JPH09134795A - Small sized x-ray source - Google Patents
Small sized x-ray sourceInfo
- Publication number
- JPH09134795A JPH09134795A JP7314900A JP31490095A JPH09134795A JP H09134795 A JPH09134795 A JP H09134795A JP 7314900 A JP7314900 A JP 7314900A JP 31490095 A JP31490095 A JP 31490095A JP H09134795 A JPH09134795 A JP H09134795A
- Authority
- JP
- Japan
- Prior art keywords
- ray
- cup
- source
- electron
- small
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 239000000463 material Substances 0.000 claims abstract description 20
- 238000003780 insertion Methods 0.000 claims abstract description 17
- 230000037431 insertion Effects 0.000 claims abstract description 17
- 229910052790 beryllium Inorganic materials 0.000 claims abstract description 13
- ATBAMAFKBVZNFJ-UHFFFAOYSA-N beryllium atom Chemical compound [Be] ATBAMAFKBVZNFJ-UHFFFAOYSA-N 0.000 claims abstract description 13
- 238000010894 electron beam technology Methods 0.000 claims abstract description 11
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 claims abstract description 4
- 229910052782 aluminium Inorganic materials 0.000 claims abstract description 4
- 230000001133 acceleration Effects 0.000 claims description 14
- 239000012780 transparent material Substances 0.000 claims description 11
- 230000005855 radiation Effects 0.000 claims description 3
- 239000000853 adhesive Substances 0.000 abstract description 7
- 230000001070 adhesive effect Effects 0.000 abstract description 7
- WFKWXMTUELFFGS-UHFFFAOYSA-N tungsten Chemical compound [W] WFKWXMTUELFFGS-UHFFFAOYSA-N 0.000 abstract description 5
- 229910052721 tungsten Inorganic materials 0.000 abstract description 5
- 239000010937 tungsten Substances 0.000 abstract description 5
- 238000002844 melting Methods 0.000 abstract description 4
- 230000008018 melting Effects 0.000 abstract description 4
- 229910001220 stainless steel Inorganic materials 0.000 abstract description 4
- 239000010935 stainless steel Substances 0.000 abstract description 4
- ZOKXTWBITQBERF-UHFFFAOYSA-N Molybdenum Chemical compound [Mo] ZOKXTWBITQBERF-UHFFFAOYSA-N 0.000 abstract description 3
- 229910052750 molybdenum Inorganic materials 0.000 abstract description 3
- 239000011733 molybdenum Substances 0.000 abstract description 3
- 230000035515 penetration Effects 0.000 abstract 5
- 230000000694 effects Effects 0.000 abstract 1
- 238000004846 x-ray emission Methods 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- 230000005540 biological transmission Effects 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 230000001225 therapeutic effect Effects 0.000 description 3
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 2
- 229910052709 silver Inorganic materials 0.000 description 2
- 239000004332 silver Substances 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 1
- 238000004026 adhesive bonding Methods 0.000 description 1
- 230000002238 attenuated effect Effects 0.000 description 1
- 238000005219 brazing Methods 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- 239000011810 insulating material Substances 0.000 description 1
- 238000001959 radiotherapy Methods 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 210000005239 tubule Anatomy 0.000 description 1
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、Ｘ線発生源を患者
の体内に挿入して放射線治療を行う小型Ｘ線源に関す
る。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a compact X-ray source for performing radiotherapy by inserting an X-ray source into a patient's body.
【０００２】[0002]
【従来の技術】従来の小型Ｘ線源の一例が特表平6−500
661 号公報に開示されている。この小型Ｘ線源の構成に
ついて図４を用いて説明する。図４において、小型Ｘ線
源は、電子発生源１１，複数の電極で構成される電子加
速・集束系１３，電子発生源１１と電子加速・集束系１
３とを真空中に封入・保持する真空容器１，真空容器１
に接続される外径数mmの患者挿入細管１４，患者挿入細
管１４の先端に取り付けられるＸ線発生部１５，電子発
生源１１と電子加速・集束系１３に電力を供給する高圧
電源部２１，高圧電源部２１の出力を制御する制御部
３，真空容器１と高圧電源部２１とを保持するハウジン
グ２から構成される。2. Description of the Related Art An example of a conventional small X-ray source is Tokuhyo 6-500
No. 661 is disclosed. The structure of this small X-ray source will be described with reference to FIG. In FIG. 4, the small X-ray source includes an electron generation source 11, an electron acceleration / focusing system 13 composed of a plurality of electrodes, an electron generation source 11 and an electron acceleration / focusing system 1.
