DE1491218C3 - Blood vessel prosthesis and method for making the same - Google Patents
Blood vessel prosthesis and method for making the sameInfo
- Publication number
- DE1491218C3 DE1491218C3 DE1491218A DE1491218A DE1491218C3 DE 1491218 C3 DE1491218 C3 DE 1491218C3 DE 1491218 A DE1491218 A DE 1491218A DE 1491218 A DE1491218 A DE 1491218A DE 1491218 C3 DE1491218 C3 DE 1491218C3
- Authority
- DE
- Germany
- Prior art keywords
- blood vessel
- prosthesis
- collagen
- tube
- mass
- 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
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L33/00—Antithrombogenic treatment of surgical articles, e.g. sutures, catheters, prostheses, or of articles for the manipulation or conditioning of blood; Materials for such treatment
- A61L33/0005—Use of materials characterised by their function or physical properties
- A61L33/0011—Anticoagulant, e.g. heparin, platelet aggregation inhibitor, fibrinolytic agent, other than enzymes, attached to the substrate
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/062—Apparatus for the production of blood vessels made from natural tissue or with layers of living cells
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/14—Macromolecular materials
- A61L27/22—Polypeptides or derivatives thereof, e.g. degradation products
- A61L27/24—Collagen
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/34—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/507—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials for artificial blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/54—Biologically active materials, e.g. therapeutic substances
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00365—Proteins; Polypeptides; Degradation products thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
- A61L2300/23—Carbohydrates
- A61L2300/236—Glycosaminoglycans, e.g. heparin, hyaluronic acid, chondroitin
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
- A61L2300/404—Biocides, antimicrobial agents, antiseptic agents
- A61L2300/406—Antibiotics
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
- A61L2300/42—Anti-thrombotic agents, anticoagulants, anti-platelet agents
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Chemical & Material Sciences (AREA)
- Transplantation (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Epidemiology (AREA)
- Engineering & Computer Science (AREA)
- Medicinal Chemistry (AREA)
- Dermatology (AREA)
- Biomedical Technology (AREA)
- Vascular Medicine (AREA)
- Pulmonology (AREA)
- Gastroenterology & Hepatology (AREA)
- Cardiology (AREA)
- Heart & Thoracic Surgery (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Hematology (AREA)
- Biophysics (AREA)
- Materials Engineering (AREA)
- Materials For Medical Uses (AREA)
- Prostheses (AREA)
- Laminated Bodies (AREA)
- Treatments For Attaching Organic Compounds To Fibrous Goods (AREA)
Description
5. Verfahren nach Anspruch 4, dadurch ge- kontrolle bei der Serienproduktion stellen weitere kennzeichnet, daß die zubereitete Kollagen- Nachteile dieser Methode dar.5. The method according to claim 4, thereby providing additional control during series production indicates that the prepared collagen is a disadvantage of this method.
masse bei der Homogenisierung mit Mucopoly- 40 Aufpibe der Erfindung ist demgegenüber die Hersacchariden und/oder mit Glycerin und/oder mit stellung einer Blutgefäßprothese, welche nach außen mindestens einem Antibiotikum vermischt wird. hin hochporös ist und ein Durchwachsen der um-In contrast, the mass in the homogenization with Mucopoly 40 Aufpibe of the invention is the Hersacchariden and / or with glycerine and / or with the position of a blood vessel prosthesis, which to the outside at least one antibiotic is mixed. is highly porous and a growth in the surrounding
6. Verfahren nach Anspruch 4 und 5, dadurch liegenden Blutgefäßzellgewebe relativ rasch gestattet,
gekennzeichnet, daß die Kunstfasergeweberöhre welche aber im Inneren so aufgebaut ist, daß
an der Kollagenröhre mit Hilfe einer durch Be- 45 Blutungen mit Sicherheit vermieden werden,
spritzen oder Anstreichen aufgetragenen Zwi- Die Erfindung besteht darin, daß der Kunstfaserschenschicht
aus nativer Kollagenmasse fixiert gewebeschlauch mit einer Innenschicht aus einer
wird. selbsttragenden, an sich bekannten Kollagenmasse6. The method according to claim 4 and 5, characterized in that lying blood vessel cell tissue is allowed relatively quickly, characterized in that the synthetic fiber tube which, however, is constructed inside so that bleeding can be avoided with certainty on the collagen tube with the aid of a bleeding caused by bleeding,
The invention consists in that the synthetic fiber layer made of native collagen mass is fixed with a fabric tube with an inner layer made of a. self-supporting, known collagen mass
verbunden ist, die durch eine die Resorbierbarkeitis connected by an absorbability
50 modifizierende chemische Härtung unvollständig gehärtet ist und deren Innenfläche mit einem Antikoagulationsmittel behandelt ist. Mit dieser Blutgefäßprothese wurden sehr gute Erfahrungen ge-Die Erfindung betrifft eine Blutgefäßprothese mit macht.50 modifying chemical hardening incompletely hardened and the inner surface of which is treated with an anticoagulant. With this blood vessel prosthesis Very good experiences have been made. The invention relates to a blood vessel prosthesis with power.
