JPH08215210A - Medical laser probe and manufacture thereof - Google Patents
Medical laser probe and manufacture thereofInfo
- Publication number
- JPH08215210A JPH08215210A JP7028087A JP2808795A JPH08215210A JP H08215210 A JPH08215210 A JP H08215210A JP 7028087 A JP7028087 A JP 7028087A JP 2808795 A JP2808795 A JP 2808795A JP H08215210 A JPH08215210 A JP H08215210A
- Authority
- JP
- Japan
- Prior art keywords
- core material
- tubular
- laser probe
- tubular member
- molded body
- 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
Landscapes
- Laser Surgery Devices (AREA)
- Radiation-Therapy Devices (AREA)
Abstract
Description
【発明の詳細な説明】Detailed Description of the Invention
【０００１】[0001]
【産業上の利用分野】本発明は、内科や外科医療におい
て使用される医療用レーザープローブないし探針の製造
方法に関するものである。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a method for manufacturing a medical laser probe or probe used in internal medicine and surgery.
【０００２】[0002]
【従来の技術】最近、光ファイバーを介して生体器官の
組織にレーザーを照射し、組織に直接接触し、組織を切
開する、接触型のレーザー照射装置が実用化されてい
る。この装置においては、光ファイバーの先端にレーザ
ープローブを接続し、このレーザープローブの先端から
ＹＡＧレーザー、Ａｒレーザー等のレーザー光線を照射
して、生体器官の組織の切開や凝血を行う。このレーザ
ープローブは、従来、人造の単結晶サファイアによって
形成されていることが多かった。即ち、単結晶サファイ
アのロッドやパイプを製作し、このロッドやパイプを研
磨加工することによって、所望の形状のレーザープロー
ブを製作していた。レーザープローブの形状は多岐にわ
たり、例えば、フック、チーゼル、コニカル、カーブ等
に大別されるが、患部の形態に合わせるために、細かく
は千差万別の形状を持っている。2. Description of the Related Art Recently, a contact-type laser irradiation apparatus has been put into practical use, which irradiates a tissue of a living organ with a laser beam through an optical fiber, directly contacts the tissue, and incises the tissue. In this device, a laser probe is connected to the tip of an optical fiber, and a laser beam such as a YAG laser or an Ar laser is irradiated from the tip of the laser probe to perform incision or coagulation of tissue of a living organ. Conventionally, this laser probe has often been formed of artificial single crystal sapphire. That is, a single crystal sapphire rod or pipe is manufactured, and the rod or pipe is polished to manufacture a laser probe having a desired shape. The laser probe has a wide variety of shapes including, for example, hooks, chisels, conicals, curves, and the like. However, the laser probes have various shapes to suit the shape of the affected area.
【０００３】[0003]
【発明が解決しようとする課題】しかし、単結晶サファ
イアのロッドやパイプを研磨加工してレーザープローブ
を作成しようとしても、こうした微細な研磨加工で種々
雑多な形状を作りだすことは困難である。特に、フック
形状の場合には、プローブの先端を鉤爪状に湾曲させる
必要があるが、こうした形状を研磨加工によって形成す
ることは困難であった。しかも、このような研磨加工は
大量生産には不向きであり、コストが高い。また、単結
晶サファイアは、結晶軸が揃っていることから、機械的
強度が低く、熱衝撃強度が低い。レーザープローブの先
端は例えば７００〜８００℃程度にまで加熱されるの
で、特に高温時の強度が弱いために先端が折れるおそれ
もあり、問題である。However, even if an attempt is made to grind a rod or pipe of single crystal sapphire to make a laser probe, it is difficult to make various shapes by such fine grinding. In particular, in the case of a hook shape, it is necessary to bend the tip of the probe into a claw shape, but it was difficult to form such a shape by polishing. Moreover, such polishing is not suitable for mass production, and the cost is high. Further, single crystal sapphire has low mechanical strength and low thermal shock strength because the crystal axes are aligned. Since the tip of the laser probe is heated to, for example, about 700 to 800 ° C., the tip may be broken due to its weak strength especially at high temperature, which is a problem.
【０００４】本発明の課題は、高温時の熱衝撃強度が高
く、種々の形状、特にフック形状のレーザープローブを
容易に製造することができ、製造コストを低くすること
ができるようにすることである。An object of the present invention is to make it possible to easily manufacture laser probes of various shapes, particularly hook shapes, which have a high thermal shock strength at high temperature and can reduce the manufacturing cost. is there.
【０００５】[0005]
【課題を解決するための手段】本発明は、透光性セラミ
ックス製の芯材と透光性セラミックス製の管状部材とか
らなり、芯材が管状部材の内部空間に挿入されており、
この管状部材の焼成時の収縮による圧縮応力によって芯
材が管状部材に対して結合されていることを特徴とす
る、医療用レーザープローブに係るものである。The present invention comprises a core material made of translucent ceramics and a tubular member made of translucent ceramics, and the core material is inserted into the internal space of the tubular member,
The present invention relates to a medical laser probe, wherein the core material is bonded to the tubular member by a compressive stress due to shrinkage of the tubular member during firing.
【０００６】また、本発明は、透光性セラミックス製の
医療用レーザープローブを製造する方法であって、芯材
の成形体を焼成し、この焼成体の少なくとも一方の端面
を研磨加工して芯材を得、この芯材を一方の端面側から
管状成形体または管状仮焼体の内部空間に挿入し、次い
で管状成形体または管状仮焼体を焼成して管状部材を
得、管状成形体または管状仮焼体の焼成収縮によって管
状部材と芯材とを結合することを特徴とする、医療用レ
ーザープローブの製造方法に係るものである。Further, the present invention is a method for producing a medical laser probe made of translucent ceramics, wherein a molded body of a core material is fired, and at least one end surface of the fired body is ground to form a core. A material is obtained, this core material is inserted into the internal space of the tubular molded body or the tubular calcined body from one end surface side, and then the tubular molded body or the tubular calcined body is fired to obtain a tubular member, or the tubular molded body or The present invention relates to a method for manufacturing a medical laser probe, characterized in that the tubular member and the core material are joined together by firing shrinkage of the tubular calcined body.
