JPH0355136B2 - - Google Patents
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- JPH0355136B2 JPH0355136B2 JP59060325A JP6032584A JPH0355136B2 JP H0355136 B2 JPH0355136 B2 JP H0355136B2 JP 59060325 A JP59060325 A JP 59060325A JP 6032584 A JP6032584 A JP 6032584A JP H0355136 B2 JPH0355136 B2 JP H0355136B2
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- valve
- artificial
- cylindrical
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- leaflet
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Description
【発明の詳細な説明】
本発明はステントレス人工三葉弁に関するもの
である。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a stentless artificial trilobular valve.
近年、心臓外科領域においては、術式進歩と
種々の人工材料の開発により飛躍的な発展が認め
られている。人工弁の分野においても機械的人工
弁や生物人工弁で種々の改良が加えられ、数多く
の弁置換手術が行われている。機械的人工弁は耐
久性が優れ、構造や材質の改良によりかなり良好
なものが得られているが、未だ、血行力学的に問
題があり、且つ血栓形成の課題は解決されていな
い。一方生物人工弁では、弁置換後の石灰化、、
硬化、萎縮、穿孔など耐久性面で問題がある。 In recent years, rapid progress has been observed in the field of cardiac surgery due to advances in surgical techniques and the development of various artificial materials. In the field of artificial valves, various improvements have been made to mechanical and biological valves, and numerous valve replacement surgeries have been performed. Mechanical prosthetic valves have excellent durability, and improvements in structure and materials have made them quite good, but they still have hemodynamic problems and the problem of thrombus formation has not been solved. On the other hand, with bioprosthetic valves, calcification after valve replacement,
There are durability problems such as hardening, atrophy, and perforation.
高分子材料を用いた生物弁類似の人工三葉弁に
関しては、既に米国特許明細書第4222126号、第
4265694号、第4364126号、第4364127号、
WP83／00617号公報等に種々の形態が提案され
ているが、いずれも硬いフレーム部分及びステン
ト部分を有するために生体弁と同様の動きをとら
すことができなかつた。 Regarding artificial three-leaflet valves similar to biological valves using polymeric materials, US Pat.
No. 4265694, No. 4364126, No. 4364127,
Although various forms have been proposed in WP83/00617, etc., all of them have a rigid frame portion and a stent portion, and therefore cannot have the same movement as a biological valve.
本発明者はかかる問題点を解消すべく、鋭意研
究の結果、本発明に到達したのである。即ち、本
発明は、球面又は円柱を基本とした曲面を有する
三葉弁の弁尖部と軟質縫着部材とが一体化されて
いることを特徴とする人工三葉弁である。 In order to solve this problem, the present inventor has arrived at the present invention as a result of intensive research. That is, the present invention is an artificial three-leaflet valve characterized in that the valve leaflets of the three-leaflet valve having a curved surface based on a spherical or cylindrical surface and a soft sewing member are integrated.
次に本発明のステントレス人工三葉弁を図面を
用いて説明する。 Next, the stentless artificial trilobate valve of the present invention will be explained using the drawings.
第１図は本発明の人工弁の全体図、第２図はそ
の平面図、第３図はその側面図を示す。図中、１
は軟質縫着部材、２は弁尖部、６は縫着部材突出
部である。 FIG. 1 is an overall view of the artificial valve of the present invention, FIG. 2 is a plan view thereof, and FIG. 3 is a side view thereof. In the figure, 1
2 is a soft sewing member, 2 is a valve leaflet, and 6 is a sewing member protrusion.
第４図は従来から提案されている人工弁の基本
形体の全体図で、図中、３は硬いステント部、４
はバルキーな縫着部材、５は弁尖部である。 Figure 4 is an overall view of the basic shape of the artificial valve that has been proposed in the past.In the figure, 3 is a hard stent part, 4
5 is a bulky sewing member, and 5 is a valve leaflet.
第５図は本発明の人工弁を生体に縫着する際の
縫着部位ａ，ｂ，ｃを示す。第６図は本発明の人
工弁を製作する際に使用するモルド（弁製作用雄
型）の一例である。 FIG. 5 shows sewing sites a, b, and c when sewing the artificial valve of the present invention to a living body. FIG. 6 is an example of a mold (male mold for manufacturing a valve) used when manufacturing the artificial valve of the present invention.