einem physiologisch inerten Kunstfasergewebe- 55 Zur Erzielung einer stark verbesserten Haftfähigschlauch, der eine Wandporosität über 2000 ml H2O/ keit der Außensehicht an der Innenschicht ist es cm2min bei einem Innendruck von 120 mm Hg auf- zweckmäßig, wenn die beiden Schichten durch eine weist, sowie ein Verfahren zur Herstellung derselben. native Kollagenmasse miteinander verbunden sind. Bekannt ist es, Fäden, Schläuche und Filme aus Vorteilhaft ist es, wenn die Innenschicht mita physiologically inert synthetic fiber fabric- 55 To achieve a greatly improved adhesive hose, which has a wall porosity of over 2000 ml H 2 O / speed of the outer layer on the inner layer, it is advisable for cm 2 min at an internal pressure of 120 mm Hg for the two layers to pass through one has, and a method for making the same. native collagen masses are linked together. It is known to make threads, tubes and films from it is advantageous if the inner layer with
Dispersionen von tierischen Haut- und Sehnen- 60 Mucopolysacchariden und/oder mit Glycerin und/
Kollagen herzustellen. Hierzu wird nur geringfügig oder mit wenigstens einem Antibiotikum angereichert
chemisch vorbehandeltes tierisches Kollagenmaterial ist. Hierdurch werden die Möglichkeiten eines Einzerkleinert
und zerfasert und die erhaltene Masse Wachsens der Blutgefäßprothese verbessert,
unter Zusatz von Säuren, alkalisch reagierenden Hergestellt wird die Prothese dadurch, daß manTo produce dispersions of animal skin and tendon mucopolysaccharides and / or with glycerine and / collagen. For this purpose, chemically pretreated animal collagen material is only slightly or enriched with at least one antibiotic. As a result, the possibilities of crushing and fraying are improved and the mass of growth of the blood vessel prosthesis obtained is improved,
with the addition of alkaline acids, the prosthesis is produced by
Mitteln oder Salzen nach Quellung in einem 65 eine in an sich bekannter Weise durch alkalische wässerigen Milieu homogenisiert und dann die ge- Quellung des Rind-Leimgallertgewebes zubereitete quollene Masse unter Umständen mechanisch noch Kollagenmasse desintegriert und homogenisiert und weiter verfeinert, wobei das Material auf verhältnis- die Masse in Form einer selbsttragenden Röhre ge-Agents or salts after swelling in a 65 in a manner known per se by alkaline aqueous medium and then prepared the swelling of the beef glue jelly tissue swollen mass may be mechanically disintegrated and homogenized and collagen mass further refined, the material being proportioned to the mass in the form of a self-supporting tube
staltet, die man sodann mit der hochporösen Kunst- Ausf ührungsbeispielthat you can then use with the highly porous art design example
iasergeweberohre überzieht, worauf man die innere s v iaservergeweberohre covers, whereupon the inner s v
Oberfläche der Kollagenröhre durch Einwirkung Kollagenmasse, zubereitet durch alkalische Quel-Surface of collagen tube by exposure to collagen mass prepared by alkaline source
eines Gerbmittels teilweise härtet und nach Aus- lung des Rind-Leimgallertgewebes, wird desintegriertof a tanning agent partially hardens and after the beef glue gelatin has developed, it is disintegrated
waschen des Gerbmittels mit einem Antikoagulations- s und gründlich homogenisiert (z.B. 24 Stunden langwash the tanning agent with an anticoagulant and thoroughly homogenize (e.g. for 24 hours
mittel präpariert, trocknet und schließlich in einer in einem Homogenisator) und dann 24 Stunden langmedium prepared, dried and finally in one in a homogenizer) and then for 24 hours
luftdichten Hülle sterilisiert in einem Kühlschrank bei 0 bis 4° C sich selbst be-airtight envelope sterilizes itself in a refrigerator at 0 to 4 ° C
Dabei kann es zweckmäßig sein, daß die zu- lassen. Die st* behandelte Kollagenmasse kann manIt can be useful that they allow. The st * treated collagen mass can be
