JPS58145098A - Portable x-ray generator - Google Patents
Portable x-ray generatorInfo
- Publication number
- JPS58145098A JPS58145098A JP57027237A JP2723782A JPS58145098A JP S58145098 A JPS58145098 A JP S58145098A JP 57027237 A JP57027237 A JP 57027237A JP 2723782 A JP2723782 A JP 2723782A JP S58145098 A JPS58145098 A JP S58145098A
- Authority
- JP
- Japan
- Prior art keywords
- ray tube
- switch
- outside
- ray
- portable
- 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.)
- Granted
Links
- 239000012212 insulator Substances 0.000 claims abstract description 7
- 230000003287 optical effect Effects 0.000 claims abstract description 6
- 239000013307 optical fiber Substances 0.000 claims abstract description 6
- 239000004020 conductor Substances 0.000 claims abstract description 4
- 235000014676 Phragmites communis Nutrition 0.000 claims description 2
- 238000010248 power generation Methods 0.000 claims description 2
- 229920003002 synthetic resin Polymers 0.000 abstract description 3
- 239000000057 synthetic resin Substances 0.000 abstract description 3
- 239000011248 coating agent Substances 0.000 abstract 1
- 238000000576 coating method Methods 0.000 abstract 1
- 238000010894 electron beam technology Methods 0.000 description 13
- 238000010586 diagram Methods 0.000 description 4
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 3
- 230000005540 biological transmission Effects 0.000 description 3
- 229910052802 copper Inorganic materials 0.000 description 3
- 239000010949 copper Substances 0.000 description 3
- 238000003384 imaging method Methods 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 229910052751 metal Inorganic materials 0.000 description 3
- 239000002184 metal Substances 0.000 description 3
- 210000000214 mouth Anatomy 0.000 description 3
- 239000011521 glass Substances 0.000 description 2
- 238000010438 heat treatment Methods 0.000 description 2
- 230000001678 irradiating effect Effects 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 description 1
- 229910052782 aluminium Inorganic materials 0.000 description 1
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 1
- 229910052790 beryllium Inorganic materials 0.000 description 1
- ATBAMAFKBVZNFJ-UHFFFAOYSA-N beryllium atom Chemical compound [Be] ATBAMAFKBVZNFJ-UHFFFAOYSA-N 0.000 description 1
- 230000008878 coupling Effects 0.000 description 1
- 238000010168 coupling process Methods 0.000 description 1
- 238000005859 coupling reaction Methods 0.000 description 1
- 239000013078 crystal Substances 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 238000009413 insulation Methods 0.000 description 1
- 239000000696 magnetic material Substances 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 230000010355 oscillation Effects 0.000 description 1
- 239000003973 paint Substances 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- 230000002441 reversible effect Effects 0.000 description 1
- 238000007789 sealing Methods 0.000 description 1
- 239000010936 titanium Substances 0.000 description 1
- 229910052719 titanium Inorganic materials 0.000 description 1
- WFKWXMTUELFFGS-UHFFFAOYSA-N tungsten Chemical compound [W] WFKWXMTUELFFGS-UHFFFAOYSA-N 0.000 description 1
- 229910052721 tungsten Inorganic materials 0.000 description 1
- 239000010937 tungsten Substances 0.000 description 1
Classifications
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/02—Constructional details
- H05G1/04—Mounting the X-ray tube within a closed housing
- H05G1/06—X-ray tube and at least part of the power supply apparatus being mounted within the same housing
Landscapes
- X-Ray Techniques (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
Description
【発明の詳細な説明】
本発明は、例えば医療用等に好適に使用し得る携帯用Ｘ
線発生装置に関するものである。DETAILED DESCRIPTION OF THE INVENTION The present invention provides a portable
This relates to a line generator.