Vacuum container 1, vacuum container 1 for enclosing and holding 3 and 3 in a vacuum
A patient insertion thin tube 14 having an outer diameter of several mm, an X-ray generator 15 attached to the tip of the patient insertion thin tube 14, a high voltage power supply 21 for supplying electric power to an electron source 11 and an electron acceleration / focusing system 13, It is composed of a control unit 3, which controls the output of the high-voltage power supply unit 3, a vacuum container 1, and a housing 2 which holds the high-voltage power supply unit 21.
【０００３】電子発生源１１から放出された電子線は、
複数電極で構成される電子加速・集束系１３で加速・集
束され、患者挿入細管１４を通ってＸ線発生部１５に到
達しＸ線を発生する。発生したＸ線はＸ線発生部１５の
周囲の物質を透過して外部に放射され、治療対象６に照
射され、治療を行う。The electron beam emitted from the electron source 11 is
It is accelerated and focused by the electron acceleration / focusing system 13 composed of a plurality of electrodes, passes through the patient insertion thin tube 14, reaches the X-ray generation unit 15, and generates X-rays. The generated X-rays pass through the substance around the X-ray generation unit 15 and are radiated to the outside to irradiate the treatment target 6 for treatment.
【０００４】[0004]
【発明が解決しようとする課題】患者挿入細管１４に取
り付けられているＸ線発生部１５は、厚さ１mm程度の、
例えばベリリウムのようなＸ線透過材の円盤上に、例え
ばタングステンやモリブデンのような原子番号が大き
く、融点の高い材料を数μｍの膜厚で成膜したものであ
る。また、患者挿入細管１４には、例えばステンレス鋼
のような放出ガス量が少なく機械的強度の大きい材質の
パイプが用いられる。ステンレス鋼はＸ線吸収係数が大
きいため、小型Ｘ線源から放射されるＸ線は電子線の進
行方向の前方方向にのみ分布する。この場合のＸ線の放
射角度分布は図４に示す如くなり、Ｘ線焦点から治療対
象６側にのみ制限される。さらに、Ｘ線線量はＸ線焦点
からの距離が大きくなると急激に減衰するため、有効照
射野が狭く十分な治療効果を得られないという問題があ
った。従って、本発明では有効照射野の大きい小型Ｘ線
源を提供することを目的とした。The X-ray generator 15 attached to the patient insertion thin tube 14 has a thickness of about 1 mm.
For example, a material having a large atomic number and a high melting point, such as tungsten and molybdenum, is deposited on a disk of an X-ray transparent material such as beryllium to a film thickness of several μm. The patient insertion thin tube 14 is made of a material such as stainless steel that has a small amount of released gas and a large mechanical strength. Since stainless steel has a large X-ray absorption coefficient, X-rays emitted from a small X-ray source are distributed only in the forward direction of the electron beam traveling direction. The X-ray emission angle distribution in this case is as shown in FIG. 4, and is limited only from the X-ray focus to the treatment target 6 side. Further, since the X-ray dose rapidly attenuates as the distance from the X-ray focus increases, there is a problem that the effective irradiation field is narrow and a sufficient therapeutic effect cannot be obtained. Therefore, the object of the present invention is to provide a compact X-ray source having a large effective irradiation field.