【０００７】[0007]
【作用】本発明者は、種々の材質を検討すると共に、そ
の加工方法について種々検討してきたが、その過程で、
透光性セラミックス、特に純度９９％以上の高純度アル
ミナによってレーザープローブを形成することに着目し
た。こうした素材は、特にレーザープローブの使用温度
領域においてきわめて熱衝撃強度が高い。特に透光性多
結晶アルミナはＹＡＧレーザーの波長１．０６μｍのレ
ーザー光を通過させて、プローブの先端を赤熱させるの
に、きわめて適していた。The present inventor has studied various materials and various processing methods, and in the process,
Attention was paid to the formation of the laser probe by using the translucent ceramics, particularly high-purity alumina having a purity of 99% or more. These materials have extremely high thermal shock strength, especially in the operating temperature range of the laser probe. In particular, the translucent polycrystalline alumina was extremely suitable for allowing the laser light of the YAG laser having a wavelength of 1.06 μm to pass therethrough and causing the tip of the probe to glow red.
【０００８】しかも、レーザープローブを一体のものと
して製造するのではなく、管状成形体と芯材の成形体と
を別個に押し出し成形し、芯材の成形体を焼成し、この
焼成体の両端面を研磨加工して芯材を得、この芯材を管
状成形体または管状仮焼体の内部空間に挿入し、管状成
形体または管状仮焼体を焼成して管状部材を得、管状成
形体の焼成収縮によって管状部材と芯材とを結合した。
この方法によれば、押し出し製法によって各成形体を製
造できるので、大量生産に適しており、製造コストを大
きく減少させることができる。Moreover, instead of manufacturing the laser probe as an integrated body, the tubular molded body and the molded body of the core material are separately extruded and molded, the molded body of the core material is fired, and both end surfaces of the fired body are extruded. To obtain a core material, insert the core material into the internal space of the tubular molded body or the tubular calcined body, and fire the tubular molded body or the tubular calcined body to obtain a tubular member. The tubular member and the core material were bonded by firing shrinkage.
According to this method, since each molded body can be manufactured by the extrusion manufacturing method, it is suitable for mass production, and the manufacturing cost can be greatly reduced.
【０００９】また、本発明者は、他のセラミックス成形
方法、例えば射出成形法、プレス成形法による芯材およ
び管状成形体の成形も行ったが、やはり上記の製造方法
を適用できることを確認した。ただし、製造効率の観点
から、押し出し方法による成形がもっとも好ましいThe present inventor has also performed molding of a core material and a tubular molded body by another ceramics molding method such as an injection molding method or a press molding method, but it has been confirmed that the above-described manufacturing method can be applied. However, from the viewpoint of manufacturing efficiency, extrusion is most preferable.
【００１０】しかも、このように芯材を管状部材の内部
に固定する構造を採用すれば、レーザープローブの先端
側に芯材が位置するのであり、この芯材を研磨加工すれ
ば、所望形状のレーザープローブを形成することが容易
にできる。Moreover, if the structure in which the core material is fixed inside the tubular member is adopted, the core material is located on the tip side of the laser probe. If this core material is ground, a desired shape is obtained. A laser probe can be easily formed.
【００１１】また、本発明者は、管状部材の中に芯材を
挿入し、両者の間を無機接着剤によって接着することも
検討した。しかし、この管状部材と芯材との間は気密性
が悪くなり、手術中に血液がパイプ内に入り、レーザー
光の熱によってこの侵入した血液が凝固、炭化し、レー
ザー光がパイプ中を通りにくくなり、レーザープローブ
の切れ味が悪くなることがありうることが判明してき
た。しかし、本発明の製造方法および医療用レーザープ
ローブによれば、管状部材と芯材との間の気密性がきわ
めて高く、このように血液等の体液が侵入するというお
それがないことを確認した。The present inventor has also examined inserting a core material into a tubular member and bonding the two with an inorganic adhesive. However, the airtightness between the tubular member and the core becomes poor, blood enters the pipe during the operation, and the invaded blood is coagulated and carbonized by the heat of the laser light, and the laser light passes through the pipe. It has become clear that it may become difficult and the sharpness of the laser probe may deteriorate. However, according to the production method and the medical laser probe of the present invention, it was confirmed that the airtightness between the tubular member and the core material is extremely high, and thus there is no possibility that body fluid such as blood invades.
【００１２】[0012]
【実施例】本発明においては、透光性セラミックスとし
て、純度９９％以上の透光性多結晶アルミナを使用する
ことが特に好ましい。また、芯材を構成する焼成体の平
均結晶粒子径を２０〜５０μｍとし、管状部材の平均結
晶粒子径を、芯材の平均結晶粒子径よりも小さくするこ
とも想到した。EXAMPLE In the present invention, it is particularly preferable to use a translucent polycrystalline alumina having a purity of 99% or more as the translucent ceramic. It was also conceived that the average crystal grain size of the fired body constituting the core material is 20 to 50 μm and the average crystal grain size of the tubular member is smaller than the average crystal grain size of the core material.
