diameter of the sheath material is 0.511IL, the outer diameter of the core material is 0.4 stitches,
A radiation image information tube reading section was prepared in the same manner as in Example 1 except that quartz optical fibers having a numerical aperture of 0.3 were bundled together.

The radiation image information was evaluated in the same manner as in Example 1.
The results are shown in Table 2.

Example 7 The light condensing/transmitting body of the radiation image information reading device of Example 1 was
A radiographic image was obtained in the same manner as in Example 1, except that the outer diameter of the sheath material was 0.5 mm, the outer diameter of the core material was 0.4 m, 1h, and a bundle of quartz glass/plastic composite optical fibers with a numerical aperture of 0.35. I read the information.

The radiation image information was evaluated in the same manner as in Example 1, and the results are also listed in Table 2.

Example 8 Light condensing/transmitting body t1 of the radiation image information reading device of Example 1
A radiographic image was obtained in the same manner as in Example 1, except that silica glass/plastic composite optical fibers with a sheath material outer diameter of 0.5 mm, a core material outer diameter of 0.4 mm, and a numerical aperture of 0.41 were bundled. I read the information.

The radiation image information tit was evaluated in the same manner as in Example 1, and the results are also listed in Table 2.

Comparative Example 2 The light condensing and transmitting body of the radiation image information reading device of Example 1 was
Example 1 except that the outer diameter of the sheath material was 0.5iits, the outer diameter of the core material was 0.4B, and the quartz optical fibers (diamond guide manufactured by Dainichi Nippon Electric Cable Co., Ltd.) were bundled together and the numerical aperture was 0.2. Radiographic image information was read in the same manner as above.

The radiation image information was evaluated in the same manner as in Example 1,
The results are also listed in Table 2.

Table 2 From the results of Example 5 in Table 1 and Table 2, the radiation images obtained by the examples of the present invention have high light collection and transmission efficiency, small shading, and are excellent for medical diagnosis. Ta. However, since Example 6 FiNA was smaller than the other Examples, a decrease in light collection and transmission efficiency was observed.

Example 9 The light condensing/transmitting body of the radiation image information reading device of Example 1 was
1. Same as Example 1 except that the sheath material had an outer diameter of 05 silk, the core material had an outer diameter of 0.35 mm, and plastic optical fibers with a track number of 05 were bundled. The radiographic image information was read.

The radiation image information was evaluated in the same manner as in Example 1, and the results are shown in Table 3.

Example 1d The light condensing and transmitting body of the radiation image information reading device of Example 1 was
The outer diameter of the sheath material is 0.5II111, the outer diameter of the core material is 0.321
1. Same as Example 1 except that plastic optical fibers with 11% numerical aperture of 0.5 were bundled. I read all the radiation image information.

The radiation image information was evaluated in the same manner as in Example 1 [2,
The results are also listed in Table 3.

Table 3 From the results of Examples 1 and 5 in Table 1 and the radiation images obtained by the examples of the present invention in Table 3,
C2go;2', Ninii2=:2::・Transmission efficiency decreased.

Example 11 Light gathering/transmission body sound of the radiation image information reading device of Example 1,
A plastic optical fiber with an outer diameter of the sheath material of 2.511% and a numerical aperture of 0.5 (ESCA JK-1 manufactured by Mitsubishi Raykan Co., Ltd.)
Radiographic image information was read in the same manner as in Example 1, except that 00) was created by bundling.

The radiation image information was evaluated in the same manner as in Example 1 [7], and the results are shown in Table 4.

111 No (capital) - Table 4 Results of Examples 1 and 3 in Table 1 and Example 11 from Table 4
Compared to ij:d (7), since φ was large, seeding caused by the condensing surface pressure was observed.

(Effects of the Invention) By configuring the light collecting and transmitting body for stimulated luminescence using an original fiber as in the present invention, the light collecting and transmitting body [7] can be freely processed and molded into a convenient shape, the device can be miniaturized, The light collection efficiency and transmission efficiency of stimulated luminescence can be improved.

Furthermore, by using a plastic optical fiber as the original fiber and increasing the numerical aperture, the light collection efficiency can be further improved.

Furthermore, the light condensing/transmitting body according to the present invention is flexible, and the material and design constraints regarding the distance IHc between the light condensing surface and the transmitting surface are removed, and optical fibers and fibers are not tied together in a loose bundle. Alternatively, since it can be in the form of a cord, the installation of the device and the arrangement of parts can be changed freely, making it possible to provide an easy-to-use method and device.

Furthermore, in the light collecting/transmitting body according to the present invention, by downsizing the shape of the transmission surface, it is possible to downsize the light-receiving surface of the photoelectric converter, and it is possible to reduce shading caused by the uniformity of the light-receiving surface. .

[Brief explanation of drawings]

FIG. 1 is a schematic diagram of an embodiment of the apparatus of the present invention, and FIG. 2 is a perspective view showing an example of a light condensing/transmitting body according to the present invention. FIG. 3 is an enlarged view of the light collecting surface (FIG. 3(a)) and transmission surface (FIG. 3(b)) of the light collecting/transmitting body. Figures 4(a), (b), (e) and (d) are schematic diagrams of other embodiments of the invention. FIG. 5 is a diagram showing a radiographic image recording method, and FIGS. 6 to 8 are diagrams showing an outline of a conventional radiation image reading device. 10...Moving table, 11...Conversion panel, 12...
Original fiber condensing/transmitting body, 121L... condensing surface, 12
b...Transmission surface, 13.63...Photoelectric converter, 14.
64...Laser light source, Add...Light polarizer, Ru...
・Light beam. , -＼ Applicant Konishiroku Photo Industry Co., Ltd. Figure 2 20A-

Claims (4)

[Claims] (1) In a radiation image information reading device that reads radiation image information recorded on a radiation image conversion panel having a photostimulable phosphor layer using a light collecting/transmitting means, the light collecting/transmitting means has a numerical aperture of 0.3. A radiation image information reading device comprising an optical fiber bundle comprising the above optical fibers. (2) The numerical aperture of the optical fibers in the optical fiber bundle is 0.3
The radiation image information reading device according to claim 1, characterized in that the number is 5 or more. (3) The radiation image information reading device according to claim 1 or 2, wherein the optical fibers of the optical fiber bundle are plastic optical fibers. (4) One end of the optical fiber bundle is installed along the stimulated excitation light scanning line on the radiation image conversion panel, and the other end is formed to match the shape of the light receiving surface of the photoelectric converter, and the other end is formed to match the shape of the light receiving surface of the photoelectric converter. A radiation image information reading device according to any one of claims 1 to 3, characterized in that the radiation image information reading device is installed in a.