bereitete KoUagenmasse bei der Homogenisierung schon zur Erzeugung von resorbierbaren, selbst-prepared KoUagen mass during the homogenization for the production of resorbable, self-
mit Mucopolysacchariden und/oder mit Glycerin ίο tragenden Röhren, welche als Bestandteil einer kom-with mucopolysaccharides and / or with tubes carrying glycerin ίο, which are part of a com-
und/oder mit mindestens einem Antibiotikum ver- Dinierten hochporösen Blutgefäßprothese dienen,and / or are used with at least one antibiotic, highly porous blood vessel prosthesis,
mischt wird. Hierbei lassen sich die genannten Mittel verwenden,is mixed. The means mentioned can be used here,
am besten in die KoUagenmasse einbringen. Die KoUagenmasse kann man auch gegebenenfallsbest brought into the KoUagen mass. The KoUagenasse can also be used if necessary
Eine besonders feste Verbindung beider Röhren durch Vermischen mit Mucopolysacchariden, z. B. kann man dadurch erzielen, daß man die hoch- 15 vom Typus der Hyaluronsäure (0,5 bis 3,0%), mit poröse Geweberöhre an der KoUagenröhre mit Hilfe Glycerin (0,5 bis 5,0·/·) oder mit Antibiotika, z. B. einer durrh Bespritzen oder Anstreichen auf- mit CmOrtetracyklin (1 bis 5 g/100 g Masse), Neogetragenen Zwischenschicht aus amorpher, nativer, my ei η (0,5 bis 5 g/100 g Masse) oder Bacitracin chemisch nicht modifizierter Kollagenmasse fixiert. (10 000 bis 50 000 E/100 g Masse), anreichern. DieA particularly strong connection between the two tubes by mixing them with mucopolysaccharides, e.g. B. can be achieved that the high-15 of the type of hyaluronic acid (0.5 to 3.0%), with porous tissue tube on the KoUagenröhre with the help of glycerine (0.5 to 5.0 · / ·) or with antibiotics, e.g. B. a durrh spraying or painting with CmOrtetracyklin (1 to 5 g / 100 g mass), neo-worn intermediate layer of amorphous, native, my ei η (0.5 to 5 g / 100 g mass) or bacitracin chemically unmodified collagen mass fixed. (10,000 to 50,000 U / 100 g mass), enrich. the
Die auf vorstehendem Wege hergestellte hoch- ac genannten Komponenten kann man entweder einzeln
poröse Blutgefäßprothese läßt sich ohne Gefahr oder in verschiedenen Kombinationen zusetzen,
einer unmittelbaren oder später auftretenden, lang Aus der auf diese Weise aufgearbeiteten Kollagendauernden Blutung durch die Prothesenwand im- masse wird dann in einer mit rotierendem Ziehkopf
plantieren. Bei der klinischen Anwendung sind weder versehenen Preßmaschine durch Zusammenspinnen
besondere Maßnahmen noch ein spezielles Arbeits- 35 und Verbindung einzelner Fasern eine Röhre mit gcverfahren
bei der Operation erforderlich. Aus den wünschtem Durchmesser (z. B. 9 mm) und erforderbisherigen
Forschungsergebnissen auf diesem Gebiet licher Wandstärke (z. B. 0,4 bis 0,6 mm) gezogen,
geht hervor, daß die hohe Porosität des nicht und zwar unter gleichzeitigem Durchblasen von luft,
resorbierbaren Bestandteils der erfindungsgemäßen z. B. unter 40 bis 150 mm Wassersäuledruck. Die
Prothesen wesentlich bessere Resultate bei der Blut- 30 fertige Röhre trocknet man dann langsam bei einer
gefäßrekonstruktion gewährleistet, als es mit dem Temperatur von 15 bis 25° C in mildem Luftstrom,
bisher benutzten Ersatzmaterial .nöglieh war. Nach dem Trocknen überzieht man die Kollagen-The components mentioned above can be used either individually. Porous blood vessel prosthesis can be added without risk or in various combinations,
an immediately or later occurring, long bleeding through the prosthesis wall that has been processed in this way is then planted in a rotating pulling head. In clinical use, neither a press machine equipped with a spinning technique nor a special work and connection of individual fibers with a tube with gc procedures are required during the operation. From the desired diameter (z. B. 9 mm) and the necessary previous research results in this area Licher wall thickness (z. B. 0.4 to 0.6 mm), it can be seen that the high porosity of the not and that with simultaneous blowing of air, absorbable component of the z. B. under 40 to 150 mm water column pressure. The prosthesis results in significantly better results with the blood-finished tube then slowly dried during a vascular reconstruction than was possible with the temperature of 15 to 25 ° C in a gentle stream of air, previously used replacement material. After drying, the collagen is coated