【００１３】即ち、こうした透光性多結晶アルミナにお
いては、その平均結晶粒子径を大きくし、具体的には２
０μｍ以上とすることによって、そのレーザー光の直線
透過率、即ち、透明性を顕著に向上させ、レーザープロ
ーブの先端の発熱効率を高くすることができる。しか
し、このようなレーザープローブの先端が赤熱すると、
この先端が、例えば７００〜８００℃程度の高温に加熱
されるので、この先端部分が熱衝撃によって折れるとい
う事態を防止することが必要であり、先端部分に高度な
耐熱衝撃性が求められる。That is, in such a translucent polycrystalline alumina, the average crystal grain size is increased, specifically, 2
By setting the thickness to 0 μm or more, the linear transmittance of the laser beam, that is, the transparency can be significantly improved, and the heat generation efficiency at the tip of the laser probe can be increased. However, when the tip of such a laser probe glows red,
Since the tip is heated to a high temperature of, for example, about 700 to 800 ° C., it is necessary to prevent the tip from breaking due to thermal shock, and the tip is required to have high thermal shock resistance.
【００１４】そこで、芯材の平均結晶粒子径を大きくし
て、その透光性を向上させるのと同時に、管状部材の平
均結晶粒子径を、芯材の平均結晶粒子径よりも小さくす
ることによって、管状部材の方の耐熱衝撃性を向上さ
せ、これによってレーザープローブの先端部分が折れに
くいようにすることができる。こうした観点からは、管
状部材の平均結晶粒子径を１５μｍ以下とすることが、
より一層好ましい。また、この管状部材の平均結晶粒子
径は、実際の製造上の観点からは、１０μｍ以上とする
ことが好ましい。Therefore, by increasing the average crystal particle size of the core material to improve its light-transmitting property, at the same time, making the average crystal particle size of the tubular member smaller than the average crystal particle size of the core material. The tubular member can be improved in thermal shock resistance, so that the tip portion of the laser probe can be made hard to break. From this point of view, the average crystal grain size of the tubular member is set to 15 μm or less,
Even more preferred. The average crystal grain size of this tubular member is preferably 10 μm or more from the viewpoint of actual production.
【００１５】また、この際に、管状成形体または管状仮
焼体を、水素雰囲気下で焼成することが好ましい。At this time, it is preferable that the tubular compact or the tubular calcined body is fired in a hydrogen atmosphere.
【００１６】また、管状成形体には、セラミックス粒子
の他に、成形用のバインダーが含有されていることが通
常であるが、管状成形体を熱処理してこの中のバインダ
ーを除去して仮焼体を製造し、この管状仮焼体の内部空
間に芯材を挿入することが好ましい。なぜなら、管状成
形体のバインダーを飛散させることによって、仮焼体の
機械的強度は成形体の機械的強度よりも顕著に向上する
ので、管状仮焼体の内部空間に芯材を挿入するときに、
管状仮焼体の方が扱い易く、寸法も狂わないからであ
る。In addition to the ceramic particles, the tubular molded body usually contains a binder for molding. The tubular molded body is heat-treated to remove the binder, and then calcined. It is preferable to manufacture the body and insert the core into the internal space of the tubular calcined body. Because, by scattering the binder of the tubular molded body, the mechanical strength of the calcined body is significantly improved compared to the mechanical strength of the molded body, so when inserting the core material into the internal space of the tubular calcined body. ,
This is because the tubular calcined body is easier to handle and the dimensions do not change.
【００１７】また、例えばフックのように、芯材が湾曲
形状である場合には、研磨加工によってこの湾曲形状を
正確に削り出すことは困難であり、高コストである。し
かし、この芯材の成形体を乾燥台の上に載置して乾燥
し、この際に、乾燥台の載置面の形状を、芯材の形状と
相似形にすることができる。これによって、芯材の成形
体を乾燥させる際には、未だこの芯材は比較的に軟らか
いので、この載置面の形状に沿って芯材が重力によって
変形する。これによって、乾燥工程の間に、正確な湾曲
形状を有する芯材の成形体を製造することができる。Further, when the core material has a curved shape such as a hook, it is difficult to precisely cut out the curved shape by polishing, and it is expensive. However, the molded body of the core material is placed on a drying table and dried, and at this time, the shape of the mounting surface of the drying table can be made similar to the shape of the core material. As a result, when the molded body of the core material is dried, the core material is still relatively soft, so that the core material is deformed by gravity along the shape of the mounting surface. As a result, it is possible to manufacture a molded body of the core material having an accurate curved shape during the drying process.
【００１８】以下、必要に応じて図面を参照しつつ、本
発明の好適な態様について説明する。まず、透光性セラ
ミックスの原料粉末、好ましくは高純度アルミナ粉末を
準備する。これにバインダーを投入し、ニーダー等の混
練装置で混合ないし混練し、水、添加液、可塑剤等の添
加剤を混合し、再びニーダー等によって混合する。この
混合物を放置して水分が均一になるようにし、真空土練
機中に投入し、この混合物をプランジャーによって成形
して、丸棒形状の成形体を押し出し成形する。Hereinafter, preferred embodiments of the present invention will be described with reference to the drawings as necessary. First, a raw material powder for translucent ceramics, preferably high-purity alumina powder, is prepared. A binder is added to this, and the mixture is kneaded or kneaded by a kneading machine such as a kneader, water, an additive solution, an additive such as a plasticizer are mixed, and mixed again by a kneader or the like. The mixture is allowed to stand until the water content becomes uniform, and the mixture is put into a vacuum clay kneader, the mixture is molded by a plunger, and a round bar-shaped molded body is extruded.
