JPS6352760B2 - - Google Patents
Info
- Publication number
- JPS6352760B2 JPS6352760B2 JP57027237A JP2723782A JPS6352760B2 JP S6352760 B2 JPS6352760 B2 JP S6352760B2 JP 57027237 A JP57027237 A JP 57027237A JP 2723782 A JP2723782 A JP 2723782A JP S6352760 B2 JPS6352760 B2 JP S6352760B2
- Authority
- JP
- Japan
- Prior art keywords
- switch
- ray tube
- outside
- target
- battery
- 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
- 238000010894 electron beam technology Methods 0.000 claims description 13
- 239000004020 conductor Substances 0.000 claims description 5
- 239000011521 glass Substances 0.000 claims description 4
- 239000012777 electrically insulating material Substances 0.000 claims description 3
- 235000014676 Phragmites communis Nutrition 0.000 claims description 2
- 239000000615 nonconductor Substances 0.000 claims description 2
- 239000003973 paint Substances 0.000 claims description 2
- 210000000214 mouth Anatomy 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- 239000012212 insulator Substances 0.000 description 4
- 230000003287 optical effect Effects 0.000 description 4
- 239000013307 optical fiber Substances 0.000 description 4
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 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
- 238000000034 method Methods 0.000 description 3
- 230000008878 coupling Effects 0.000 description 2
- 238000010168 coupling process Methods 0.000 description 2
- 238000005859 coupling reaction Methods 0.000 description 2
- 238000010438 heat treatment Methods 0.000 description 2
- 230000001678 irradiating effect Effects 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 229910052751 metal Inorganic materials 0.000 description 2
- 239000002184 metal Substances 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- 238000010248 power generation Methods 0.000 description 2
- 229920003002 synthetic resin Polymers 0.000 description 2
- 239000000057 synthetic resin Substances 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
- 238000005452 bending Methods 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
- 230000005540 biological transmission Effects 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
- 230000010355 oscillation Effects 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- 230000002441 reversible effect Effects 0.000 description 1
- 230000035939 shock Effects 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)
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 relates to a portable X-ray generator that can be suitably used for medical purposes, for example.
従来、例えば歯科医療において歯根のX線撮影
を行う場合に、X線フイ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。従つて、このような要求があるとき
には口腔内に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
が、患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。 BACKGROUND ART Conventionally, for example, when performing X-ray photography of tooth roots in dentistry, it is common to insert 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 tooth roots 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 oral cavity and place an X-ray imaging device outside, but this can be done without causing pain to the patient. Moreover, it is quite difficult to insert an X-ray tube into the oral cavity 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1が知られている。
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
高圧トランスで昇圧、整流してX線管球部2に必
要な高電圧を供給すると共に、ヒータトランスで
フイ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。
この場合、高電圧が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
なつているため、高電圧の接続部が大型でかつ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つて、
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 response to such demands, a medical X-ray generator 1 as shown in FIG. 1 has been known.
This device is composed of an X-ray tube section 2 that emits X-rays from the tip of a narrow diameter section, a high-voltage cable 3, a high-voltage power supply section 4, and a power supply cable 5. They are separated, and both are connected by a high voltage cable 3. This device 1 boosts and rectifies 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 filament power supply using a heater transformer. These power sources are supplied to the X-ray tube section 2 through a high-voltage cable 3.
In this case, each part to which high voltage is applied needs to be highly electrically insulated, and the high voltage power supply section 4
and the connection between the high voltage cable 3 and the high voltage cable 3.
The device itself and the connecting portion between the high-voltage cable 3 and the X-ray tube section 2 are necessarily large-sized. As described above, since the conventional device 1 has a structure in which the X-ray tube section 2 and the high-voltage power supply section 4 are separated, the high-voltage connection section is large and the
A thick high-voltage cable 3 must be connected to the rear of the X-ray tube section 2, making it difficult to move the X-ray tube section 2 to a convenient location for diagnosis. In addition, there are cases where there is a possibility of high voltage leakage accidents.
For example, when the X-ray tube section 2 is inserted into the oral cavity, there is a safety concern.
