JPS583360B2 - X Sensokusha Sochi - Google Patents
X Sensokusha SochiInfo
- Publication number
- JPS583360B2 JPS583360B2 JP753198A JP319875A JPS583360B2 JP S583360 B2 JPS583360 B2 JP S583360B2 JP 753198 A JP753198 A JP 753198A JP 319875 A JP319875 A JP 319875A JP S583360 B2 JPS583360 B2 JP S583360B2
- Authority
- JP
- Japan
- Prior art keywords
- ionization chamber
- ray
- detection circuit
- current detection
- electrodes
- 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.)
- Expired
Links
- 238000001514 detection method Methods 0.000 claims description 14
- 238000003384 imaging method Methods 0.000 claims description 12
- 150000002500 ions Chemical class 0.000 claims description 11
- 238000010586 diagram Methods 0.000 description 6
- 238000000034 method Methods 0.000 description 3
- 239000007769 metal material Substances 0.000 description 2
- 210000002784 stomach Anatomy 0.000 description 2
- 210000001835 viscera Anatomy 0.000 description 2
- 230000002238 attenuated effect Effects 0.000 description 1
- 230000005684 electric field Effects 0.000 description 1
- 210000004394 hip joint Anatomy 0.000 description 1
- 238000009413 insulation Methods 0.000 description 1
- 230000002427 irreversible effect Effects 0.000 description 1
- 238000002601 radiography Methods 0.000 description 1
- 230000035939 shock Effects 0.000 description 1
- 238000002834 transmittance Methods 0.000 description 1
- 229910052724 xenon Inorganic materials 0.000 description 1
- FHNFHKCVQCLJFQ-UHFFFAOYSA-N xenon atom Chemical compound [Xe] FHNFHKCVQCLJFQ-UHFFFAOYSA-N 0.000 description 1
Landscapes
- X-Ray Techniques (AREA)
- Apparatus For Radiation Diagnosis (AREA)
- Analysing Materials By The Use Of Radiation (AREA)
- Measurement Of Radiation (AREA)
- Exposure Or Original Feeding In Electrophotography (AREA)
Description
【発明の詳細な説明】
本発明はフォトタイマー装置の改良を図った電子写真方
式のＸ線速写装置に関するものである。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to an electrophotographic X-ray speed copying apparatus that is an improved phototimer device.
Ｘ線速写装置は被写体をＸ線透視しながら患部を観察し
、必要に応じ透視像の最適状態を見計らって収納器に収
納されたフイルムをその透視像撮影位置に移動させてＸ
線写真を撮影するようにしたものであり、心臓や胃等常
に活動をしている内臓等の撮影を所望の状態になった時
行なえるようにした診断装置である。The X-ray imaging device observes the affected area while viewing the subject through X-rays, determines the optimal state of the fluoroscopic image as necessary, moves the film stored in the storage container to the fluoroscopic image capturing position, and then displays the X-ray image.
This diagnostic device is designed to take line photographs, and can take pictures of internal organs that are constantly active, such as the heart and stomach, when they reach a desired state.
この装置は上述の如く撮影対象となる内臓等の動きを見
ながらチャンス到来時にフイルムを撮影位置まで移動さ
せなければならないからフイルムを収納器ごと撮影位置
まで移動させるための駆動装置が必要であり高価で複雑
となる他、撮影位置までフイルムを送るまで１〜２秒程
度の時間遅れが生じシャツタチャンスを逸して所望とし
た写真が得にくく、またフイルムを収納した収納器が撮
影位置に到達したときのショックで写真にブレを生じさ
せる等の欠点があった。As mentioned above, this device requires moving the film to the shooting position when the opportunity arises while watching the movement of the internal organs to be photographed, so a drive device is required to move the film along with the storage container to the shooting position, which is expensive. In addition to this, there is a time delay of about 1 to 2 seconds before the film is sent to the shooting position, which makes it difficult to obtain the desired photo due to missed opportunities to shoot, and also when the storage container containing the film reaches the shooting position. There were drawbacks such as the shock of the moment causing blur in the photograph.
そこで近時、第１図ａに示す如く構成された電子写真の
一種であるエレクトロンラジオグラフイ方式（ＥＲＧ方
式）のＸ線撮影装置が提案されている。Therefore, recently, an X-ray photographing apparatus using the electron radiography method (ERG method), which is a type of electrophotography, has been proposed as shown in FIG. 1a.