従来、例えば由利医療において歯根のＸ線撮影を行う場
合に、Ｘ線フィルムを口腔内に入れ、外部からのＸ線照
射により透過像の撮影を行うのが＝一般的である。しか
しながら、実時間的に例えばブラウン管等で歯根の状態
を観察したり、あるいは画像の遠隔伝送を行う場合には
、この方法は不適当である。従って、このような要求が
あるときには１」腔内にＸ線を発射するＸ線管球を入れ
、外部にＸ線撮像装置を配置することが必要となるか、
唐３者に対し苦痛を与えずに、しかも電気的な安全性を
確保しながら、口腔内にＸ線管球を挿入することはなか
なか困難である。Conventionally, when performing X-ray photography of tooth roots, for example in Yuri Medical, it is common to place an X-ray film into the oral cavity and take a transmission image by irradiating X-rays from the outside. However, this method is inappropriate when observing the condition of the tooth root in real time using, for example, a cathode ray tube, or when transmitting images remotely. Therefore, when such a request is made, it is necessary to insert an X-ray tube that emits X-rays into the cavity and place an X-ray imaging device outside.
It is quite difficult to insert an X-ray tube into the oral cavity without causing pain to the patient and while ensuring electrical safety.
このような要求に対して従来から第１図に示す □よう
な医療用のＸ線発生装置ｌが知られている。To meet such demands, a medical X-ray generator l as shown in FIG. 1 has been known.
この装置は細径部の先端からＸ線を発射するＸ線管球部
２、高圧ケーブル３、高圧電源部４及び電源ケーブル５
とから構成され、Ｘ線管球部２と高圧電源部４は分離さ
れており、両者は高圧ケーブル３で接続されている。こ
の装置１は電源ケーブル５から供給される交流電源を高
圧電源部４内の高圧トランスで電圧、整ガｔしてＸ線管
球部２に必要な高電圧を供給すると共に、ヒータＩ・ラ
ンスでフィラメント電源を得て、これらの各電源を高圧
ケーブル３によりＸ線管球部２に供給している。This device consists of an X-ray tube part 2 that emits X-rays from the tip of a narrow diameter part, a high-voltage cable 3, a high-voltage power supply part 4, and a power cable 5.
The X-ray tube section 2 and the high-voltage power supply section 4 are separated, and both are connected by a high-voltage cable 3. This device 1 converts and regulates AC power supplied from a power cable 5 using a high-voltage transformer in a high-voltage power supply section 4 to supply the necessary high voltage to an X-ray tube section 2, and also supplies a heater I and a lance. A filament power source is obtained from the X-ray tube section 2, and each of these power sources is supplied to the X-ray tube section 2 through a high-voltage cable 3.
この場合、高電圧か印加する部分はそれぞれ高度に電気
的な絶縁をする必要があり、高圧電源部４と高圧ケーブ
ル３との接続部や、高圧ケーブル３自体や、高圧ケーブ
ル３とＸ線管球部２の接続部は必然的に大型となる。こ
のように、従来の装置１はＸ線管球部２と高圧電源部４
が離れた構造になっているため、高電圧の接続部か大型
でかつＸ線管球部２の後部に太い高圧ケーブル３を接続
しなければならず、診断に都合の良い個所にＸ線管球部
２を移動するのが困難となる。また、高電圧の漏電事故
が起きる可能性のある場合もあって、例えばＸ線管球部
２を口腔内に挿入した場合などに安全面において不安が
ある。In this case, the parts to which high voltage is applied must be highly electrically insulated, such as the connection part between the high voltage power supply section 4 and the high voltage cable 3, the high voltage cable 3 itself, and the high voltage cable 3 and the X-ray tube. The connecting portion of the ball portion 2 is necessarily large-sized. In this way, the conventional device 1 has an X-ray tube section 2 and a high-voltage power supply section 4.
Since the cables are separated from each other, it is necessary to connect a large high voltage cable 3 to the rear of the X-ray tube section 2, and the X-ray tube must be placed at a location convenient for diagnosis. It becomes difficult to move the ball part 2. Furthermore, there is a possibility that a high-voltage leakage accident may occur, so there is a safety concern when, for example, the X-ray tube section 2 is inserted into the oral cavity.