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
掲帯用X線発生装置を提供することにあり、その
要旨は、電子ビームを通過させる細径部の先端部
に導電性のターゲツトを内設し該ターゲツトから
X線を発射するガラス製のX線管球の前記細径部
を除く基体部、充電可能な電池、外部のエネルギ
供給源から電気絶縁体を介してエネルギを受け前
記電池を充電する充電回路、前記電池から供給さ
れる電圧を昇圧し前記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可能なスイ
ツチを電気絶縁物質により一体的に包囲し、前記
X線管球の細径部を含むこれら全体の周囲を導電
性材料で完全に被覆し、前記ターゲツトを該導電
性材料に電気的に接続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 the gist thereof is to A glass X-ray tube has an electrically conductive target at the tip of its narrow diameter section and emits X-rays from the target, and includes a base section other than the narrow diameter section, a rechargeable battery, and an external energy supply. a charging circuit that receives energy from a source via an electrical insulator and charges the battery; a high-voltage power generation circuit that boosts the voltage supplied from the battery and applies it to the X-ray tube; and a high-voltage power generation circuit that can be remotely operated from the outside. The switch is integrally surrounded by an electrically insulating material, the entire circumference of the X-ray tube including the narrow diameter portion is completely covered with a conductive material, and the target is electrically connected to the conductive material. It is characterized by this.
本発明を第2図以下に図示の実施例に基づいて
詳細に説明する。 The present invention will be explained in detail based on the embodiments 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11の断面図であり、12はガラス製の密
封された管体であつて、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
を発生するための点状のフイラメント15が配置
され、このフイラメント15にはフイラメント1
5自体を加熱するための電流を流し、更に例えば
60kV程度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ツト17が配置され、この
ターゲツト17はアース電極18に接続されてい
る。更にこのターゲツト17から発射されるX線
が通過する窓19は、軟X線をカツトするガラ
ス、チタン、銅等の材料で形成されているが、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。更に細経部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に沿つて適当に移動し
調整し得るようになつている。なお、21は電源
部であり、フイラメント15を加熱するためのフ
イラメント電源22と、フイラメント15から発
生した電子ビームを加速するための高圧電源23
から構成されている。 FIG. 2 shows X which can be suitably used in the embodiment of the present invention.
It is a cross-sectional view of the wire tube 11, and 12 is a sealed tube made of glass, and is composed of a large diameter part 13 with a diameter of about 20 to 30 mm and a small diameter part 14 with a diameter of about 6 mm, for example. The inside is sealed with a vacuum or gas. A dot-shaped filament 15 for generating an electron beam is arranged inside the large diameter portion 13, and the filament 1
A current is applied to heat the 5 itself, and further e.g.
Lead wires 16a and 16b for supplying DC high voltage of about 60kV from the outside are connected, and the pipe body 12
being pulled out of the Further, a target 17 made of metal such as tungsten, copper, or platinum is arranged inside the tip of the narrow diameter portion 14 and converts the accelerated electron beam into X-rays. It is connected to the. 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 blocks soft X-rays, but may be made of beryllium or the like that transmits soft X-rays as necessary. It can also be made from materials. Further, one or more annular permanent magnets 20 are disposed around the narrow diameter section 14, and the position thereof can be appropriately moved and adjusted along the narrow diameter section 14. In addition, 21 is a power supply part, which includes a filament power supply 22 for heating the filament 15 and a high voltage power supply 23 for accelerating the electron beam generated from the filament 15.
It consists of
従つて、このX線管球11では先ずフイラメン
ト電源22から電流を供給し、フイラメント15
を加熱するとフイラメント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
方のターゲツト17に向かつて進行することにな
る。この電子ビームはターゲツト17の極性によ
りターゲツト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ツト17
の微小面積中に集中することはできない。従つ
て、細径部14の周囲に永久磁石20を配置する
と、電子ビームは永久磁石20の中心軸に沿つて
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ツト1
7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。ターゲツト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19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, a current is supplied from the filament power source 22, and the filament 15 is supplied with current.