即ち、互いに対向して設けられた一対の平板状の高圧電
極１ａ，１ｂ（ここで、Ｘ線入射側の高圧電極１ａはＸ
線の減衰を防ぐため軽原子番号の金属材料で、また他方
の電極１ｂは重原子番号の金属材料で作られているもの
とする。That is, a pair of flat high-voltage electrodes 1a and 1b are provided facing each other (here, the high-voltage electrode 1a on the X-ray incident side is
In order to prevent line attenuation, the electrode 1b is made of a metal material with a light atomic number, and the other electrode 1b is made of a metal material with a heavy atomic number.
）を内臓する気密構造の電離箱１とこの電離箱１に１０
気圧程度の高圧Ｘｅ（キセノン）ガスを供給する高圧ガ
ス供給源２と前記電離箱１の高圧電極１ａ，１ｂに直流
高電圧を供給する第１の高電圧電源３と前記電離箱１に
対向して設けられるＸ線管４とこのＸ線管４に直流高電
圧を供給する第２の高電圧電源５とこれら第１及び第２
の高電圧電源３，５を制御する制御スイッチ６とより構
成され被写体即ち天板７上に載置された被検者８を介し
て上方に前記Ｘ線管４を、下方に前記電離箱１を配置す
る。) and an ionization chamber 1 with an airtight structure containing 10
Opposed to the ionization chamber 1 are a high-pressure gas supply source 2 that supplies high-pressure Xe (xenon) gas of approximately atmospheric pressure, and a first high-voltage power source 3 that supplies a DC high voltage to the high-voltage electrodes 1a and 1b of the ionization chamber 1. an X-ray tube 4 provided in the
The X-ray tube 4 is placed above the subject 8 placed on the top plate 7, and the ionization chamber 1 is placed below the ionization chamber 1. Place.
そして、電離箱１の高電圧電極１ａ，１ｂのいずれか１
方例えば負電位を印加される高電圧電極を１ａとすれば
この１ａにシート状の絶縁板９を装着し制御スイッチ６
を操作してＸ線管４と電離箱１の高圧電極１ａ，１ｂに
高電圧を印加する。Then, one of the high voltage electrodes 1a and 1b of the ionization chamber 1
For example, if a high voltage electrode to which a negative potential is applied is 1a, a sheet-like insulating plate 9 is attached to this 1a, and a control switch 6 is installed.
A high voltage is applied to the X-ray tube 4 and the high-voltage electrodes 1a and 1b of the ionization chamber 1 by operating the .
すると、Ｘ線管４からＸ線が曝射されこのＸ線は被検者
８の体内を透過して電離箱１に到達する。Then, X-rays are emitted from the X-ray tube 4, and the X-rays pass through the body of the subject 8 and reach the ionization chamber 1.
Ｘ線が電離箱１内の高圧ガスにぶつかるとその線量に対
応して高圧ガスが電離し、プラスイオンとマイナスイオ
ンが発生する。When the X-rays collide with the high-pressure gas in the ionization chamber 1, the high-pressure gas is ionized in accordance with the dose, and positive ions and negative ions are generated.
これらイオンは電極１ａ，１ｂの電界にてそれぞれ電極
１ａ，１ｂに引き寄せられるがその際、プラスイオンは
電極１ａの絶縁板９にぶつかり、この絶縁板９にチャー
ジされて撮影対象部位の肉眼では見ることのできない電
気潜像を形成する。These ions are attracted to the electrodes 1a and 1b by the electric field of the electrodes 1a and 1b, respectively, but at that time, the positive ions collide with the insulating plate 9 of the electrode 1a, and the insulating plate 9 is charged and visible to the naked eye in the area to be photographed. Forms an irreversible electrical latent image.
このようにして得られた電気潜像について、適宜なる方
法により現像、定着を行なう。The electric latent image thus obtained is developed and fixed by an appropriate method.