本発明の目的は、このような医療用の装置に安全に使用
することができ、小型で取扱いの容易な携帯用Ｘ線発生
装置を提供することにあり、その要旨は、先端からＸ線
を発射する細径部を有するＸ線管球の該細径部を除く基
体部、充電ｒＪｆ能な電池、外部から電線を接続するこ
となく外部からのエネルギを受は前記電池を充電する充
電回路、電池から供給される電圧をＡ圧し前記Ｘ線管球
に印加する高圧電源発生回路及び外部から速隔的に操作
するスイッチを絶縁体により包囲し、前記Ｘ線管球の細
径部を含む：これら全体の周囲を導電性旧料で被覆した
ことを特徴とするものである。The purpose of the present invention is to provide a portable X-ray generator that can be safely used in such medical equipment, is small and easy to handle, and its gist is to emit X-rays from the tip. A base portion of an X-ray tube other than the narrow diameter portion of an X-ray tube having a narrow diameter portion for emitting light, a battery capable of charging, and a charging circuit that charges the battery by receiving energy from the outside without connecting an electric wire from the outside. A high-voltage power generation circuit that applies A voltage supplied from a battery to the X-ray tube and a switch that is operated from the outside at rapid intervals are surrounded by an insulator, and the narrow diameter portion of the X-ray tube is included: It is characterized in that the entire periphery of these is coated with a conductive old material.
本発明を第２図以下に図示の実施例に基づいて６゛ｆ細
に説明する。The present invention will be explained in detail based on the embodiment shown in FIG. 2 and below.
第２図は本発明の実施例に好適に使用できるＸ線管球１
１の断面図であり、１２はガラスあるいは金属から成る
密±１された管体であって、直径２０〜３０ｍｍ程度の
大径部１３と、例えば直径６ｍｍ程度の細径部１４とか
ら構成されており、内部は真空又はガス入りに封じられ
ている。大径部１３の内部には電子ビームを発生するだ
めの点状のフィラメント１５が配置され、このフィラメ
ンｉ・１５にはフィラメント１５自体を加熱するだめの
電流をがＬし、更に例えば６０ｋＶ程廉の直流高電圧を
外部から供給するためのリード線１６ａ、１６ｂが接続
され、管体１２の外部に引き出されている。また、細径
部１４の先端部内には、タングステン、銅、白金等の金
属から成り、加速されて飛来してきた電子ビームをＸ線
に変換するターゲット１７が配置され、このターゲラ）
１７はアース′ｉｔ極１８に接続されている。更にこの
ターゲット１７から発射されるＸ線が通過する窓１９は
、軟Ｘ線をカントするカラス、チタン、銅等の材料で形
成されているか、必要に応じて軟Ｘ線を透過するベリリ
ウム等の材料で造ることもできる。更に細径部１４の周
囲には１個又は複数個の環状の永久磁石２０が周設され
、その位置は細径部１４に沿って適当に移動し調整し得
るようになっている。なお、２１は電源部であり、フィ
ラメント１５を加熱するためのフィラメンＩ・電源２２
と、フィラメント１５から発生した電子ビームを加速す
るだめの高圧電源２３から構成されている。FIG. 2 shows an X-ray tube 1 that can be suitably used in an embodiment of the present invention.
1, 12 is a tightly sealed tube body made of glass or metal, and is composed of a large diameter portion 13 with a diameter of approximately 20 to 30 mm and a narrow diameter portion 14 with a diameter of, for example, approximately 6 mm. The inside is sealed with a vacuum or gas. A point-shaped filament 15 that generates an electron beam is arranged inside the large diameter portion 13, and a current that heats the filament 15 itself is passed through the filament i15, and a low current of about 60 kV, for example, is applied to the filament i15. Lead wires 16a and 16b for supplying DC high voltage from the outside are connected and drawn out to the outside of the tube body 12. In addition, a target 17 made of metal such as tungsten, copper, or platinum is placed inside the tip of the narrow diameter portion 14, and converts the accelerated electron beam into X-rays.
17 is connected to the ground 'it pole 18. Furthermore, the window 19 through which the X-rays emitted from the target 17 pass is made of a material such as glass, titanium, or copper that can cant the soft X-rays, or is made of beryllium or the like that transmits the soft X-rays as necessary. It can also be made from materials. Further, one or more annular permanent magnets 20 are provided around the narrow diameter portion 14, and the position thereof can be appropriately moved and adjusted along the narrow diameter portion 14. In addition, 21 is a power supply section, and a filament I/power supply 22 for heating the filament 15 is provided.
and a high-voltage power supply 23 for accelerating the electron beam generated from the filament 15.