When heated, 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 will be attracted to the target 17 depending on the polarity of the target 17, and will collide with it.
cannot be concentrated in a very small area. Therefore, when the permanent magnet 20 is arranged around the narrow diameter portion 14, the electron beam can be moved along the central axis of the permanent magnet 20 by appropriately selecting the magnetic force and position of the permanent magnet 20. Target 1
It is possible to focus on a minute area portion of 7 and cause the collision to occur efficiently. The electron beam colliding with the target 17 generates X-rays, which pass through the window 19 of the tube body 12 and are scattered to the outside.
なお、電子ビームの焦点合せ制御には静電式レ
ンズを大径部13内に設けて併用してもよいが、
主な制御は細径部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
を口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つて、電子ビームのターゲ
ツト17への焦点合せが容易となる利点をも有し
ている。 Note that an electrostatic lens may be provided in the large diameter portion 13 and used in combination to control the focusing of the electron beam.
It is desirable that the main control is performed by the 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, for example, the small diameter portion 14
Safety is guaranteed even when inserted into the oral cavity. Also,
Since the permanent magnet 20 is provided outside the narrow diameter portion 14, the electron beam can be easily focused on the target 17 by adjusting the position of the permanent magnet 20 after the tube body 21 is sealed. It also has advantages.
第3図は細径部14を必要に応じて屈曲し、そ
の屈曲部24の周囲に沿つて永久磁石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2
4に沿つて進み、ターゲツト17の微小面積部分
に衝突させることができる。 FIG. 3 shows an embodiment in which the narrow diameter portion 14 is bent as necessary and a permanent magnet 20 is arranged along the periphery of the bent portion 24. In this case as well, the electron beam is focused by the permanent magnet 20. bending part 2 while
4, and can 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、フイラメント電流を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1程度の例えば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であつ
ても撮像側に例えばチヤンネルプレートのような
高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 supply and passing a filament current of approximately 1 mA, and is different from the conventional ordinary X-ray tube.
An output of about 1/1000, for example 0.1 to 0.3R, can be obtained. Even with such a small output X-ray tube 11, it is possible to obtain an X-ray transmitted image by arranging an imaging device with high 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線発生装置30の実施例である。こ
こでX線管球11の大径部13から成る基本部は
充電可能な可逆電池31、高電圧発生回路32、
充電回路33と共に、例えば高絶縁性を有する合
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、金属板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、
ターゲツト17はケース35に接地されている。
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32内の発振回路により交流に変換
し、トランスによつて昇圧して高圧電源として用
いるようになつている。 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, the basic part consisting of the large diameter part 13 of the X-ray tube 11 includes a rechargeable reversible battery 31, a high voltage generation circuit 32,
Together with the charging circuit 33, it is molded with, for example, a synthetic resin having high insulation properties. The periphery of this molded insulator 34 and the narrow diameter portion 14 of the X-ray tube 11
The surrounding area is covered with a case 35 made of a conductive material such as a metal plate and capable of electrostatic shielding.
The target 17 is grounded to the case 35.
The X-ray tube 11 uses a battery 31 as an energy supply source, but since the battery 31 itself has a low voltage, it is converted to alternating current by an oscillation circuit in a high voltage generation circuit 32, and then boosted by a transformer to be used as a high voltage power source. It's becoming like that.
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
なつている。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、物理的及び電気
的に外部のエネルギ供給源と非接触な状態で行
い、例えば第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つている。即
ちこの場合、充電回路33は両端部断面を外方に
向けたほぼC字状のコア37に二次コイル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。 What is important here is that this portable X-ray generator 30 has no external connection wiring, and it is impossible to connect the wiring at all, so the battery 31 can be replaced while still being sealed inside. It has become impossible to do so. This is done in consideration of human safety, and in order to use the battery 31 repeatedly, the battery 31 is charged without physical or electrical contact with an external energy supply source. For example, as shown in FIG. 5, in the charging circuit 33,
Using a core 37 around which a coil 36 is wound, a core 39 around which a coil 38 is similarly wound is connected from the outside by adjacent transformer coupling. That is, in this case, the charging circuit 33 uses a core 37 having a substantially C-shape with both ends facing outward, and a secondary coil 36 wound around the core 37.