上記ＥＲＧ方式のＸ線速写装置は高圧電極１ａ，１ｂに
高電圧を印加しなければＸ線照射野内に絶縁板９を置い
てあってもそれに電荷はチャージされないから、透視の
時でも絶縁板９をＸ線照射野内の撮影位置に置いておく
ことができ、従来のフイルムにより撮影を行なう装置の
ようなフイルム収納器駆動装置が全く不要となり、しか
も撮影は高電圧電極１ａ，１ｂに高圧電圧を加えるだけ
で良いので撮影のタイミングを逸することがない。In the above-mentioned ERG type X-ray copying apparatus, unless a high voltage is applied to the high-voltage electrodes 1a and 1b, even if the insulating plate 9 is placed in the X-ray irradiation field, no electric charge will be charged to it. can be placed at the imaging position within the X-ray irradiation field, and there is no need for a film storage device drive device like in conventional film imaging devices.Moreover, during imaging, high voltage is applied to the high voltage electrodes 1a and 1b. All you have to do is add it, so you won't miss the timing to take a photo.
ところで、Ｘ線は被検者の体格や撮影部位等により透過
率が異なるから、画質の良好なＸ線写真を得るには、こ
れらの点を考慮して曝射Ｘ線量を設定する必要がある。By the way, the transmittance of X-rays differs depending on the physique of the patient and the area being photographed, so in order to obtain high-quality X-ray photographs, it is necessary to set the exposure X-ray dose with these points in mind. .
これを手動設定するとすれば操作者の勘と経験に頼るこ
とになるが、いきおい撮影失敗が多くなり、無駄な手間
や被検者の無要な被曝を招くため、撮影対象部位を透過
したＸ線量を検出し所定値に達するとＸ線曝射を停止さ
せるようにしたフォトタイマー装置が用いられる。If this were to be set manually, it would depend on the operator's intuition and experience, but this would result in more imaging failures, wasted effort, and unnecessary radiation exposure for the patient. A phototimer device is used that detects the dose and stops X-ray exposure when it reaches a predetermined value.
このフォトタイマー装置は透過Ｘ線を検出し電気信号に
変換するＸ線検出器と、この電気信号の積算値が所定値
に達するとＸ線曝射停止信号を出力してＸ線の曝射を停
止させる制御部とより構成されているが、このうちのＸ
線検出器は第１図ｂに点線で示すように一般に電離箱１
の前面側Ａ位置または電離箱１の後面側Ｂ位置に配置さ
れる。This phototimer device includes an X-ray detector that detects transmitted X-rays and converts them into electrical signals, and when the integrated value of the electrical signals reaches a predetermined value, it outputs an X-ray exposure stop signal and stops X-ray exposure. It consists of a control section that stops the
The line detector is generally installed in the ionization chamber 1 as shown by the dotted line in Figure 1b.
is placed at position A on the front side of the ion chamber 1 or position B on the rear side of the ionization chamber 1.
この場合、前面側に配置される前面検出方式に於いては
Ｘ線検出器が電離箱１に影を作ることになり良い写真が
得にくく、また電離箱１の後面側に配置する後面検出方
式に於いては電離箱１の陰になるためＸ線が減衰し検出
特性が悪くなる等の欠点を有する。In this case, in the front detection method in which the X-ray detector is placed on the front side, the X-ray detector casts a shadow on the ionization chamber 1, making it difficult to obtain a good photograph; However, since it is in the shadow of the ionization chamber 1, the X-rays are attenuated, resulting in poor detection characteristics.
ところで、Ｘ線検出器は一般に電離箱が用いられるが、
ＥＲＧ方式のＸ線速写装置は撮影を行な５部分に電離箱
１が設けられており、これをＸ線検出器と兼用すれば電
離箱１に到達する撮影に寄与するＸ線そのものを損失無
くしかも撮影に全く影響を与えること無く検出すること
ができ、正確な線量を検出することが可能となる。By the way, an ionization chamber is generally used as an X-ray detector,
The ERG type X-ray imaging device performs imaging and is equipped with ionization chambers 1 in five sections.If this is also used as an X-ray detector, the X-rays themselves that reach the ionization chamber 1 and contribute to the imaging can be removed without loss. Moreover, it can be detected without affecting the imaging at all, and it is possible to accurately detect the dose.
本考案は上記事情に鑑みて成されたもので、ＥＲＧ方式
のＸ線速写装置の電離箱をフォトタイマー装置のＸ線検
出器と兼用させると共に電離箱の一方の電極を細分化し
撮影対象部位の形状に合わせてこれら電極を選択してフ
ォトタイマー用の信号を取り出すことにより前記欠点を
解消し良質の写真が得られるようにしたフォトタイマー
を有するＸ線速写装置を提供することを目的とする。The present invention was developed in view of the above circumstances, and it combines the ionization chamber of an ERG type X-ray imaging device with the X-ray detector of a phototimer device, and divides one electrode of the ionization chamber into smaller pieces to detect the area to be imaged. It is an object of the present invention to provide an X-ray photographic device having a phototimer which eliminates the above-mentioned drawbacks and makes it possible to obtain high-quality photographs by selecting these electrodes according to the shape and extracting signals for the phototimer.