縫着部材１は縫合により破損しない柔軟な高分
子材料からなり、その表面は抗血栓性材料によつ
て被覆されているものである。縫着部材の素材と
しては例えば、ポリエステル、ポリアミド、ポリ
プロピレン、ポリスルホン類から得た織布、編布
もしくは不織布を円筒状としたものやテフロンの
ようなフツ素系多孔質材料などから得られた円筒
状物が用いられ、これらは生体との縫合時に破損
しない材質であり、しかも、血圧変動に追従可能
な程度の柔軟性を有するものである必要がある。
更に縫着部材の表面は抗血栓性材料によつて被覆
されている。その際に被覆材として用いられる抗
血栓性材料としては、特に限定はないが、弁尖部
と一体となつていることの必要上、弁尖部の形成
に用いられる材料と同一であることが好ましい。 The suture member 1 is made of a flexible polymeric material that will not be damaged by suturing, and its surface is coated with an antithrombotic material. Examples of materials for the sewing member include cylindrical woven fabrics, knitted fabrics, or nonwoven fabrics made from polyester, polyamide, polypropylene, and polysulfones, and cylindrical cylindrical pieces made from fluorine-based porous materials such as Teflon. These materials need to be made of a material that will not break when sutured to a living body, and must also have enough flexibility to follow blood pressure fluctuations.
Additionally, the surface of the suture member is coated with an antithrombotic material. There is no particular limitation on the antithrombotic material used as the covering material at that time, but it is preferable that it be the same material used to form the valve leaflet because it needs to be integrated with the valve leaflet. preferable.
また本発明の人工弁の特徴の１つとして縫着部
材１の３つの突出部６が血圧の変化に応じてその
径を変化させることから、被覆材として用いられ
る抗血栓性材料は弾性体であることが好ましく、
その１例としてセグメント化ポリエーテルウレタ
ン系材料が通常用いられる。 Furthermore, one of the features of the artificial valve of the present invention is that the three protrusions 6 of the sewing member 1 change their diameters in response to changes in blood pressure, so the antithrombotic material used as the covering material is made of an elastic material. It is preferable that there is
As one example, segmented polyether urethane based materials are commonly used.
弁尖部２は球面又は円柱を基本型とした曲面を
有する三葉弁からなり、これは縫着部材１に接合
部のない状態で一体化されている。素材としては
通常、柔軟な抗血栓性材料であるセグメント化ポ
リエーテルウレタン系材料が好ましく用いられ
る。 The valve leaflet portion 2 consists of a three-leaflet valve having a curved surface with a basic shape of a sphere or cylinder, and is integrated with the sewing member 1 without any joints. As the material, a segmented polyether urethane-based material, which is a flexible antithrombotic material, is usually preferably used.
次に本発明の三葉弁は以下の方法によつて作ら
れるが、勿論これに限定されるものでない。即
ち、予め高分子材料からなる円筒上の編布、織
布、不織布もしくは多孔質体の内外表面全体を抗
血栓性材料で被覆し、これを弁尖部成形用の鋳型
の円筒部にはめ込む。この際、縫着部材に縫着部
ａ，ｂ，ｃが形成されるように、鋳型の頭部よ
り、円筒状の編物、織物、不織布もしくは多孔質
体を若干はみ出させておく。続いてそれを抗血栓
性材料を溶解した溶液に浸し、その後乾燥により
溶剤を除去する、いわゆるデイツピング成形を繰
返し行うことにより鋳型部上にフイルム状弁尖部
を形成していく。その場合デイツピング工程の回
数によつて皮膜の厚さが決まる。皮膜の厚さは通
常約0.05〜0.5mmである。このように形成された
弁尖部は縫着部材と接合部分なく一体化される。
続いて鋳型から取外した成型品の弁尖部の先端を
三葉となるように切断して、本発明の三葉弁が得
られる。ここで必要に応じて切断部を溶剤もしく
は抗血栓性材料の稀釈溶液で処理することによ
り、円滑な面とすることができる。 Next, the trileaflet valve of the present invention is made by the following method, but of course the method is not limited thereto. That is, the entire inner and outer surfaces of a cylindrical knitted fabric, woven fabric, nonwoven fabric, or porous body made of a polymeric material are coated with an antithrombotic material in advance, and this is fitted into the cylindrical portion of a mold for molding the valve leaflet. At this time, a cylindrical knitted fabric, woven fabric, nonwoven fabric, or porous material is slightly protruded from the head of the mold so that sewn parts a, b, and c are formed on the sewn member. Next, a film-like valve leaflet is formed on the mold part by repeatedly performing so-called dipping molding, in which the mold is soaked in a solution in which an antithrombotic material is dissolved, and then the solvent is removed by drying. In this case, the thickness of the coating is determined by the number of dipping steps. The thickness of the coating is usually about 0.05-0.5 mm. The valve leaflet portion formed in this manner is integrated with the sewing member without any joints.