従って、このＸ線管球１１では先ずフィラメント電源２
２から電流を供給し、フィラメント１５を加熱するとフ
ィラメント１５からは電子ビームが発生される。続いて
高圧電源２３により高電圧を印加することにより、電子
ビームは加速され前方のターゲット１７に向かって進行
することになる。この電子ビームはターゲット１７の極
性によりターゲット１７に引き寄せられ衝突することに
なるが、単にこのままの状態ではターゲット１７の微小
面積中に集中することはできない。従って、細径部１４
の周囲に永久磁石２０を配置すると、電子ヒームは永久
磁石２０の中心軸に沿って進むために永久磁石２０の磁
力及び位置を適当に選択することにより、電子ビームを
ターゲット１７の微小面積部分に焦点を合わせて効率良
く衝突させることができる。ターゲット１７に衝突した
゛電子ビームはここでＸ線を発生させ、管体１２の窓１
９を通過して外部に散乱されることになる。Therefore, in this X-ray tube 11, first the filament power source 2
When the filament 15 is heated by supplying current from the filament 15, an electron beam is generated from the filament 15. Subsequently, by applying a high voltage from the high voltage power supply 23, the electron beam is accelerated and advances toward the target 17 in front. This electron beam is attracted to and collides with the target 17 due to the polarity of the target 17, but it cannot be concentrated in the minute area of the target 17 if it remains as it is. Therefore, the narrow diameter portion 14
When a permanent magnet 20 is placed around the target 17, the electron beam advances along the central axis of the permanent magnet 20. By appropriately selecting the magnetic force and position of the permanent magnet 20, the electron beam is directed to a minute area of the target 17. It is possible to focus and collide efficiently. The electron beam that collided with the target 17 generates X-rays, and the window 1 of the tube body 12
9 and is scattered to the outside.
なお、電子ビームの焦点合せ制御には静電式レンズを大
径＝＋＋ １３内に設けて（７１用してもよいが、］−
な制御は細径部１４の周囲に配設した永久磁石２０によ
り行うことが望ましい。この場合、永久磁石２０は外部
電源を要せず、例えば細径部１４を［」腔内に挿入して
も安全が保障される。また、永久磁石２０は細径部１４
の外部に設けられているので、管体２１を封じた後に永
久磁石２０の位置を調整することによって、電子ビーム
のターゲラ！・１７への焦点合せが容易となる利点をも
有している。In addition, to control the focusing of the electron beam, an electrostatic lens is provided within the large diameter = ++ 13 (although it is also possible to use 71) -
It is desirable that such control be performed by a permanent magnet 20 disposed around the narrow diameter portion 14. In this case, the permanent magnet 20 does not require an external power source, and safety is ensured even if the narrow diameter portion 14 is inserted into the cavity. Further, the permanent magnet 20 has a small diameter portion 14
By adjusting the position of the permanent magnet 20 after sealing the tube body 21, the electron beam can be targeted.・It also has the advantage that focusing on 17 is easy.
第３図は細径部１４を必要に応じて屈曲し、その屈曲部
２４の周囲にｔ□って永久磁石２０を配置した実施例で
あり、この場合も電子ビームは永久磁石２０により、焦
点合せをされながら屈曲部２４に沿って進み、ターゲッ
ト１７の微小面積部分に衝突させることかできる。FIG. 3 shows an embodiment in which the narrow diameter portion 14 is bent as necessary and a permanent magnet 20 is placed around the bent portion 24 at a distance of t. In this case as well, the electron beam is focused by the permanent magnet 20. It can advance along the bent portion 24 while being aligned and collide with a small area portion of the target 17.
このＸ線管球１１は高圧電源として約６０ｋＶを印加し
、フィラメント電流を１ｍＡ程度流すことにより実用性
が生じ、従来の通常のＸ線管球の１０００分の１８１度
の例えば０．１〜０．３Ｒの出力が得られる。このよう
な微小出力のＸ線管球１１であっても撮像側に例えばチ
ャンネルプレートのような晶増倍度を有する撮像装置を
配置することによりＸ線による透過像を得ることが可能
となる。This X-ray tube 11 is made practical by applying approximately 60 kV as a high-voltage power source and passing a filament current of approximately 1 mA. An output of .3R is obtained. Even with such a small output X-ray tube 11, it is possible to obtain an X-ray transmission image by arranging an imaging device having crystal multiplication, such as a channel plate, on the imaging side.