【００１９】次いで、この丸棒形状の成形体を押し出し
成形装置内に投入し、管状成形体または芯材の成形体を
それぞれ押し出し成形する。図１（ａ）は、このように
して押し出し成形された管状成形体の一例を示す断面図
である。管状成形体１は、ほぼ真っ直ぐな円管形状をし
ており、管状成形体の両端にその内部空間１ａが開放さ
れている。一方、図１（ｂ）、（ｃ）は、それぞれ芯材
の成形体２、３を示す断面図である。この時点では、芯
材を長く成形しておき、この成形体を切断して複数の成
形体２、３を切り出すことが好ましい。次いで、成形体
１、２、３を乾燥する必要がある。Next, the round bar shaped body is put into an extrusion molding apparatus, and a tubular body or a core body is extruded. FIG. 1A is a cross-sectional view showing an example of a tubular molded body that is extrusion molded in this way. The tubular molded body 1 has a substantially straight circular tube shape, and the internal space 1a is open at both ends of the tubular molded body. On the other hand, FIGS. 1B and 1C are cross-sectional views showing molded bodies 2 and 3 of the core material, respectively. At this point, it is preferable that the core material is molded long and the molded body is cut to cut out a plurality of molded bodies 2 and 3. Next, it is necessary to dry the molded bodies 1, 2, and 3.
【００２０】この乾燥の段階で、成形体１、３について
は、乾燥時に各成形体ができるだけ変形しないように、
乾燥条件を注意することが必要である。しかし、図１
（ｂ）に示すフック用の芯材成形体２については、次の
ようにして乾燥を行うことができる。即ち、図２に示す
ように、乾燥台４の表面に、平坦面４ａ、湾曲面４ｂお
よび垂直に近い角度で急傾斜している傾斜面４ｃを形成
する。この平坦面４ａ上に成形体２を載置するときに、
仮想線で示すように、成形体２の一部分を乾燥台４に対
して接触させないようにし、浮いた状態としておく。こ
の状態で放置すると、成形体２は未だ水分を多量に含ん
だ軟らかい状態であるから、矢印Ａで示すように重力に
よって自然に変形し、湾曲面５ｂおよび傾斜面５ｃの外
形に沿うように変形して各面５ｂ、５ｃに対して接触す
る。At this drying stage, the molded bodies 1 and 3 should be prevented from deforming as much as possible during drying.
It is necessary to pay attention to the drying conditions. However, FIG.
The core material molding 2 for hooks shown in (b) can be dried as follows. That is, as shown in FIG. 2, a flat surface 4a, a curved surface 4b, and an inclined surface 4c steeply inclined at an angle close to vertical are formed on the surface of the drying table 4. When the molded body 2 is placed on this flat surface 4a,
As shown by the phantom line, a part of the molded body 2 is kept out of contact with the drying table 4 and left in a floating state. When left in this state, the molded body 2 is still in a soft state containing a large amount of water, so that the molded body 2 is naturally deformed by gravity as shown by the arrow A and is deformed along the outer shapes of the curved surface 5b and the inclined surface 5c. Then, the surfaces 5b and 5c are brought into contact with each other.
【００２１】この変形の結果、所望のフック形状を有す
る芯材成形体５が形成される。この成形体５において
は、平坦面４ａの部分に真直部分５ａが形成され、湾曲
面４ｂに沿って湾曲部分５ｂが形成され、傾斜面４ｃに
沿って傾斜部分５ｃが形成されている。むろん、この乾
燥台の上面の形状を変化させることによって、種々の形
状の成形体を作成することが可能になった。As a result of this deformation, the core material molded body 5 having a desired hook shape is formed. In the molded body 5, a straight portion 5a is formed on the flat surface 4a, a curved portion 5b is formed along the curved surface 4b, and an inclined portion 5c is formed along the inclined surface 4c. Needless to say, by changing the shape of the upper surface of the drying table, it became possible to produce molded articles of various shapes.
【００２２】次いで、好ましくは、各成形体を焼成する
前に、バインダーを除去する脱脂工程ないし仮焼工程を
実施する。この際、各成形体を高純度透光性アルミナの
粉末によって形成している場合には、仮焼温度を８００
℃〜１３００℃とすることが好ましい。また、脱脂工程
は、酸化雰囲気中で行うことが、バインダーの除去を促
進するために好ましい。Next, preferably, a degreasing step for removing the binder or a calcination step is carried out before firing each molded body. At this time, when each molded body is formed of high-purity translucent alumina powder, the calcination temperature is set to 800.
C. to 1300.degree. C. are preferable. The degreasing step is preferably performed in an oxidizing atmosphere in order to accelerate the removal of the binder.
【００２３】芯材の成形体３、５については、更に焼成
を行って焼成体を製造する。この際、各成形体を高純度
透光性アルミナの粉末によって形成している場合には、
焼成温度を１７５０℃〜１８６０℃とすることが好まし
い。そして、各焼成体の両端面を鏡面研磨加工すること
によって、各端面のＲｍａｘを０．６μｍ以下とするこ
とが好ましい。図２の成形体５を焼成し、この焼成体を
研磨することによって、図３（ａ）に示す芯材７が得ら
れる。図１（ｃ）の成形体３を焼成し、この焼成体を研
磨することによって、図３（ｂ）に示す芯材１０が得ら
れる。The molded bodies 3 and 5 of the core material are further fired to produce fired bodies. At this time, when each molded body is formed of high-purity translucent alumina powder,
The firing temperature is preferably 1750 ° C to 1860 ° C. Then, it is preferable that both end faces of each fired body are mirror-polished so that Rmax of each end face is 0.6 μm or less. By firing the molded body 5 of FIG. 2 and polishing the fired body, the core material 7 shown in FIG. 3A is obtained. By firing the molded body 3 of FIG. 1C and polishing the fired body, the core material 10 shown in FIG. 3B is obtained.