以下、本考案の一実施例について図面を参照して説明す
る。An embodiment of the present invention will be described below with reference to the drawings.
第２図は本装置の電離箱部分の概略構成を示す図であり
、２１は電離箱の外筐、２２，２３はこの外筺２１内に
互いに対向して配置された一対の高圧電極であり、この
電極２２，２３のうち図示下方の電極２３を複数の区画
に区分しそれぞれを電気的に独立させてある。FIG. 2 is a diagram showing a schematic configuration of the ionization chamber portion of this device, where 21 is an outer casing of the ionization chamber, and 22 and 23 are a pair of high-voltage electrodes arranged opposite to each other within this outer casing 21. Of these electrodes 22 and 23, the lower electrode 23 in the figure is divided into a plurality of sections, each of which is electrically independent.
そして、これら区分された分割電極２３ａ，２３ｂ、２
３ｃ・・・は各々常開及び常閉接点を有する選択スイッ
チ２４ａ，２４ｂ，２４ｃ・・・に接続されている。These divided electrodes 23a, 23b, 2
3c... are connected to selection switches 24a, 24b, 24c... each having normally open and normally closed contacts.
更にこれら選択スイッチ２４ａ，２４ｂ，２４ｃ・・・
の常閉接点側他端は開閉スイッチ２５を介して直流高圧
電源２６の正極側に接続され、この直流高圧電源２６の
負極側は前記図示上方側の電極２２に接続されている。Furthermore, these selection switches 24a, 24b, 24c...
The other end of the normally closed contact side is connected to the positive electrode side of a DC high voltage power source 26 via the open/close switch 25, and the negative electrode side of this DC high voltage power source 26 is connected to the electrode 22 on the upper side in the figure.
更に前記選択スイッチ２４ａ，２４ｂ，２４ｃ，・・・
の常開接点側他端は電離電流を検出して信号を出力する
電離電流検出回路２７及び前記開閉スイッチ２５を介し
て前記直流高圧電源２６の正極側に接続されている。Furthermore, the selection switches 24a, 24b, 24c, . . .
The other end of the normally open contact side is connected to the positive electrode side of the DC high voltage power supply 26 via the ionization current detection circuit 27 that detects ionization current and outputs a signal, and the opening/closing switch 25.
２８は電離電流検出回路２７の出力信号を積算し予め設
定された値に達するとＸ線曝射停止信号を出力する制御
部である。28 is a control unit that integrates the output signal of the ionizing current detection circuit 27 and outputs an X-ray exposure stop signal when a preset value is reached.
このような構成の電離箱をＥＲＧ方式のＸ線速射装置に
内臓させ且つ制御部２８の出力側をＸ線曝射を制御する
制御スイッチ６に接続しておく。The ionization chamber having such a configuration is built into an ERG type X-ray rapid emission device, and the output side of the control section 28 is connected to the control switch 6 for controlling X-ray exposure.
次に上記構成の本装置の動作について説明する。Next, the operation of this apparatus having the above configuration will be explained.
今、分割電極２３ａに注目し選択スイッチ２４ａを作動
させたとすると、選択スイッチ２４ａの常閉接点は開き
、常開接点は閉じる。Now, if we focus on the divided electrode 23a and operate the selection switch 24a, the normally closed contact of the selection switch 24a will open and the normally open contact will close.
他の選択スイッチ２４ｂ，２４ｃ，・・・は作動させな
いので常閉接点側のみ閉じている。Since the other selection switches 24b, 24c, . . . are not operated, only the normally closed contact side is closed.
この状態で開閉スイッチ２５を閉じると電極２２には負
極性の高電圧が、また電極２３の分割電極２３ａ，２３
ｂ，２３ｃ・・・には正極性の高電圧が印加される。When the open/close switch 25 is closed in this state, a negative high voltage is applied to the electrode 22, and the divided electrodes 23a, 23 of the electrode 23 are
A high voltage of positive polarity is applied to b, 23c, .