第４図は先のＸ線管球１１を使用した本発明に係る携帯
用Ｘ線発生装＃３０の実施例である。ここでＸ線管球１
１の大径部１３から成る基体部は充電可能な可逆電池３
１、高電圧発生回路３２、充電回路３３と共に、例えば
高絶縁性を４１する合成樹脂によりモールドされている
。このモールド絶縁体３４の周囲及びＸ線管球１１の細
径部１４の周囲は、金属根などの導電性材料から成り静
電シールドのできるケース３５で被覆されていて、ター
ゲット１７はケース３５に接地されている。FIG. 4 shows an embodiment of a portable X-ray generator #30 according to the present invention using the X-ray tube 11 described above. Here, X-ray tube 1
The base portion consisting of the large diameter portion 13 of 1 is a rechargeable reversible battery 3
1. Together with the high voltage generation circuit 32 and the charging circuit 33, it is molded with, for example, a synthetic resin with high insulation properties. The periphery of this molded insulator 34 and the periphery of the narrow diameter portion 14 of the X-ray tube 11 are covered with a case 35 made of a conductive material such as a metal root and capable of electrostatic shielding. Grounded.
Ｘ線管球１１は電池３１をエネルギ供給源としているが
、電池３１そのものは低電圧なので、高電圧発生回路３
２内の発振回路により交流に変換し、トランスによって
電圧して高圧電源として用いるようになっている。The X-ray tube 11 uses a battery 31 as an energy supply source, but since the battery 31 itself has a low voltage, the high voltage generation circuit 3
The oscillation circuit inside the oscillator circuit converts the voltage into alternating current, which is then converted to a voltage by a transformer and used as a high-voltage power source.
なお、ここで重要なことはこの携帯用Ｘ線発生装置３０
には外部からの接続配線が全くなく、しかも配線の接続
自体も不可能なことであり、電池３１も内部に封じ込ん
だまま交換できないようになっている。これはあくまで
も人体への安全性を考慮したものであり、電池３１を繰
り返して使用するために電池３１への充電は、第５図に
示すように充電回路３３に、コイル３６を巻回したコア
３７を用いて、外部から同様にコイル３８を巻回したコ
ア３９を近接するトランス結合により行うようになって
いる。即ちこの場合、充゛屯回路３３は内端部断面を外
方に向けたほぼＣ字状のコア３７に一二次コイル３６を
巻回したものを使用し、外部から一次コイル３８に商用
交流電流を流したコア３９の断面を近づけて固定すれば
、二次コイル３６には電圧が誘起され、発生された電流
を充電回路３３内の整流回路４０ａ、４０ｂにより整流
して電池３１に充電することができる。なお、この場合
はケース３５はアルミニウム、銅などの非磁性材料であ
ることを要する。The important thing here is that this portable X-ray generator 30
There is no connection wiring from the outside at all, and it is impossible to connect the wiring itself, and the battery 31 is also sealed inside and cannot be replaced. This is only in consideration of safety for the human body, and in order to use the battery 31 repeatedly, charging the battery 31 is performed using a core around which a coil 36 is wound around a charging circuit 33, as shown in FIG. 37, and a core 39 around which a coil 38 is similarly wound from the outside is connected to a nearby transformer. That is, in this case, the filling circuit 33 uses a primary and secondary coil 36 wound around a substantially C-shaped core 37 with the inner end cross section facing outward, and a commercial alternating current is connected to the primary coil 38 from the outside. When the cross section of the core 39 through which the current flows is brought close and fixed, a voltage is induced in the secondary coil 36, and the generated current is rectified by the rectifier circuits 40a and 40b in the charging circuit 33 to charge the battery 31. be able to. In this case, the case 35 needs to be made of a non-magnetic material such as aluminum or copper.
更にこのＸ線発生装置３０を作動させるためにはスイッ
チが必要であるが、この装置３０はフィラメント１５を
加熱するためのスイッチ４１及びフィラメント１５に高
電圧を印加するためのスイッチ４２か内蔵されている。Further, a switch is required to operate this X-ray generator 30, and this device 30 has a built-in switch 41 for heating the filament 15 and a switch 42 for applying a high voltage to the filament 15. There is.