【００２４】次いで、管状成形体または管状仮焼体の内
部空間に芯材の成形体をセットする。この際には、例え
ば図３（ａ）に示すように、モリブデン等からなる設置
台８上に、好ましくは脱脂後の管状仮焼体６を設置し
て、内部空間６ａ内に上側端面６ｂ側から芯材７を挿入
することができる。この際、載置台８上には固定孔８ａ
が形成されており、この固定孔８ａ内に、細長い位置決
め用部材９の下端部が挿入され、固定されている。Next, the molded body of the core material is set in the internal space of the tubular molded body or the tubular calcined body. At this time, for example, as shown in FIG. 3 (a), the tubular calcined body 6 which is preferably degreased is installed on the installation table 8 made of molybdenum or the like, and the upper end surface 6 b side is provided in the internal space 6 a. The core material 7 can be inserted from the. At this time, the fixing hole 8a is provided on the mounting table 8.
Is formed, and the lower end of the elongated positioning member 9 is inserted and fixed in the fixing hole 8a.
【００２５】載置台８の表面から、位置決め用部材９の
上端までの間隔をＬ1 とし、載置台８の表面から管状仮
焼体６の上側端面６ｂまでの間隔をＬとする。端面６ｂ
側から、芯材７の真直部分７ａを挿入すると、芯材７の
端面が位置決め用部材９の上側端面に対して接触し、こ
こで芯材７の挿入が終了する。このとき、位置決め用部
材９の上端から管状仮焼体６の上側端面６ｂまでの間隔
Ｌ2 が、芯材７のうち管状仮焼体６内に挿入された部分
の寸法となる。従って、この挿入方法によって、管状仮
焼体６からの芯材７の露出部分の寸法を正確に決定する
ことができる。The distance from the surface of the mounting table 8 to the upper end of the positioning member 9 is L 1, and the distance from the surface of the mounting table 8 to the upper end surface 6b of the tubular calcined body 6 is L. End face 6b
When the straight portion 7a of the core material 7 is inserted from the side, the end surface of the core material 7 contacts the upper end surface of the positioning member 9, and the insertion of the core material 7 is completed here. At this time, the distance L 2 from the upper end of the positioning member 9 to the upper end surface 6b of the tubular calcined body 6 is the dimension of the portion of the core material 7 inserted into the tubular calcined body 6. Therefore, the dimension of the exposed portion of the core material 7 from the tubular calcined body 6 can be accurately determined by this insertion method.
【００２６】また、図３（ｂ）に示すように、モリブデ
ン等からなる設置台８上に、脱脂後の管状仮焼体６を設
置して、内部空間６ａ内に上側端面６ｂ側から芯材１０
を挿入する。この芯材１０は、内部空間６ａ内を、設置
台８の表面に接触する位置にまで移動する。Further, as shown in FIG. 3 (b), the degreased tubular calcined body 6 is placed on an installation table 8 made of molybdenum or the like, and the core material is inserted into the internal space 6a from the upper end face 6b side. 10
Insert. The core 10 moves in the internal space 6 a to a position where it comes into contact with the surface of the installation table 8.
【００２７】このように脱脂後の管状仮焼体と芯材とを
互いに嵌め合わせる段階では、焼成後の管状仮焼体の内
部空間の直径は、焼成後の芯材の外径よりも、３０〜１
００μｍ小さくなるように、収縮を制限することが好ま
しい。内部空間の直径が焼成後の芯材の直径を越える
と、焼成後にも両者の間の圧着力ないし圧縮応力が低く
なり、両者の間の気密性が低下してくる傾向がある。In the step of fitting the degreased tubular calcined body and the core material to each other as described above, the diameter of the internal space of the calcined tubular calcined body is 30 times larger than the outer diameter of the calcined core material. ~ 1
It is preferable to limit the shrinkage so that it becomes smaller by 00 μm. If the diameter of the internal space exceeds the diameter of the core material after firing, the pressure bonding force or compressive stress between the two will be low even after firing, and the airtightness between them will tend to be reduced.
【００２８】次いで、管状仮焼体６を、好ましくは水素
雰囲気下で焼結させ、管状部材の内部空間に、芯材を圧
着、固定する。例えば、図３（ａ）に示す管状仮焼体６
と芯材７とを熱処理すると、図４（ａ）に示すように、
管状仮焼体６が焼結して、焼結体からなる管状部材１１
が形成される。管状部材１１の内部空間には、端面１１
ｂ側から、芯材７の真直部分７ａが挿入されており、真
直部分７ａに対して管状部材１１から、矢印Ｂに示すよ
うな圧縮応力が加わっており、これによって両者の間が
気密に保持される。この接合体において、基本的なフッ
ク形状は実現されているが、更に具体的な患部の形態に
合わせるために、この接合体の先端部分を精密研磨加工
する必要がある。Next, the tubular calcined body 6 is preferably sintered in a hydrogen atmosphere, and the core material is pressure-bonded and fixed in the internal space of the tubular member. For example, the tubular calcined body 6 shown in FIG.
When the core material 7 and the core material 7 are heat treated, as shown in FIG.
The tubular calcined body 6 is sintered to form a tubular member 11 made of a sintered body.
Is formed. The inner surface of the tubular member 11 has an end surface 11
The straight portion 7a of the core material 7 is inserted from the side b, and a compressive stress as shown by an arrow B is applied to the straight portion 7a from the tubular member 11, whereby the space between the two is kept airtight. To be done. Although a basic hook shape is realized in this joined body, it is necessary to perform precision polishing on the tip portion of this joined body in order to further match the specific shape of the affected area.
【００２９】また、実際にレーザー光をレーザープロー
ブの先端に導入するためには、内部空間１１ａに光ファ
イバーを挿入するが、この際、芯材７のうち管状部材１
１内に挿入されている部分の寸法が重要である。しか
し、図３（ａ）を参照しつつ説明した前述の方法によれ
ば、この長さ寸法を、容易に、正確に制御することがで
きる。Further, in order to actually introduce the laser light to the tip of the laser probe, an optical fiber is inserted into the internal space 11a. At this time, the tubular member 1 of the core material 7 is inserted.