Subsequently, the tips of the valve leaflets of the molded product removed from the mold are cut into three leaflets to obtain the three leaflet valve of the present invention. Here, if necessary, the cut portion can be treated with a solvent or a diluted solution of an antithrombotic material to provide a smooth surface.
本発明の人工三葉弁の大きさは特に限定はない
が、通常、弁の口径が13〜35mm、縫着部材の長さ
が７mm〜30mmの範囲である。 Although the size of the artificial three-leaflet valve of the present invention is not particularly limited, the diameter of the valve is usually in the range of 13 to 35 mm, and the length of the sewn member is in the range of 7 to 30 mm.
本発明の人工弁は生体弁の弁置換用としてのみ
ならず、種々の形態の人工心臓用弁としても有効
に使用可能である。本発明の人工弁を人工心臓用
の弁として用いる場合には、従来の機械弁におい
て問題とされた血栓形成が解消されることが最大
の利点である。 The artificial valve of the present invention can be effectively used not only as a replacement for a biological valve, but also as a valve for various types of artificial heart. When the artificial valve of the present invention is used as a valve for an artificial heart, the greatest advantage is that thrombus formation, which has been a problem with conventional mechanical valves, is eliminated.
大動脈弁置換用として本発明の人工弁を用いる
際には、第５図においてａの部分（点線部分）を
縫着し、次いでｂの部分を大動脈壁に縫着する。
縫着部の３つの頂上部ｃは、プレジエツト付マツ
トレス縫合で大動脈壁の外で結紮する。 When using the artificial valve of the present invention for aortic valve replacement, the part a (dotted line part) in FIG. 5 is sewn, and then the part b is sewn to the aortic wall.
The three crests c of the sutures are ligated outside the aortic wall with pine-less sutures with pledgets.
以上のように本発明の三葉弁は従来の硬いステ
ントを有する三葉弁と異なり、生体弁（大動脈
弁）と同様の機構で開閉するステントレス三葉弁
であるがために、小口径においても大きな圧差を
生じることがない。また本発明の人工弁構造では
血流のうつ滞の部分も少ないために血栓形成面に
おいても有利である。 As described above, the trileaflet valve of the present invention is different from the conventional trileaflet valve having a hard stent, and because it is a stentless trileaflet valve that opens and closes using the same mechanism as a biological valve (aortic valve), it can be used with a small diameter. does not create a large pressure difference. Furthermore, the artificial valve structure of the present invention has fewer areas where blood flow is stagnant, which is advantageous in terms of thrombus formation.
更に本発明の人工弁は大動脈壁の動きに追従し
て開閉するために頻脈応答性が良好で、材質の折
れ曲りストレスも少いものとなり、その結果とし
て弁の耐久性向上が期待される。 Furthermore, since the artificial valve of the present invention opens and closes following the movement of the aortic wall, it has good tachycardia response and has less bending stress on the material, which is expected to improve the durability of the valve. .
以下に本発明の人工三葉弁の製作方法の例示な
らびに流体力学的機能評価結果を記述する。 Below, an example of the manufacturing method of the artificial three-leaflet valve of the present invention and the results of hydrodynamic function evaluation will be described.