これらのスイッチ４１．４２は、フィラメント１５の点
灯とこれへの高電圧の供給とを同時に行うようにすれば
１個で済むが、フィラメント１５の温度が十分にＡ温し
ないうちに、高電圧を印加すると人体に有害な軟Ｘ線か
発生する問題がある。ケース３５の表面に内部配線を引
き出すことは安全性に問題かあるので、スインチ４１．
４２はモールド絶縁体３４内に埋設し外部から遠隔的に
作動させることが必要である。例えば磁石の着脱などに
よって作動するリードスイッチや、あるいは第６図に示
すような光ファイバ４３を利用した光スィッチ４４を用
いることができる。この光スィッチ４４の場合は、ケー
ス３５の外表面に穴４５を開け、ここに光を透過する導
電塗料４６を埋め込み、その内側に光ファイ／へ４３の
端部を埋設しておけば、外部から変調された光を光ファ
イバ４３に供給することにより、内部の光スィッチ４４
を作動させることができる。特に高電圧供給用のスイッ
チ４２は、例えは瞬間的な動作、あるいはコマ撮りのた
めの間欠的な動作、更には連続照射をするための連絞的
に必要な時間だけ作動し続けるような動作を選択的に実
施できるスイッチが好適である。If these switches 41 and 42 are used to turn on the filament 15 and supply high voltage to it at the same time, only one switch is required, but if the high voltage is turned on before the temperature of the filament 15 is not sufficiently high. When applied, there is a problem in that soft X-rays that are harmful to the human body are generated. Since pulling out the internal wiring on the surface of the case 35 is a safety issue, the switch 41.
42 must be embedded within the mold insulator 34 and actuated remotely from the outside. For example, a reed switch operated by attaching and detaching a magnet, or an optical switch 44 using an optical fiber 43 as shown in FIG. 6 can be used. In the case of this optical switch 44, a hole 45 is made on the outer surface of the case 35, a conductive paint 46 that transmits light is embedded in the hole 45, and the end of the optical fiber/heater 43 is buried inside the hole 45. By supplying modulated light from the optical fiber 43 to the internal optical switch 44
can be operated. In particular, the high-voltage supply switch 42 may operate instantaneously, or intermittently for time-lapse photography, or may continue to operate for a required period of time for continuous irradiation. A switch that can selectively perform the following is preferable.
前述の実施例においては、Ｘ線管球１１の電子ビームの
焦点合せ制御を永久磁石２０により行うようにしたが、
大径部１３内の静電レンズにより行うようにしても支障
はない。また、モールド絶縁体３４についても合成樹脂
以外に絶縁油等を用いることもできる。電池３１への充
電の方法については、この他にも超音波を用いてその振
動エネルギーを蓄電したり、あるいは電池として太陽′
電池を用いて光を照射することにより充電を行うとか、
ピエゾトランスを用いることも可能である。In the embodiment described above, the focusing control of the electron beam of the X-ray tube 11 was performed by the permanent magnet 20.
There is no problem even if the electrostatic lens in the large diameter portion 13 is used. Further, for the mold insulator 34, insulating oil or the like can also be used instead of synthetic resin. There are other ways to charge the battery 31, such as using ultrasonic waves to store the vibration energy, or using solar power as a battery.
Charging by irradiating light with a battery, etc.
It is also possible to use a piezo transformer.
このＸ線発生袋側３０では、ケース３５がターゲット１
７などの接地電位となるためにケース３５が高電圧にな
ることがなく、高電圧の漏洩による衝撃を店、渚に与え
るおそれは全くない。従って、このような状態でスイッ
チ４１．４２を作動させれば、クーケラ）１７からはＸ
線が出力され、歯科医療の歯根の透過像等を容易に観察
したり撮影することが可能となる。なお、スインチの作
動状態、電池の充電状態の確認を装置３０に設けたＵＥ
Ｄにより行うこともできる。On this X-ray generation bag side 30, the case 35 is the target 1
Since the case 35 is at a ground potential such as 7, the voltage will not become high, and there is no risk of impact on the store or beach due to high voltage leakage. Therefore, if switches 41 and 42 are operated in this state, X
Lines are output, making it possible to easily observe and photograph transmission images of tooth roots in dental care. In addition, the UE is equipped with a device 30 that checks the operating state of the switch and the charging state of the battery.