【０００５】[0005]
【課題を解決するための手段】上記目的を達成するた
め、本発明では電子発生源と、電子線の加速・集束系
と、前記電子発生源と前記電子線の加速・集束系を収容
する真空容器と、該真空容器の一端に接続され、その先
端にＸ線発生部を具備する患者挿入細管と、前記電子発
生源と前記電子線の加速・集束系に電力を供給する電源
部とから構成する小型Ｘ線源において、前記Ｘ線発生部
のＸ線照射範囲を前記電子線の進行方向を基準にして９
０度より大きくしたことを特徴とする（請求項１）。In order to achieve the above object, in the present invention, an electron source, an electron beam acceleration / focusing system, and a vacuum housing the electron source and the electron beam acceleration / focusing system. A container, a patient insertion thin tube connected to one end of the vacuum container and provided with an X-ray generation unit at its tip, a power supply unit for supplying electric power to the electron source and the electron beam acceleration / focusing system. In the small X-ray source, the X-ray irradiation range of the X-ray generator is set to 9
It is characterized in that it is larger than 0 degree (claim 1).
【０００６】本発明では更に、前記Ｘ線発生部がカップ
状のＸ線透過材と、該Ｘ線透過材の内側底面に設けた原
子番号の大きな高融点元素からなるターゲット膜とから
構成されていることを特徴とする（請求項２）。Further, in the present invention, the X-ray generating portion is composed of a cup-shaped X-ray transmitting material and a target film made of a high melting point element having a large atomic number provided on the inner bottom surface of the X-ray transmitting material. (Claim 2).
【０００７】本発明では更に、前記カップ状Ｘ線透過材
の材質がベリリウム若しくはアルミニウムであることを
特徴とする（請求項３）。The present invention is further characterized in that the material of the cup-shaped X-ray transparent material is beryllium or aluminum (claim 3).
【０００８】本発明によれば、小型Ｘ線源から放射され
るＸ線を、Ｘ線焦点から治療対象６側にのみ制限するこ
となく、広い範囲に照射可能となる。According to the present invention, it is possible to irradiate a wide range of X-rays emitted from a compact X-ray source without limiting the X-ray focal point to the treatment target 6 side only.
【０００９】[0009]
【発明の実施の形態】以下、図面を用いて本発明の実施
例について説明する。図１は、本発明の構成の一実施例
を示したものである。本実施例の小型Ｘ線源は、電子発
生源１１，複数の電極で構成される電子加速・集束系１
３，電子発生源１１と電子加速・集束系１３とを真空中
に封入・保持する真空容器１，真空容器１に接続される
外径数mmの患者挿入細管１４，患者挿入細管１４の先端
に取り付けられるＸ線発生部１５，電子発生部１１と電
子加速・集束系１３に電力を供給する高圧電源部２１，
高圧電源部２１の出力を制御する制御部３，真空容器１
と高圧電源部２１を保持するハウジング２から構成され
る。本実施例の特徴は、Ｘ線発生部１５の構成にある。
以下、詳細に説明する。Embodiments of the present invention will be described below with reference to the drawings. FIG. 1 shows an embodiment of the configuration of the present invention. The small X-ray source of this embodiment is an electron source 11 and an electron acceleration / focusing system 1 composed of a plurality of electrodes.
3, a vacuum container 1 for enclosing and holding an electron source 11 and an electron acceleration / focusing system 13 in a vacuum 1, a patient insertion thin tube 14 with an outer diameter of several mm connected to the vacuum container 1, and a tip of the patient insertion thin tube 14. An X-ray generator 15, an electron generator 11, and a high-voltage power supply 21, which supplies electric power to the electron acceleration / focusing system 13,
Control unit 3 for controlling the output of the high-voltage power supply unit 3, vacuum container 1
And a housing 2 that holds the high-voltage power supply unit 21. The feature of this embodiment lies in the configuration of the X-ray generation unit 15.
The details will be described below.