従ってＸ線管４より曝射されたＸ線が電離箱内に到達す
ると電離箱内のガスがＸ線量に応じて電離し、プラスイ
オンは負極側である電極２２へ、マイナスイオンは正極
側である電極２３の各分割電極２３ａ，２３ｂ，２３ｃ
・・・に引き寄せられる。Therefore, when the X-rays emitted from the X-ray tube 4 reach the ionization chamber, the gas inside the ionization chamber is ionized according to the amount of X-rays, and the positive ions are transferred to the electrode 22, which is the negative electrode side, and the negative ions are transferred to the positive electrode side. Each divided electrode 23a, 23b, 23c of a certain electrode 23
I'm drawn to...
この引き寄せられたイオンは電離電流として、電離箱の
回路中を流れるがそのうちの分割電極２３ａに引き寄せ
られたイオンによる電離電流だけは選択スイッチ２４ａ
の常開接点側を通り電離電流検出回路２７を通って流れ
る。These attracted ions flow through the circuit of the ionization chamber as ionization current, but only the ionization current due to the ions attracted to the divided electrode 23a flows through the selection switch 24a.
The current flows through the normally open contact side of the ionizing current detection circuit 27.
そのため、この電離電流検出回路２７は分割電極２３ａ
部分に到来するＸ線のみを検出したことになり、この分
割電極２３ａが撮影対象部分と対向し且つこの撮影対象
部分を十分カバーするだけの面積であったとすれば実質
的に撮影対象部分の透過線量が検出されることになる。Therefore, this ionization current detection circuit 27 has a split electrode 23a.
This means that only the X-rays arriving at the area are detected, and if this divided electrode 23a faces the area to be imaged and has an area sufficient to cover the area to be imaged, then the area to be imaged is substantially transmitted. The dose will be detected.
従って、この電離電流検出回路２７の出力信号を受けて
作動する制御部２８は撮影対象部分を撮影するのに最も
適した露光量に達した時にＸ線曝射停止信号が出力され
ることになり、この信号により制御スイッチ６が作動し
て電源をしゃ断し撮影が終了される。Therefore, the control section 28, which operates in response to the output signal of the ionizing current detection circuit 27, outputs an X-ray exposure stop signal when the most suitable exposure amount for photographing the area to be photographed is reached. In response to this signal, the control switch 6 is operated to cut off the power and the photographing is completed.
尚、この場合図示下方の電極２３を分割電極としたので
、撮影用の絶縁板は図示上方の電極２２近傍に設けるこ
とになりプラスイオンによる電気潜像として撮影される
が、これを逆にしても同様に実施できる。In this case, since the lower electrode 23 in the figure is a split electrode, the insulating plate for photographing will be provided near the upper electrode 22 in the figure, and an electric latent image of positive ions will be photographed, but if this is reversed. can be implemented in the same way.
また分極電極は第３図に示すように更に細分化し、胃で
はパターンＩに、胸部ではパターン■に、股関節ではパ
ターン■という具合に撮影対象に合わせてこれら分割電
極を組み合わせて電離電流を検出することにより、より
正確な露光制御ができる。In addition, the polarized electrodes are further subdivided as shown in Figure 3, and the ionizing current is detected by combining these divided electrodes according to the subject to be imaged, such as pattern I for the stomach, pattern ■ for the chest, and pattern ■ for the hip joints. This allows more accurate exposure control.
このように、電離箱の電極のうちの一方を細分化して各
々を電気的に独立させると共に各々選択スイッチをより
電離電流検出回路を介して高圧電源にまたは直接高圧電
源に接続する二通りの回路を選択できるようにしたので
、撮影部分の形状に合わせて細分化された分割電極を選
択し電離電流検出回路につなぐようにすることにより、
絶縁板の撮影対象部分に対する正確な露光量が検出でき
るから、良質のＸ線写真を得ることができ、しかも電離
箱がフォトタイマーの検出器と兼用されるので、部品が
少なくなる等優れた性能を有するＥＲＧ方式のＸ線速写
装置が得られる。In this way, one of the electrodes of the ionization chamber is subdivided to make each one electrically independent, and each selection switch is connected to the high-voltage power supply via the ionization current detection circuit or directly to the high-voltage power supply. By selecting the divided electrodes that are subdivided according to the shape of the imaged area and connecting them to the ionizing current detection circuit,
Since the accurate exposure amount for the area to be photographed on the insulating plate can be detected, high-quality X-ray photographs can be obtained, and since the ionization chamber is also used as a phototimer detector, the number of parts is reduced, resulting in excellent performance. An ERG-type X-ray photographic device having the following can be obtained.