人工弁の製作例
第７図に示したような数値制御施盤により製作
したモルド（図中、単位はmm、平面XYZに対し
点ｗは21°沈み込んでいる）を用い、２％濃度の
セグメント化ポリエーテルウレタンウレア溶液で
３回デイツピング、乾燥を繰返した。乾燥はモー
ターによる回転を行いながら60℃、40％RH下で
各20分間続いて室温、40％RH下で10分間行つ
た。Example of manufacturing an artificial valve Using a mold manufactured using a numerically controlled machine as shown in Figure 7 (in the figure, the unit is mm, point w is sunken at 21° with respect to the plane XYZ), a segment with a 2% concentration was used. Dipping and drying were repeated three times with a polyether urethane urea solution. Drying was carried out at 60° C. and 40% RH for 20 minutes each while rotating with a motor, and then at room temperature and 40% RH for 10 minutes.
次に、10％濃度のポリマー溶液で２回デイツピ
ング、乾燥を繰返した。乾燥は前の工程と同様に
モルドを回転させながら60℃、40％RH下で40分
間、続じて室温下で10分間行つた。この段階で、
予め２％濃度のポリマー溶液で被覆を行つておい
たテフロン製織布（厚さ１mm）からなる円筒状の
縫着部材を上記モルドの円筒部にかぶせた後、更
に10％濃度のポリマー溶液で縫着部材とモルドの
３頂点付近の側壁との接合が充分得られるように
注意しながら２回デイツピング、乾燥を繰返し
た。続いて２％濃度のポリマー溶液を用い３回、
弁尖部および縫合部材全体のデイツピング、乾燥
を繰返した。充分に乾燥した後、全体をメタノー
ルに浸漬し、モルドから人工弁を取りはずした
後、更に充分乾燥を行い最終的に弁の弁尖部の先
端部分を切離し三葉とした。 Next, dipping and drying were repeated twice with a 10% polymer solution. Drying was carried out at 60° C. and 40% RH for 40 minutes while rotating the mold as in the previous step, and then at room temperature for 10 minutes. At this stage,
After covering the cylindrical part of the mold with a cylindrical sewing member made of Teflon woven cloth (thickness 1 mm) that had been coated with a 2% polymer solution in advance, the cylindrical sewing member was coated with a 10% polymer solution. Dipping and drying were repeated twice, taking care to ensure sufficient bonding between the sewing member and the side wall near the three vertices of the mold. Subsequently, three times using a 2% concentration polymer solution,
Dipping and drying of the valve leaflet and the entire suture member were repeated. After sufficiently drying, the whole was immersed in methanol, and the artificial valve was removed from the mold, and then thoroughly dried, and finally the tip of the leaflet of the valve was cut off to form a trefoil.
以上のようにして外径21mm、弁尖部の厚み0.08
mm、縫合部材の長さ14mmの三葉弁を用いて機能試
験を行つた。 As above, the outer diameter is 21 mm and the thickness of the valve leaflet is 0.08 mm.
A functional test was performed using a trilobed valve with a suture member length of 14 mm.
人工弁の機能試験
１ 「人工弁に関するJIS規格原案」における圧
力損失−流量特性曲線試験を拍動流ポンプ、ラ
テツクスゴム製大動脈基部モデルを備えた人工
弁試験装置を用い、駆動圧0.2Kg／cm2、収縮
期・拡張期比１：２、拍動数80c.p.mのポンプ
駆動条件下で本発明の弁と従来弁との比較を行
つた。Functional Test of Artificial Valve 1 Pressure drop-flow characteristic curve test according to the "JIS standard draft for artificial valves" was performed using an artificial valve testing device equipped with a pulsatile flow pump and a latex rubber aortic root model, with a driving pressure of 0.2 Kg/cm 2 The valve of the present invention was compared with a conventional valve under pump drive conditions with a systolic/diastolic ratio of 1:2 and a pulsation rate of 80 c.pm.