D can also be used.
第１図は従来のＸ線発生装置の構成図、第２図以ドは本
発明に係る携帯用Ｘ線発生装置の実施例を＞１＜ Ｌ
、第２図はＸ線管球の断面図、第３図はその細径Ｂ１３
を屈曲した状態の側面図１第４図はＸ線発生装置の構成
図、第５図はトランス結合により充電する場合の構成図
、第６図は光スィッチの構成図でああ。
袷号１１はＸ線管球、１２は管体、１３は大径部、１４
は細径部、１５はフィラメント、１７はターゲニント、
２０は永久磁石、２１は電源部、２２は２イラメント電
源、２３は高圧電源、３０は携帯用Ｘ線発生装置、３１
は電池、３２は高電圧発生回路、３３は充電回路、３４
はモールド絶縁体、３５はケース、３６はコイル、３７
はコア、４１．４２はスイッチ、４３は光ファイバ、４
４は光スィッチである。
特許出願人 アロ カ株式会社
第１図
泥３０
第４図
第５図
第６図
４Fig. 1 is a block diagram of a conventional X-ray generator, and Fig. 2 and subsequent figures show an embodiment of a portable X-ray generator according to the present invention.
, Figure 2 is a cross-sectional view of the X-ray tube, and Figure 3 is its small diameter B13.
Figure 4 is a configuration diagram of the X-ray generator, Figure 5 is a configuration diagram for charging by transformer coupling, and Figure 6 is a configuration diagram of an optical switch. 11 is the X-ray tube, 12 is the tube body, 13 is the large diameter part, 14
15 is a filament, 17 is a target,
20 is a permanent magnet, 21 is a power supply unit, 22 is a 2-illament power supply, 23 is a high voltage power supply, 30 is a portable X-ray generator, 31
is a battery, 32 is a high voltage generation circuit, 33 is a charging circuit, 34
is a molded insulator, 35 is a case, 36 is a coil, 37
is the core, 41.42 is the switch, 43 is the optical fiber, 4
4 is a light switch. Patent applicant: Aloka Co., Ltd. Figure 1 Doro 30 Figure 4 Figure 5 Figure 6 Figure 4
Claims (1)
該細径部を除く基体部、充電可能な電池、外部から電線
を接続することなく外部からのエネルギを受は前記電池
を充電する充電回路、電池から供給される電圧をＡ圧し
前記Ｘ線管球に印加する高圧電源発生回路及び外部から
遠隔的に操作するスイッチを絶縁体により包囲し、前記
Ｘ線管球の細径部を含むこれら全体の周囲を導電性材料
で被覆したことを特徴とする携帯用Ｘ線発生装置。 ２、前記充電回路には一次コイルを巻回したコアを設け
、−次コイルを巻回し電流を通電したコアを外部から近
接してトランス結合するようにした特許請求の範囲第１
項記載の携帯用Ｘ線発生装置ざ１゜ ３、 前記スイッチはリードスイッチとし、外部から磁
石の着脱により作動させるようにした特許請求の範囲第
１項記載、の携帯用Ｘ線発生装置。 ４、 前記スイッチは光ファイバを接続した光スィッチ
とし、外部から光を供給することにより作動させるよう
にした特許請求の範囲第１項記載の携帯用Ｘ線発生装置
。[Scope of Claims] 1. A base portion of an X-ray tube other than the narrow diameter portion of an X-ray tube having a narrow diameter portion that emits X-rays from the tip, a rechargeable battery, and an The energy receiving circuit surrounds, with an insulator, a charging circuit that charges the battery, a high-voltage power generation circuit that converts the voltage supplied from the battery into A voltage and applies it to the X-ray tube, and a switch that is remotely operated from the outside. A portable X-ray generator characterized in that the entire periphery of the X-ray tube including its narrow diameter portion is covered with a conductive material. 2. The charging circuit is provided with a core around which a primary coil is wound, and the core, which is wound with a secondary coil and energized with current, is closely connected to the outside by a transformer.