The size of the part inserted in 1 is important. However, according to the method described above with reference to FIG. 3A, the length dimension can be easily and accurately controlled.
【００３０】また、図３（ｂ）に示す管状仮焼体６と芯
材１０とを熱処理すると、図４（ｂ）に示すように、管
状仮焼体６が焼結して、焼結体からなる管状部材１１が
形成される。管状部材１１の内部空間の端面１１ｂ側に
は、真直な芯材１０が挿入されている。芯材１０に対し
て、管状部材１１から、矢印Ｂに示すような圧縮応力が
加わっており、これによって両者の間が気密に保持され
る。この接合体において、レーザープローブのうちフッ
ク以外の基本的な形状は実現されているが、更に具体的
な患部の形態に合わせるために、この接合体の先端部分
を精密研磨加工する必要がある。これによって、チーゼ
ル、コニカル、カーブといった各形状のレーザープロー
ブを削りだすことができる。When the tubular calcined body 6 and the core material 10 shown in FIG. 3 (b) are heat-treated, the tubular calcined body 6 is sintered as shown in FIG. 4 (b) to obtain a sintered body. The tubular member 11 is formed. The straight core material 10 is inserted on the end surface 11b side of the internal space of the tubular member 11. A compressive stress as shown by an arrow B is applied to the core material 10 from the tubular member 11, whereby the space between the two is airtightly maintained. In this joined body, the basic shape of the laser probe other than the hook is realized, but in order to further match the specific shape of the affected area, the tip portion of this joined body needs to be precision-polished. With this, laser probes of various shapes such as chisel, conical and curved can be cut out.
【００３１】以下、更に具体的な実験結果を述べる。前
述した図１〜図４に示す方法に従って、図４（ａ）に示
すレーザープローブ用素材を作成した。ただし、原料と
しては、高純度透光性アルミナの粉末（純度９９．９９
％）を使用し、バインダーとして、メチルセルロース系
の粘結剤４％と滑剤２％とを添加した。この混合物をニ
ーダーで５分間混練し、水、添加液および可塑剤を合計
２１．０％添加し、この混合物を更にニーダー中で２０
分間混練した。この混合物をビニール袋の中に入れ、２
４時間貯蔵し、水分が均一となるようにした。これを真
空土練機およびプランジャー成形機中に入れ、直径６０
ｍｍ、長さ３００ｍｍの丸棒状の成形体を製造した。Hereinafter, more specific experimental results will be described. According to the method shown in FIGS. 1 to 4 described above, the laser probe material shown in FIG. However, as the raw material, high-purity translucent alumina powder (purity 99.99) is used.
%), And 4% of a methylcellulose-based binder and 2% of a lubricant were added as binders. This mixture was kneaded in a kneader for 5 minutes, water, an additive solution and a plasticizer were added in a total amount of 21.0%, and the mixture was further added in a kneader for 20 minutes.
Kneaded for minutes. Put this mixture in a plastic bag, 2
It was stored for 4 hours so that the water content was uniform. Put this in a vacuum kneader and a plunger molding machine,
A round bar shaped body having a length of 300 mm and a length of 300 mm was manufactured.
【００３２】次いで、これを押し出し成形して、図１に
示す各成形体１、２を製造した。成形体１は、酸化雰囲
気中で１２００℃で仮焼して脱脂した。成形体２は、図
２に示すように乾燥台４上に載置し、変形させて乾燥し
た後、得られた成形体５を酸化雰囲気中で１２００℃で
仮焼して脱脂し、水素雰囲気中で１８６０℃で焼成し、
その平均結晶粒子径を２０〜３０μｍとした。図３
（ａ）に示すようにして芯材７を管状仮焼体６内に挿
入、固定し、管状仮焼体６を水素雰囲気中で１７２０℃
で焼成し、その平均結晶粒子径を１０〜１５μｍとし
た。Then, this was extrusion-molded to manufacture the molded bodies 1 and 2 shown in FIG. The molded body 1 was calcined at 1200 ° C. in an oxidizing atmosphere to degrease it. The molded body 2 is placed on a drying table 4 as shown in FIG. 2, deformed and dried, and then the obtained molded body 5 is calcined at 1200 ° C. in an oxidizing atmosphere to degrease it, and then in a hydrogen atmosphere. Firing at 1860 ° C in
The average crystal grain size was set to 20 to 30 μm. FIG.
As shown in (a), the core material 7 is inserted and fixed in the tubular calcined body 6, and the tubular calcined body 6 is heated at 1720 ° C. in a hydrogen atmosphere.
And the average crystal grain size was adjusted to 10 to 15 μm.
【００３３】このように、管状部材の焼成温度は、芯材
の焼成温度よりも低くすることが好ましい。なぜなら、
管状部材の焼成温度が芯材の焼成温度よりも高いと、管
状成形体の焼成の段階で芯材の方が更に焼結し、その寸
法が小さくなっていくので、寸法の制御が困難である
し、管状部材から芯材へと加わる圧縮応力が不十分にな
ったり、不均一になったりするからである。Thus, the firing temperature of the tubular member is preferably lower than the firing temperature of the core material. Because
When the firing temperature of the tubular member is higher than the firing temperature of the core material, the core material is further sintered during the firing step of the tubular molded body, and the dimension becomes smaller, which makes it difficult to control the dimension. However, the compressive stress applied from the tubular member to the core becomes insufficient or non-uniform.