When the cross-section of the core 39 through which a commercial alternating current is passed is fixed close to the secondary coil 36, 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, and the battery 31 can be charged 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
はスイツチが必要であるが、この装置30はフイ
ラメント15を加熱するためのスイツチ41及び
フイラメント15に高電圧を印加するためのスイ
ツチ42が内蔵されている。これらのスイツチ4
1,42は、フイラメント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、フイラメント15の温度が十分に昇温し
ないうちに、高電圧を印加すると人体に有害な軟
X線が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があるの
で、スイツチ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。例えば磁場を与えることによつて作動す
るリードスイツチや、あるいは第6図に示すよう
な光フアイバ43を利用した光スイツチ44を用
いることができる。この光スイツチ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
に光フアイバ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アイバ43に供給するこ
とにより、内部の光スイツチ44を作動させるこ
とができる。特に高電圧供給用のスイツチ42
は、例えば瞬間的な動作、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
連続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ツチが好適である。 Furthermore, 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 high voltage to the filament 15. There is. These switches 4
If the filament 15 is turned on and the high voltage is supplied to it at the same time, only one 1 and 42 is required, but if high voltage is applied before the temperature of the filament 15 has risen sufficiently, it may cause damage to the human body. There is a problem that harmful soft X-rays are generated. Since it is a safety problem to draw out the internal wiring on the surface of the case 35, the switches 41 and 42 need to be buried in the molded insulator 34 and operated remotely from the outside. For example, a reed switch operated by applying a magnetic field 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, if 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 43 is buried inside the hole 45, it can be modulated from the outside. By supplying the light to the optical fiber 43, the internal optical switch 44 can be operated. switch 42 especially for high voltage supply
For example, it is preferable to use a switch that can selectively perform instantaneous operation, intermittent operation for time-lapse shooting, or continuous operation for only the necessary time for continuous irradiation. be.
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
ルギーを畜電したり、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 above-described embodiment, the focusing control of the electron beam of the X-ray tube 11 was performed by the permanent magnet 20, but there is no problem if the focusing control is performed by an electrostatic lens in the large diameter portion 13. Further, for the mold insulator 34, insulating oil or the like can also be used instead of synthetic resin. Other methods of charging the battery 31 include storing the vibrational energy using ultrasonic waves, charging by irradiating light with a solar cell as a battery, and using a piezo transformer. It is also possible to use
このX線発生装置30では、ケース35がター
ゲツト17などの接地電位となるためにケース3
5が高電圧になることがなく、高電圧の漏洩によ
る衝撃を患者に与えるおそれは全くない。従つ
て、このような状態でスイツチ41,42を作動
させれば、ターゲツト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。また、電池は充電
可能であるため、電池着脱機構等を設ける必要は
なく装置構成が単純となり、充電方法も非接触で
行う方法を採用しているので、ケース35には電
極端子等を設けず極めて安全性が高い。なお、ス
イツチの作動状態、電池の充電状態の確認を装置
30に設けたLEDにより行うこともできる。 In this X-ray generator 30, since the case 35 is at the ground potential of the target 17, etc.
5 does not become a high voltage, and there is no risk of shock to the patient due to high voltage leakage. Therefore, if the switches 41 and 42 are operated in such a state, X-rays are output from the target 17, making it possible to easily observe or photograph a transmitted image of the tooth root for dental treatment. In addition, since the battery is rechargeable, there is no need to provide a battery attachment/detachment mechanism, and the device configuration is simple. Also, since a non-contact charging method is adopted, the case 35 does not have electrode terminals, etc. Extremely safe. Note that the operating state of the switch and the charging state of the battery can also be confirmed using the LED provided in the device 30.