【００１０】本実施例のＸ線発生部１５は、カップ状の
Ｘ線透過材１５ａの内側の底面にターゲット膜１５ｂを
付けたものである。カップ状のＸ線透過材１５ａにはベ
リリウムやアルミニウム等の原子番号の小さな元素を用
い、ターゲット膜１５ｂにはタングステンやモリブデン
等の原子番号の大きな、高融点の元素を用いる。カップ
状のＸ線透過材１５ａは患者挿入細管１４の細管部に接
続される。この接続はろう付又は接着等により行われ
る。カップ状のＸ線透過材１５ａを用いることにより、
従来品ではステンレス製の患者挿入細管１４でＸ線遮蔽
されていたＸ線が小型Ｘ線源外に放射されるため、Ｘ線
の有効照射野が拡がる。有効照射野はカップ状Ｘ線透過
材１５ａのカップ部の高さを高くすることにより拡大す
ることができる。The X-ray generating section 15 of this embodiment is a cup-shaped X-ray transmitting material 15a having a target film 15b attached to the inner bottom surface thereof. An element with a small atomic number such as beryllium or aluminum is used for the cup-shaped X-ray transparent material 15a, and a high melting point element with a large atomic number such as tungsten or molybdenum is used for the target film 15b. The cup-shaped X-ray transparent material 15a is connected to the thin tube portion of the patient insertion thin tube 14. This connection is made by brazing or gluing. By using the cup-shaped X-ray transmission material 15a,
In the conventional product, the X-rays shielded by the patient insertion thin tube 14 made of stainless steel are radiated to the outside of the small X-ray source, so that the effective X-ray irradiation field is expanded. The effective irradiation field can be expanded by increasing the height of the cup portion of the cup-shaped X-ray transparent material 15a.
【００１１】図２には、本発明適用品と従来品のＸ線線
量の放射角度依存性の概略比較を示す。図２において、
縦軸はＸ線線量の対数値を、横軸はＸ線放射角度θを示
したものである。Ｘ線放射角度は、ターゲット膜に入射
する電子線の方向を基準にした角度である。本発明適用
品のＸ線線量を実線Ａで、従来品のＸ線線量を破線Ｂで
示した。従来品でＸ線放射角度θ＝θ１(９０度より小
さい角度)でＸ線線量が大幅に減衰しているのに対し、
本発明適用品ではθ＝θ２（９０度より大きい角度）ま
でＸ線線量が大きく、Ｘ線放射領域が広がっている。す
なわち、本発明適用品の如くカップ状のＸ線透過材１５
ａを用いることにより、Ｘ線の有効照射野は、０〜θ１
の範囲から０〜θ２の範囲に拡大することができる。ま
た、本発明適用品においても、θ＝θ１の近くで若干の
減衰が生ずるが、狭い範囲であるので実用上の問題はな
い。FIG. 2 shows a schematic comparison of the radiation angle dependence of the X-ray dose between the product of the present invention and the conventional product. In FIG.
The vertical axis shows the logarithmic value of the X-ray dose, and the horizontal axis shows the X-ray emission angle θ. The X-ray emission angle is an angle based on the direction of the electron beam incident on the target film. The solid line A shows the X-ray dose of the product to which the invention is applied, and the broken line B shows the X-ray dose of the conventional product. In the conventional product, the X-ray dose is greatly attenuated at the X-ray emission angle θ = θ1 (angle smaller than 90 degrees).
In the product to which the present invention is applied, the X-ray dose is large up to θ = θ2 (angle larger than 90 degrees), and the X-ray emission region is widened. That is, the cup-shaped X-ray transmission material 15 like the product to which the present invention is applied.
By using a, the effective irradiation field of X-rays is 0 to θ1.
Can be expanded from the range of 0 to the range of θ2. Also in the product to which the present invention is applied, some attenuation occurs near θ = θ1, but there is no practical problem because it is in a narrow range.
【００１２】以上説明した如く、カップ状のＸ線透過材
を用いることにより、Ｘ線有効照射野の拡大をはかるこ
とができるが、バルク材のベリリウムをカップ状に加工
して、内面の底にタングステン膜を形成するのには作業
に困難が伴うものである。そこで、以下に示すような方
法によってもベリリウム製のカップ状Ｘ線透過材を得る
ことができるので、その方法について説明する。As described above, by using a cup-shaped X-ray transmitting material, the effective X-ray irradiation field can be expanded. It is difficult to form a tungsten film. Therefore, a cup-shaped X-ray transparent material made of beryllium can also be obtained by the method described below, so that method will be described.