第８図において、ａは本発明の人工弁の圧力
損失−流量特性曲線である。ｂはBjo¨rk−
Shileyデイスク弁、ｃはS.J.Mパイロカイトカ
ーボン製二派弁およびｄはHancockブタ弁で
いずれも比較のために試験したものである。な
お、“圧力損失−流量特性曲線”（Valve State
Plot）は、１心拍における圧損と流量とをプロ
ツトしたもので、第８図ｅの点線が生体本来の
弁、実線が人工弁のプロツトをあらわす。図
中、流量は１分間当りの流量の瞬間値、△Ｐは
左室−大動脈圧較差を示す。ａ−ｂ−ｃは収縮
期での前方流量、ｃ−ｄ−ｅは閉鎖期の逆流
量、ｅ−ａは拡張期のもれ量を示す。 In FIG. 8, a is a pressure loss-flow characteristic curve of the artificial valve of the present invention. b is Bjo¨rk−
A Shiley disc valve, c an SJM pyrokite carbon two-way valve, and d a Hancock pig valve were all tested for comparison. In addition, the “pressure loss-flow characteristic curve” (Valve State
Plot) is a plot of the pressure drop and flow rate during one heartbeat, and the dotted line in FIG. 8e represents the original valve of the living body, and the solid line represents the plot of the artificial valve. In the figure, the flow rate is the instantaneous value of the flow rate per minute, and ΔP is the left ventricular-aortic pressure gradient. a-b-c indicates the forward flow rate in the systolic phase, c-de indicates the reflux flow rate in the occlusion phase, and e-a indicates the leakage amount in the diastolic phase.
第８図ａ〜ｅより明らかなように、本発明の
弁は従来の何れの弁に比べても、開放時圧損が
少く、最大流量が大であつた。 As is clear from FIGS. 8a to 8e, the valve of the present invention had a smaller pressure loss when opened and a larger maximum flow rate than any of the conventional valves.
２ 拍出流量特性試験
本発明の人工弁及び従来品の流量パターンの
比較を行つた（第９図）。2 Output flow rate characteristic test The flow patterns of the artificial valve of the present invention and a conventional valve were compared (Fig. 9).
流量パターンはQF（前方流量）、QR（閉鎖まで
の逆流量）、QL（閉鎖後のもれ量）につき解析
したものである。図中ａは本発明の人工弁（ス
テンレス型）、ｂはステントレス型と同じ形で、
ポリプロピレン製のステントを縫着部材と同じ
形にして外側にとりつけたものである。ｃは
Bjo¨rk−Shileyデイスク弁、ｄはS.J.M.パイロ
ライトカーボン製二派弁、ｅはHancokブタ弁
である。 The flow rate pattern was analyzed for Q F (forward flow rate), Q R (reverse flow rate until closure), and Q L (leakage amount after closure). In the figure, a is the artificial valve of the present invention (stainless steel type), b is the same shape as the stentless type,
A polypropylene stent is attached to the outside in the same shape as the sewing member. c is
Bjo¨rk-Shiley disk valve, d is SJM pyrolite carbon two-way valve, e is Hancok pig valve.
第１図は本発明の人工弁の全体図を示す。第２
図は本発明の人工弁の平面図を示す。第３図は本
発明の人工弁の側面図を示す。第４図は従来の人
工弁の基本形体の全体図を示す。第５図は本発明
の人工弁の全体図を示す。第６図は本発明の人工
弁を製作する際に使用するモルドの一例を示す。
第７図は本発明の人工弁を製作する際に使用する
モルドの一例を示す。第８図は人工弁の圧力損失
−流量特性曲線を示す。ａは本発明の人工弁、ｂ
はBjo¨rk−Shileyデイスク弁、ｃはS.J.M.パイロ
ライトカーボン製二派弁、ｄはHancockブタ弁
の圧力損失−流量特性曲線を示す。ｅは生体本来
の弁の圧力損失−流量特性曲線を示す。第９図は
人工弁の流量パターンを示す。ａは本発明の人工
弁、ｂはステント型人工弁、ｃはBjo¨rk−Shiley
デイスク弁、ｄはS.J.M.パイロライトカーボン製
二葉弁、ｅはHancokブタ弁の量流パターンを示
す。
FIG. 1 shows an overall view of the artificial valve of the present invention. Second
The figure shows a plan view of the artificial valve of the invention. FIG. 3 shows a side view of the artificial valve of the present invention. FIG. 4 shows an overall view of the basic shape of a conventional artificial valve. FIG. 5 shows an overall view of the artificial valve of the present invention. FIG. 6 shows an example of a mold used when manufacturing the artificial valve of the present invention.
FIG. 7 shows an example of a mold used in manufacturing the artificial valve of the present invention. FIG. 8 shows the pressure loss-flow characteristic curve of the artificial valve. a is the artificial valve of the present invention, b
shows the pressure loss-flow characteristic curve of the Bjo¨rk-Shiley disc valve, c shows the SJM pyrolite carbon two-way valve, and d shows the Hancock pig valve. e shows the pressure loss-flow characteristic curve of the biological valve. FIG. 9 shows the flow pattern of the artificial valve. a is the artificial valve of the present invention, b is a stent-type artificial valve, c is Bjo¨rk-Shiley
Disc valve, d shows the SJM pyrolite carbon bileaflet valve, e shows the flow pattern of the Hancok pig valve.