第1図は従来のX線発生装置の構成図、第2図
以下は本発明に係る携帯用X線発生装置の実施例
を示し、第2図はX線管球の断面図、第3図はそ
の細径部を屈曲した状態の側面図、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図は光スイツチの構
成図である。
符号11はX線管球、12は管体、13は大径
部、14は細径部、15はフイラメント、17は
ターゲツト、20は永久磁石、21は電源部、2
2はフイラメント電源、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はスイツチ、43は光フアイバ、44
は光スイツチである。
Fig. 1 is a block diagram of a conventional X-ray generator, Fig. 2 and the following show an embodiment of a portable X-ray generator according to the present invention, Fig. 2 is a cross-sectional view of an X-ray tube, and Fig. 3 4 is a configuration diagram of the X-ray generator, FIG. 5 is a configuration diagram for charging by transformer coupling, and FIG. 6 is a configuration diagram of an optical switch. . 11 is an X-ray tube, 12 is a tube body, 13 is a large diameter part, 14 is a small diameter part, 15 is a filament, 17 is a target, 20 is a permanent magnet, 21 is a power supply part, 2
2 is a filament 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 are switches, 43 is an optical fiber, 44
is a light switch.
Claims (1)
電性のターゲツトを内設し該ターゲツトからX線
を発射するガラス製のX線管球の前記細径部を除
く基体部、充電可能な電池、外部のエネルギ供給
源から電気絶縁体を介してエネルギを受け前記電
池を充電する充電回路、前記電池から供給される
電圧を昇圧し前記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可能なスイツチ
を電気絶縁物質により一体的に包囲し、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
料で完全に被覆し、前記ターゲツトを該導電性材
料に電気的に接続したことを特徴とする携帯用X
線発生装置。 2 前記充電回路には二次コイルを巻回したコア
を設け、一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。 3 前記スイツチはリードスイツチとし、外部か
ら磁場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。 4 前記スイツチは光スイツチとし、外部からの
光を導電塗料、電気絶縁物質を介して受けること
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 body excluding the narrow diameter part of a glass X-ray tube that has a conductive target inside the tip of the narrow diameter part through which the electron beam passes and emits X-rays from the target. a rechargeable battery, a charging circuit that receives energy from an external energy source via an electrical insulator and charges the battery, and a high-voltage power source that boosts the voltage supplied from the battery and applies it to the X-ray tube. A generator circuit and a switch that can be operated remotely from the outside are integrally surrounded by an electrically insulating material, and the entire periphery of the X-ray tube, including the narrow diameter part, is completely covered with a conductive material, and the target is is electrically connected to the conductive material.
Line generator. 2. The portable device according to claim 1, wherein the charging circuit is provided with a core around which a secondary coil is wound, and the core around which the primary coil is wound and current is passed through is transformer-coupled in close proximity from the outside. X-ray generator. 3. The portable X-ray generator according to claim 1, wherein the switch is a reed switch and is activated by supplying a magnetic field from outside. 4. Claim 1, wherein the switch is a light switch, and is activated by receiving light from the outside through a conductive paint or an electrically insulating material.
The portable X-ray generator described in Section 1.
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 JPS58145098A (en) | 1983-08-29 |
JPS6352760B2 true 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 (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11039526B2 (en) | 2017-06-07 | 2021-06-15 | Hamamatsu Photonics K.K. | X-ray generation device |
Families Citing this family (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0247758B1 (en) * | 1986-05-15 | 1992-10-07 | Xi Tec, Inc. | Method for production of fluoroscopic and radiographic x-ray images and hand held diagnostic apparatus incorporating the same |
FR2685545B1 (en) * | 1991-12-19 | 1994-03-18 | Godfroy Jean Pierre | TRANSMISSION HEAD FOR LIGHT RADIOGRAPHY APPARATUS. |
US5442677A (en) * | 1993-10-26 | 1995-08-15 | Golden; John | Cold-cathode x-ray emitter and tube therefor |
WO1997007740A1 (en) | 1995-08-24 | 1997-03-06 | Interventional Innovations Corporation | 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 |
US7448802B2 (en) * | 2002-02-20 | 2008-11-11 | Newton Scientific, Inc. | Integrated X-ray source module |
DE102014201514B4 (en) * | 2014-01-28 | 2021-09-16 | Siemens Healthcare Gmbh | X-ray tube |
GB2523796A (en) * | 2014-03-05 | 2015-09-09 | Adaptix Ltd | 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 (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11039526B2 (en) | 2017-06-07 | 2021-06-15 | Hamamatsu Photonics K.K. | X-ray generation device |
Also Published As
Publication number | Publication date |
---|---|
JPS58145098A (en) | 1983-08-29 |
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