【００３４】以上のようにして、図４（ａ）に示すレー
ザープローブ用素材を製造し、この先端部分を研磨加工
した。この結果、管状部材と芯材とは互いに強固に結合
されており、両者の間は気密性が保持されており、この
先端部分を赤熱させても血液等の液体の侵入は見られな
かった。また、この先端部分を８００℃に急速に加熱し
ても、先端部分の破損ないしクラック等はまったく見ら
れなかった。As described above, the material for the laser probe shown in FIG. 4 (a) was manufactured, and the tip portion was polished. As a result, the tubular member and the core material were firmly bonded to each other, and the airtightness was maintained between them, and no infiltration of liquid such as blood was observed even when the tip portion was heated red. Further, even when the tip portion was rapidly heated to 800 ° C., no damage or crack was observed at the tip portion.
【００３５】また、比較例として、前述したような形状
の芯材と管状部材とを別個に焼結させた。ただし、芯材
および管状部材の各々の原料粉末、成形体の添加物、仮
焼温度，焼成温度は、前述した本発明の実施例と同様と
した。そして、芯材と管状部材とを、無機接着剤を使用
して２００℃で加熱処理することによって、両者を接合
した。そして、この先端部分を赤熱させたところ、血液
等の液体の侵入が見られることがあった。In addition, as a comparative example, the core material and the tubular member having the above-described shapes were separately sintered. However, the respective raw material powders of the core material and the tubular member, the additives of the molded body, the calcination temperature, and the calcination temperature were the same as those in the above-described examples of the present invention. Then, the core material and the tubular member were heat-treated at 200 ° C. using an inorganic adhesive to bond them. When the tip portion was red-heated, infiltration of liquid such as blood was sometimes observed.
【００３６】[0036]
【発明の効果】以上述べたように、本発明によれば、医
療用レーザープローブを製造するのに際して、レーザー
プローブの高温時の熱衝撃強度を高くすることができ、
種々の形状、特にフック形状のレーザープローブを容易
に製造することができ、製造コストを低くすることがで
きる。しかも、管状部材と芯材との間の気密性がきわめ
て高く、血液等の体液が侵入するというおそれがない。
従って、本発明は、医療用レーザーメスの分野において
きわめて有益てある。As described above, according to the present invention, when manufacturing a medical laser probe, the thermal shock strength at high temperature of the laser probe can be increased,
Laser probes of various shapes, especially hook shapes, can be easily manufactured, and the manufacturing cost can be reduced. Moreover, the airtightness between the tubular member and the core material is extremely high, and there is no fear that body fluid such as blood will enter.
Therefore, the present invention is extremely useful in the field of medical laser scalpel.
【図１】（ａ）は、真直な管状成形体１を示す断面図で
あり、（ｂ）は、真直な芯材の成形体２を示す断面図で
あり、（ｃ）は、真直な芯材の成形体の断面を示す図で
ある。1A is a cross-sectional view showing a straight tubular molded body 1, FIG. 1B is a cross-sectional view showing a straight cored molded body 2, and FIG. 1C is a straight core. It is a figure which shows the cross section of the molded object of a material.
【図２】乾燥台４上に成形体２を載置し、この成形体２
を変形させて成形体５を得る工程を説明するための概略
断面図である。[FIG. 2] A molded body 2 is placed on a drying table 4, and the molded body 2
FIG. 6 is a schematic cross-sectional view for explaining a step of deforming the mold to obtain the molded body 5.
【図３】（ａ）は、脱脂後の管状仮焼体６の内部空間６
ａに芯材７を挿入した状態を示す断面図であり、（ｂ）
は、脱脂後の管状仮焼体６の内部空間６ａに芯材１０を
挿入した状態を示す断面図である。FIG. 3A is an internal space 6 of the tubular calcined body 6 after degreasing.
It is sectional drawing which shows the state which inserted the core material 7 in a, (b)
FIG. 4 is a cross-sectional view showing a state where the core material 10 is inserted into the internal space 6a of the tubular calcined body 6 after degreasing.
【図４】（ａ）は、管状部材１１の内部空間１１ａに芯
材７の真直部分７ａが挿入され、保持されている状態を
示す断面図であり、（ｂ）は、管状部材１１の内部空間
１１ａに芯材１０が挿入され、保持されている状態を示
す断面図である。4A is a cross-sectional view showing a state where a straight portion 7a of a core material 7 is inserted and held in an internal space 11a of the tubular member 11, and FIG. 4B is an internal view of the tubular member 11. It is sectional drawing which shows the state by which the core material 10 is inserted in the space 11a, and is hold | maintained.
１ 管状成形体 ２、３ 芯材の真直な成形体 ４
乾燥台 ４ａ 乾燥台上の平坦面 ４ｂ 乾燥台
上の湾曲面 ４ｃ 傾斜面 ５ 変形したフック形
状の芯材の成形体 ５ａ 成形体５の真直部分 ５
ｂ成形体５の湾曲部分 ６ 脱脂後の管状仮焼体
６ａ 管状仮焼体６の内部空間 ７ フック形状の芯
材 ８ 設置台 ８ａ 固定孔 １０ 真直な芯
材 １１管状部材 １１ａ 管状部材の内部空間
Ａ 成形体２が変形する方向 Ｂ 管状部材１１から芯材への圧縮応力の方向1 Tubular molded body 2, 3 Straight molded body of core material 4
Drying table 4a Flat surface on the drying table 4b Curved surface on the drying table 4c Inclined surface 5 Molded body of deformed hook-shaped core material 5a Straight part 5 of the molded body 5
b Curved part of molded body 6 Tubular calcined body after degreasing
6a Internal space of the tubular calcined body 7 Hook-shaped core material 8 Installation stand 8a Fixing hole 10 Straight core material 11 Tubular member 11a Internal space of the tubular member
A direction of deformation of the molded body B direction of compressive stress from the tubular member 11 to the core material
Claims (9)
ミックス製の管状部材とからなり、前記芯材が前記管状
部材の内部空間に挿入されており、この管状部材の焼成
時の収縮による圧縮応力によって前記芯材が前記管状部
材に対して結合されていることを特徴とする、医療用レ
ーザープローブ。1. A translucent ceramic core material and a translucent ceramic tubular member, wherein the core material is inserted into the internal space of the tubular member, and the tubular member shrinks during firing. A medical laser probe, characterized in that the core material is bonded to the tubular member by a compressive stress due to.