Das Anbringen der resorbierbaren selbsttragenden röhre mit Hilfe einer speziellen Vorrichtung mit derAttaching the resorbable self-supporting tube with the help of a special device with the
Röhre im Inneren der Kunstfasergeweberöhre läßt Kunstfasergeweberöhre, worauf man sie von innenTube inside the synthetic fiber fabric tube lets synthetic fiber fabric tube, whereupon you can see it from the inside
die Maschen des Gewibes relativ frei, so daß rasches 35 mit einer i°/oigen wässerigen 2,4,6-Trimethoxytriazin-the meshes of the fabric are relatively free, so that a 100% aqueous 2,4,6-trimethoxytriazine
Durchwachsen der umliegenden Blutgefäßzellgewebe lösung, nachher mit überschüssigem destilliertemThe surrounding blood vessel cell tissue solution grows through, afterwards with excess distilled
erfolgen kann, ohne daß ein vorheriger Abbau des Wasser und schließlich mit einer Lösung eines ge-can take place without a previous degradation of the water and finally with a solution of a
resorbierbaren Bestandteils notwendig wäre. Die eigneten Antikoagulationsmittels, z. B. mit einerabsorbable component would be necessary. Suitable anticoagulants, e.g. B. with a
blutgerinnungshemmende Wirksamkeit der inneren l°/oigen wässerigen Heparinlösung, durchwäscht. DieAnticoagulant effectiveness of the inner 10% aqueous heparin solution, washed through. the
Oberfläche verhindert die Bildung von Thromben. 40 Herstellung der Blutgefäßprothese beendigt manSurface prevents the formation of thrombi. 40 Manufacture of the blood vessel prosthesis is terminated
Ein weiterer Vorteil liegt darin, daß man die durch Trocknen unter bereits erwähnten Bedingun-Another advantage is that the drying under the aforementioned conditions
biologischen Eigenschaften des Materials zur Her- gen. Durch Luftüberdruck in der inneren Röhrebiological properties of the material used to produce it. By means of excess air pressure in the inner tube
stellung von Blutgefäßprothesen gemäß der Erfin- während des Trocknens wird eine feste VerbindungPosition of blood vessel prostheses according to the invention while drying becomes a solid connection
dung dank großer chemischer Reaktivität der beider Schichten erzielt Diese Verbindung kannThis connection can be achieved thanks to the great chemical reactivity of the two layers
KoUagenmasse je nach Bedarf neuen Forschungs- 45 man auch so verfestigen, daß uan zwischen beideDepending on the need for new research, the coagulation mass can also be solidified in such a way that there is between the two
ergebnissen anpassen kann. Das ist besonders für Schichten eine dünne Zwischenschicht aus amorpher,can adjust results. This is especially for layers a thin intermediate layer of amorphous,
das Einwachsen des nicht resorbierbaren Bestandteils nativer, chemisch nicht modifizierter KoUagenmassethe ingrowth of the non-resorbable component of native, chemically unmodified KoUagen mass
und für die Neubildung der Blutgefäßwand wichtig. aufträgt.and important for the formation of new blood vessel walls. applies.
Durch chemische Härtung der KoUagenröhre läßt Die fertige Blutgefäßprothese wird dann in einenBy chemical hardening of the KoUagenröhre the finished blood vessel prosthesis is then in a
sich auch ihre Resorptionsdauer beeinflussen und 50 luftdichten Umschlag, z. B. in eine Glasampulle,also affect their resorption time and 50 airtight envelope, z. B. in a glass ampoule,
standardisieren, so daß eine vorzeitige Resorption eingeschlossen und mit Gamma-Strahlung (z. B. instandardize so that premature absorption is included and treated with gamma radiation (e.g. in
dieser Röhre vermieden werden kann. einer Gabe von 2.10« r 5 Stunden lang) sterilisiert.this tube can be avoided. a dose of 2.10 «r for 5 hours).