Claims (1)
状の軟質縫着部材に弁尖部形成用の鋳型をはめこ
み、抗血栓性材料溶液を用いてデイツピング成形
により弁尖部を軟質縫着部材と一体成形してな
る、球面又は円柱面を基本とした曲面を有する三
葉弁の弁尖部と円筒状の軟質縫着部材とが、シー
ムレスに一体化されていることを特徴とするステ
ントレス人工三葉弁 ２ 軟質縫着部が高分子素材からなる円筒状の織
布、編布、不織布もしくは多孔質物からなり、そ
の表面が抗血栓性材料で被覆されていることを特
徴とする特許請求の範囲第１項記載のステントレ
ス人工三葉弁。 ３ 弁尖部および軟質縫着部の表面被覆層がセグ
メント化ポリエーテルウレタン系材料からなるこ
とを特徴とする特許請求の範囲第１項記載のステ
ントレス人工三葉弁。[Claims] 1. A mold for forming a valve leaflet is fitted in advance into a cylindrical soft sewing member coated with an antithrombotic material, and the valve leaflet is formed by dipping molding using an antithrombotic material solution. It is characterized in that the valve leaflets of the trilobular valve having a curved surface based on a spherical or cylindrical surface, which is integrally molded with the soft sewing member, and the cylindrical soft sewing member are seamlessly integrated. A stentless artificial three-lobed valve 2 characterized in that the soft sewn portion is made of a cylindrical woven fabric, knitted fabric, non-woven fabric, or porous material made of a polymeric material, and its surface is coated with an antithrombotic material. A stentless artificial trilobular valve according to claim 1. 3. The stentless artificial trileaflet valve according to claim 1, wherein the surface coating layer of the valve leaflet portion and the soft suture portion is made of a segmented polyether urethane material.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP6032584A JPS60203251A (en) | 1984-03-28 | 1984-03-28 | Stentless artificial three-lobe valve |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP6032584A JPS60203251A (en) | 1984-03-28 | 1984-03-28 | Stentless artificial three-lobe valve |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS60203251A JPS60203251A (en) | 1985-10-14 |
| JPH0355136B2 true JPH0355136B2 (en) | 1991-08-22 |
Family
ID=13138900
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP6032584A Granted JPS60203251A (en) | 1984-03-28 | 1984-03-28 | Stentless artificial three-lobe valve |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS60203251A (en) |
Families Citing this family (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| AU578967B2 (en) * | 1984-09-13 | 1988-11-10 | Allegheny Ludlum Steel Corp. | Method and apparatus for direct casting of crystalline strip in non-oxadizing atmosphere |
| AU578968B2 (en) * | 1984-09-13 | 1988-11-10 | Allegheny Ludlum Steel Corp. | Method and apparatus for direct casting of crystalline strip by radiantly cooling |
| JPS61255656A (en) * | 1985-05-08 | 1986-11-13 | 東洋紡績株式会社 | Tube internal mount type heart valve |
| FR2838631B1 (en) * | 2002-04-23 | 2004-12-24 | Engeneering And Technological | METHOD FOR PRODUCING AN AORTIC OR MITRAL HEART VALVE PROSTHESIS AND AORTIC OR MITRAL HEART VALVE PROSTHESIS THUS OBTAINED |
| US8163011B2 (en) * | 2006-10-06 | 2012-04-24 | BioStable Science & Engineering, Inc. | Intra-annular mounting frame for aortic valve repair |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4340091A (en) * | 1975-05-07 | 1982-07-20 | Albany International Corp. | Elastomeric sheet materials for heart valve and other prosthetic implants |
| DK229077A (en) * | 1977-05-25 | 1978-11-26 | Biocoating Aps | HEARTBALL PROSTHET AND PROCEDURE FOR MANUFACTURING IT |
-
1984
- 1984-03-28 JP JP6032584A patent/JPS60203251A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS60203251A (en) | 1985-10-14 |
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