の透光性アルミナであり、前記芯材の平均結晶粒子径が
２０〜５０μｍであり、前記管状部材の平均結晶粒子径
が前記芯材の平均結晶粒子径よりも小さいことを特徴と
する、請求項１記載の医療用レーザープローブ。2. The translucent ceramic is translucent alumina having a purity of 99% or more, the core material has an average crystal particle size of 20 to 50 μm, and the tubular member has an average crystal particle size of the core material. 2. The medical laser probe according to claim 1, which is smaller than the average crystal particle size of.
５μｍであることを特徴とする、請求項２記載の医療用
レーザープローブ。3. The average crystal grain size of the tubular member is 10 to 1
The medical laser probe according to claim 2, which has a thickness of 5 μm.
ローブを製造する方法であって、芯材の成形体を焼成
し、この焼成体の少なくとも一方の端面を研磨加工して
芯材を得、この芯材を前記一方の端面側から管状成形体
または管状仮焼体の内部空間に挿入し、次いで前記管状
成形体または前記管状仮焼体を焼成して管状部材を得、
前記管状成形体または前記管状仮焼体の焼成収縮によっ
て前記管状部材と前記芯材とを結合することを特徴とす
る、医療用レーザープローブの製造方法。4. A method for manufacturing a medical laser probe made of translucent ceramics, which comprises firing a molded body of a core material and polishing at least one end surface of the fired body to obtain a core material. This core material is inserted into the internal space of the tubular molded body or the tubular calcined body from the one end face side, and then the tubular molded body or the tubular calcined body is fired to obtain a tubular member,
A method for manufacturing a medical laser probe, characterized in that the tubular member and the core material are bonded by firing shrinkage of the tubular formed body or the tubular calcined body.
の透光性アルミナであり、前記芯材の平均結晶粒子径を
２０〜５０μｍとし、前記管状部材の平均結晶粒子径を
前記芯材の平均結晶粒子径よりも小さくすることを特徴
とする、請求項４記載の医療用レーザープローブの製造
方法。5. The translucent ceramics is translucent alumina having a purity of 99% or more, the core material has an average crystal particle diameter of 20 to 50 μm, and the tubular member has an average crystal particle diameter of the core material. The method for producing a medical laser probe according to claim 4, wherein the diameter is smaller than the average crystal grain size.
は管状仮焼体の焼成温度よりも高くすることを特徴とす
る、請求項４または５記載の医療用レーザープローブの
製造方法。6. The method for producing a medical laser probe according to claim 4, wherein the firing temperature of the core material is set higher than the firing temperature of the tubular compact or the tubular calcined body.
素雰囲気下で焼成することを特徴とする、請求項４記載
の医療用レーザープローブの製造方法。7. The method for producing a medical laser probe according to claim 4, wherein the tubular formed body or the tubular calcined body is fired in a hydrogen atmosphere.
体内のバインダーを除去して管状仮焼体を得、この管状
仮焼体の前記内部空間に前記芯材を挿入することを特徴
とする、請求項４記載の医療用レーザープローブの製造
方法。8. The tubular compact is heat-treated to remove the binder in the tubular compact to obtain a tubular calcined body, and the core material is inserted into the internal space of the tubular calcined body. The method for producing a medical laser probe according to claim 4, wherein
材の成形体を乾燥台の上に載置して乾燥させるのに際し
て、前記乾燥台の載置面の形状を前記芯材の形状と相似
形にし、前記芯材の成形体を乾燥させる際にこの成形体
を前記載置面の形状に沿って重力によって変形させるこ
とを特徴とする、請求項４記載の医療用レーザープロー
ブの製造方法。9. When the molded body of the core material is placed on a drying table and dried when the core material has a curved shape, the placement surface of the drying table has the shape of the core material. 5. The medical laser probe according to claim 4, wherein the shape is similar to that of the above, and when the molded body of the core material is dried, the molded body is deformed by gravity along the shape of the placing surface. Manufacturing method.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP7028087A JP2971770B2 (en) | 1995-02-16 | 1995-02-16 | Medical laser probe and method of manufacturing the same |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP7028087A JP2971770B2 (en) | 1995-02-16 | 1995-02-16 | Medical laser probe and method of manufacturing the same |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH08215210A true JPH08215210A (en) | 1996-08-27 |
| JP2971770B2 JP2971770B2 (en) | 1999-11-08 |
Family
ID=12239008
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP7028087A Expired - Fee Related JP2971770B2 (en) | 1995-02-16 | 1995-02-16 | Medical laser probe and method of manufacturing the same |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2971770B2 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103781432A (en) * | 2011-11-17 | 2014-05-07 | 奥林巴斯株式会社 | Ultrasonic vibration probe, method for manufacturing ultrasonic vibration probe and ultrasonic therapeutic device |
-
1995
- 1995-02-16 JP JP7028087A patent/JP2971770B2/en not_active Expired - Fee Related
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103781432A (en) * | 2011-11-17 | 2014-05-07 | 奥林巴斯株式会社 | Ultrasonic vibration probe, method for manufacturing ultrasonic vibration probe and ultrasonic therapeutic device |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2971770B2 (en) | 1999-11-08 |
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