1.3. The portable X-ray generator according to claim 1, wherein the switch is a reed switch and is activated by attaching and detaching a magnet from the outside. 4. The portable X-ray generator according to claim 1, wherein the switch is an optical switch connected to an optical fiber, and is activated by supplying light from the outside.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57027237A JPS58145098A (en) | 1982-02-22 | 1982-02-22 | Portable x-ray generator |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57027237A JPS58145098A (en) | 1982-02-22 | 1982-02-22 | Portable x-ray generator |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS58145098A true JPS58145098A (en) | 1983-08-29 |
| JPS6352760B2 JPS6352760B2 (en) | 1988-10-20 |
Family
ID=12215457
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP57027237A Granted JPS58145098A (en) | 1982-02-22 | 1982-02-22 | Portable x-ray generator |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS58145098A (en) |
Cited By (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS63299100A (en) * | 1986-05-15 | 1988-12-06 | ザイ・テック・インク | Method of forming x-ray image of x-ray transmission and radiation photographing and hand-carry type diagnosis apparatus employing the method |
| FR2685545A1 (en) * | 1991-12-19 | 1993-06-25 | Godfroy Jean Pierre | Emission head for a flash-radiography apparatus |
| US5442677A (en) * | 1993-10-26 | 1995-08-15 | Golden; John | Cold-cathode x-ray emitter and tube therefor |
| JP2001224579A (en) * | 2000-02-15 | 2001-08-21 | Hitachi Medical Corp | X-ray equipment |
| US6289079B1 (en) | 1999-03-23 | 2001-09-11 | Medtronic Ave, Inc. | X-ray device and deposition process for manufacture |
| US6353658B1 (en) | 1999-09-08 | 2002-03-05 | The Regents Of The University Of California | Miniature x-ray source |
| US6799075B1 (en) | 1995-08-24 | 2004-09-28 | Medtronic Ave, Inc. | X-ray catheter |
| JP2006520068A (en) * | 2003-02-20 | 2006-08-31 | インフォ，インク． | Integrated X-ray source module |
| CN104812153A (en) * | 2014-01-28 | 2015-07-29 | 西门子公司 | X-ray tube unit |
| CN106104745A (en) * | 2014-03-05 | 2016-11-09 | 昂达博思有限公司 | X ray generator |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP6792519B2 (en) | 2017-06-07 | 2020-11-25 | 浜松ホトニクス株式会社 | X-ray generator |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5039886A (en) * | 1973-07-09 | 1975-04-12 |
-
1982
- 1982-02-22 JP JP57027237A patent/JPS58145098A/en active Granted
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5039886A (en) * | 1973-07-09 | 1975-04-12 |
Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS63299100A (en) * | 1986-05-15 | 1988-12-06 | ザイ・テック・インク | Method of forming x-ray image of x-ray transmission and radiation photographing and hand-carry type diagnosis apparatus employing the method |
| FR2685545A1 (en) * | 1991-12-19 | 1993-06-25 | Godfroy Jean Pierre | Emission head for a flash-radiography apparatus |
| US5442677A (en) * | 1993-10-26 | 1995-08-15 | Golden; John | Cold-cathode x-ray emitter and tube therefor |
| US6799075B1 (en) | 1995-08-24 | 2004-09-28 | Medtronic Ave, Inc. | X-ray catheter |
| US6289079B1 (en) | 1999-03-23 | 2001-09-11 | Medtronic Ave, Inc. | X-ray device and deposition process for manufacture |
| US6353658B1 (en) | 1999-09-08 | 2002-03-05 | The Regents Of The University Of California | Miniature x-ray source |
| JP2001224579A (en) * | 2000-02-15 | 2001-08-21 | Hitachi Medical Corp | X-ray equipment |
| JP2006520068A (en) * | 2003-02-20 | 2006-08-31 | インフォ，インク． | Integrated X-ray source module |
| CN104812153A (en) * | 2014-01-28 | 2015-07-29 | 西门子公司 | X-ray tube unit |
| US9842720B2 (en) | 2014-01-28 | 2017-12-12 | Siemens Aktiengesellschaft | X-ray tube unit |
| CN104812153B (en) * | 2014-01-28 | 2018-03-27 | 西门子公司 | X-ray radiator |
| CN106104745A (en) * | 2014-03-05 | 2016-11-09 | 昂达博思有限公司 | X ray generator |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS6352760B2 (en) | 1988-10-20 |
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