【００１３】図３には、ベリリウム製のカップ状Ｘ線透
過材の一例を示す。図３において、カップ状Ｘ線透過材
１５ａは、外径の等しい円盤１５ａ1と円筒１５ａ2のベ
リリウム材から構成される。円盤１５ａ1 にはあらかじ
めタングステン等の高融点元素をＸ線ターゲット膜１５
ｂとして成膜しておく。円盤１５ａ1と円筒１５ａ2の
間、円筒１５ａ1 と患者挿入細管１４との間は、真空用
接着剤などにより結合する。ただし、真空用接着剤は通
常絶縁物であるため、円盤１５ａ1と円筒１５ａ2の間、
円筒１５ａ2 と患者挿入細管１４の接合面を真空用接着
剤で満たすと、Ｘ線ターゲットの部分が患者挿入細管１
４から絶縁されることになり、Ｘ線ターゲット１５ｂに
入射した電子はＸ線ターゲット１５ｂ及びベリリウム製
円盤１５a1に留まり、これらを充電することになる。こ
れを避けるため、円盤１５ａ1 ，円筒１５ａ2 及び患者
挿入細管１４の導電性を確保する必要がある。FIG. 3 shows an example of a cup-shaped X-ray transparent material made of beryllium. In FIG. 3, the cup-shaped X-ray transparent material 15a is composed of a beryllium material of a disk 15a 1 and a cylinder 15a 2 having the same outer diameter. The disk 15a 1 is preliminarily provided with a refractory element such as tungsten in the X-ray target film 15
The film is formed as b. The disk 15a 1 and the cylinder 15a 2 and the cylinder 15a 1 and the patient insertion thin tube 14 are connected by a vacuum adhesive or the like. However, since the vacuum adhesive is usually an insulating material, the adhesive between the disk 15a 1 and the cylinder 15a 2
When the joint surface between the cylinder 15a 2 and the patient-inserted thin tube 14 is filled with a vacuum adhesive, the portion of the X-ray target is filled with the patient-inserted thin tube 1.
Therefore, the electrons incident on the X-ray target 15b remain in the X-ray target 15b and the beryllium disk 15a 1 and charge them. In order to avoid this, it is necessary to ensure the conductivity of the disk 15a 1 , the cylinder 15a 2 and the patient insertion thin tube 14.
【００１４】導電性を確保するための一例として、銀ペ
ースト等を外表面に薄く塗布する方法が考えられる。し
かし、銀が厚すぎるとＸ線遮蔽材となるので、Ｘ線有効
照射野の拡大を損うおそれがある。そこで、図に示すよ
うに、円筒１５ａ2 及び患者挿入細管１４に溝２０を設
け、この部分に真空用接着剤２２を流し込み、接合面の
一部は円盤１５ａ1 と円筒１５ａ2 の間、円筒１５ａ2
と患者挿入細管１４の間で接触させて、導電性を維持す
るようにする。上述の如き構成をとることにより、ベリ
リウム製のカップ状Ｘ線透過材１５ａを形成することが
可能となり、小型Ｘ線源の有効照射野を拡大し、治療効
果の向上をはかることができる。As an example for ensuring conductivity, a method of thinly applying silver paste or the like on the outer surface can be considered. However, if the silver is too thick, it becomes an X-ray shielding material, which may impair the expansion of the X-ray effective irradiation field. Therefore, as shown in the figure, a groove 20 is provided in the cylinder 15a 2 and the patient insertion thin tube 14, and a vacuum adhesive 22 is poured into this portion, and a part of the joint surface is between the disk 15a 1 and the cylinder 15a 2 15a 2
And the patient insertion tubule 14 are contacted to maintain electrical conductivity. With the above-described configuration, the cup-shaped X-ray transparent material 15a made of beryllium can be formed, the effective irradiation field of the small X-ray source can be expanded, and the therapeutic effect can be improved.
【００１５】[0015]
【発明の効果】以上説明した如く、本発明によれば、小
型Ｘ線源から放射されるＸ線は、Ｘ線焦点から治療対象
６側にのみ制限されることがなくなるため、その有効照
射範囲は従来に比較して広くなり、治療効果を向上させ
ることができる。As described above, according to the present invention, the X-rays emitted from the small X-ray source are not limited to the treatment target 6 side from the X-ray focal point, and therefore the effective irradiation range thereof. Is wider than before, and the therapeutic effect can be improved.