第１図ａはＥＲＧ方式のＸ線速写装置を説明するための
図、第１図ｂはＸ線検出器の配置例を説明するための図
、第２図は本考案の一実施例を示す電離箱部分の概略構
成図、第３図は分割電極の一例を示す図である。
１・・・・・・電離箱、１ａ，１ｂ，２２，２３・・・
・・・高圧電極、４・・・・・・Ｘ線管、８・・・・・
・被検者、９・・・・・・絶縁板、２３ａ，２３ｂ、２
３ｃ・・・・・分割電極、２４ａ，２４ｂ，２４ｃ・・
・・選択スイッチ、２６・・・・・・高圧電源、２７・
・・・・・電離電流検出回路、２８・・・・・・制御部
。Fig. 1a is a diagram for explaining an ERG type X-ray copying device, Fig. 1b is a diagram for explaining an example of the arrangement of an X-ray detector, and Fig. 2 is a diagram showing an embodiment of the present invention. A schematic configuration diagram of the ionization chamber portion, and FIG. 3 is a diagram showing an example of a divided electrode. 1...Ionization chamber, 1a, 1b, 22, 23...
...High voltage electrode, 4...X-ray tube, 8...
・Subject, 9... Insulation plate, 23a, 23b, 2
3c...Divided electrode, 24a, 24b, 24c...
...Selection switch, 26...High voltage power supply, 27.
... Ionization current detection circuit, 28 ... Control section.
Claims (1)
体を介してこの電離箱に対向して設けられるＸ線管から
のＸ線により電離したイオンをこの絶縁板にチャージす
ることにより撮影を行なうＸ線速写装置に於いて、前記
一対の高圧電極の一方を複数の区画に分割して各々電気
的に独立した分割電極とした電離箱と、これら分割電極
からの電流を検出する電離電流検出回路と、撮影時前記
電離箱の両高圧電極に電圧を供給する高電圧電源と、前
記被写体の形状に対応して前記分割電極を選択し前記電
離電流検出回路に接続する選択スイッチと、前記電離電
流検出回路の出力信号を積算し予め設定した値に達した
ときＸ線曝射停止信号を出力しＸ線の曝射を停止させる
制御部とを備えたことを特徴とするＸ線速写装置。1. By placing an insulating plate between a pair of high-voltage electrodes in an ionization chamber, and charging this insulating plate with ions ionized by X-rays from an X-ray tube placed opposite the ionization chamber through the subject. In an X-ray photographic device that performs imaging, there is an ionization chamber that divides one of the pair of high-voltage electrodes into a plurality of sections, each of which is an electrically independent divided electrode, and an ionization chamber that detects the current from these divided electrodes. a current detection circuit, a high voltage power supply that supplies voltage to both high voltage electrodes of the ionization chamber during imaging, and a selection switch that selects the divided electrode in accordance with the shape of the object and connects it to the ionization current detection circuit; An X-ray flash photography characterized by comprising: a control unit that outputs an X-ray exposure stop signal to stop X-ray exposure when the output signals of the ionizing current detection circuit reach a preset value by integrating the output signals of the ionizing current detection circuit. Device.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP753198A JPS583360B2 (en) | 1974-12-26 | 1974-12-26 | X Sensokusha Sochi |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP753198A JPS583360B2 (en) | 1974-12-26 | 1974-12-26 | X Sensokusha Sochi |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5176088A JPS5176088A (en) | 1976-07-01 |
| JPS583360B2 true JPS583360B2 (en) | 1983-01-20 |
Family
ID=11550713
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP753198A Expired JPS583360B2 (en) | 1974-12-26 | 1974-12-26 | X Sensokusha Sochi |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS583360B2 (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0218764U (en) * | 1988-07-25 | 1990-02-07 | ||
| JPH0233162U (en) * | 1988-06-24 | 1990-03-01 |
-
1974
- 1974-12-26 JP JP753198A patent/JPS583360B2/en not_active Expired
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0233162U (en) * | 1988-06-24 | 1990-03-01 | ||
| JPH0218764U (en) * | 1988-07-25 | 1990-02-07 |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5176088A (en) | 1976-07-01 |
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