【図１】本発明の一実施例を示す図。FIG. 1 is a diagram showing one embodiment of the present invention.
【図２】本発明適用品と従来品のＸ線線量の放射角度依
存性の概略比較を示す図。FIG. 2 is a diagram showing a schematic comparison of radiation angle dependence of X-ray dose between a product to which the present invention is applied and a conventional product.
【図３】ベリリウム製のカップ状Ｘ線透過材の一例を示
す図。FIG. 3 is a diagram showing an example of a cup-shaped X-ray transparent material made of beryllium.
【図４】従来の小型Ｘ線源の構成を示す図。FIG. 4 is a diagram showing a configuration of a conventional small X-ray source.
１ 真空容器 ２ ハウジング ３ 制御部 １１ 電子発生源 １３ 電子加速・集束系 １４ 患者挿入細管 １５ Ｘ線発生部 １５ａ カップ状Ｘ線透過材 １５ａ1 ベリリウム製円盤 １５ａ2 ベリリウム製円筒 １５ｂ Ｘ線ターゲット膜 ２０ 溝 ２１ 高圧電源部 ２２ 真空用接着剤DESCRIPTION OF SYMBOLS 1 Vacuum container 2 Housing 3 Control part 11 Electron generation source 13 Electron acceleration / focusing system 14 Patient insertion thin tube 15 X-ray generation part 15a Cup-shaped X-ray transmission material 15a 1 Beryllium disc 15a 2 Beryllium cylinder 15b X-ray target film 20 Groove 21 High voltage power supply 22 Vacuum adhesive
Claims (3)
前記電子発生源と前記電子線の加速・集束系を収容する
真空容器と、該真空容器の一端に接続され、その先端に
Ｘ線発生部を具備する患者挿入細管と、前記電子発生源
と前記電子線の加速・集束系に電力を供給する電源部と
から構成する小型Ｘ線源において、前記Ｘ線発生部のＸ
線照射範囲を前記電子線の進行方向を基準にして９０度
より大きくしたことを特徴とする小型Ｘ線源。1. An electron source, an electron beam acceleration / focusing system,
A vacuum container for accommodating the electron source and the electron beam acceleration / focusing system, a patient insertion thin tube connected to one end of the vacuum container and having an X-ray generator at its tip, the electron source and the A small X-ray source including a power supply unit for supplying electric power to an electron beam acceleration / focusing system, wherein X of the X-ray generation unit is used.
A small X-ray source, characterized in that a radiation range is set to be larger than 90 degrees with respect to a traveling direction of the electron beam.
Ｘ線発生部がカップ状のＸ線透過材と、該Ｘ線透過材の
内側底面に設けた原子番号の大きな高融点元素からなる
ターゲット膜とから構成されていることを特徴とする小
型Ｘ線源。2. The miniature X-ray source according to claim 1, wherein the X-ray generation section is composed of a cup-shaped X-ray transmitting material and a refractory element having a large atomic number provided on the inner bottom surface of the X-ray transmitting material. A small X-ray source, which comprises a target film.
カップ状Ｘ線透過材の材質がベリリウム若しくはアルミ
ニウムであることを特徴とする小型Ｘ線源。3. The compact X-ray source according to claim 2, wherein the material of the cup-shaped X-ray transparent material is beryllium or aluminum.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP7314900A JPH09134795A (en) | 1995-11-09 | 1995-11-09 | Small sized x-ray source |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP7314900A JPH09134795A (en) | 1995-11-09 | 1995-11-09 | Small sized x-ray source |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH09134795A true JPH09134795A (en) | 1997-05-20 |
Family
ID=18058995
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP7314900A Pending JPH09134795A (en) | 1995-11-09 | 1995-11-09 | Small sized x-ray source |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH09134795A (en) |
-
1995
- 1995-11-09 JP JP7314900A patent/JPH09134795A/en active Pending
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