Claims (4)
Form einer selbsttragenden Röhre gestaltet wird. Als resorierbares Material wurden bisher Catgutdit sodann mit der hochporösen» Kunstfaser- 30 fasern, gegebenenfalls mit Kunstfasern zusammen geweberöhre überzogen wird, worauf die innere gewirkt oder -gewebt, amorphe Gelatine oder auch Oberfläche der Kollagenröhre durch Einwirkung Kollagenfilm, der in Form einer Röhre zusammeneines Gerbmittels teilweise gehärtet und nach genäht ist, benutzt. Die experimentelle Erprobung Auswaschen des Gerbmittels mit einem Anti- solcher Prothese war im wesentlichen erfolglos, da koagulationsmittel präpariert, getrocknet und 35 die Versuchstiere größtenteils (über 500O) ausschließlich in einer luftdichten Hülle sterilisiert geblutet waren. Ein kompliziertes Herstellungswird. verfahren und die Unmöglichkeit der Qualitäts-4. A method for the production of blood vessel-implanted blood vessel replacement of basic meaning prostheses according to claim 1 to 3, characterized in that it is characterized by a combination of a resorbable one in ar. known as material is solved with a thin tissue prosthesis way by alkaline swelling of the beef glue - the resorbable material has the task of gelatinous tissue prepared collagen mass of the - during the healing process the blooming is integrated and homogenized and the mass in meshes of the synthetic fiber tissue impede.
Shape of a self-supporting tube is designed. As a resorbable material, catgutdit has hitherto been covered with the highly porous synthetic fiber, if necessary with synthetic fibers, on which the inner knitted or woven, amorphous gelatin or the surface of the collagen tube through the action of a collagen film, which is in the form of a tube together with a tanning agent partially hardened and after being sewn, used. The experimental trial washout of the tanning agent with an anti such prosthesis was substantially unsuccessful since coagulant prepared, dried and 35, the test animals were bled mostly sterilized (over 50 0 O) exclusively in an air-tight envelope. A complicated manufacturing process becomes. procedure and the impossibility of quality
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CS564463 | 1963-06-15 |
Publications (3)
Publication Number | Publication Date |
---|---|
DE1491218A1 DE1491218A1 (en) | 1969-04-03 |
DE1491218B2 DE1491218B2 (en) | 1972-06-08 |
DE1491218C3 true DE1491218C3 (en) | 1973-01-04 |
Family
ID=5401669
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
DE1491218A Expired DE1491218C3 (en) | 1963-06-15 | 1963-12-12 | Blood vessel prosthesis and method for making the same |
Country Status (6)
Country | Link |
---|---|
US (1) | US3425418A (en) |
BE (1) | BE649183A (en) |
BR (1) | BR6355428D0 (en) |
CH (1) | CH472219A (en) |
DE (1) | DE1491218C3 (en) |
GB (1) | GB1018288A (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE3608158A1 (en) * | 1986-03-12 | 1987-09-17 | Braun Melsungen Ag | VESSELED PROSTHESIS IMPREGNATED WITH CROSSLINED GELATINE AND METHOD FOR THE PRODUCTION THEREOF |
Families Citing this family (85)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3526005A (en) * | 1967-06-29 | 1970-09-01 | Gulf General Atomic Inc | Method of preparing an intravascular defect by implanting a pyrolytic carbon coated prosthesis |
US3688317A (en) * | 1970-08-25 | 1972-09-05 | Sutures Inc | Vascular prosthetic |
US3710777A (en) * | 1970-12-23 | 1973-01-16 | C Sparks | Method and apparatus for growing graft tubes in place |
US3710400A (en) * | 1971-08-30 | 1973-01-16 | C Sparks | Graft member grown in a living body |
US3908657A (en) * | 1973-01-15 | 1975-09-30 | Univ Johns Hopkins | System for continuous withdrawal of blood |
US3974526A (en) * | 1973-07-06 | 1976-08-17 | Dardik Irving I | Vascular prostheses and process for producing the same |
US6436135B1 (en) | 1974-10-24 | 2002-08-20 | David Goldfarb | Prosthetic vascular graft |
US4101984A (en) * | 1975-05-09 | 1978-07-25 | Macgregor David C | Cardiovascular prosthetic devices and implants with porous systems |
US4280954A (en) | 1975-07-15 | 1981-07-28 | Massachusetts Institute Of Technology | Crosslinked collagen-mucopolysaccharide composite materials |
GB1515963A (en) * | 1975-07-15 | 1978-06-28 | Massachusetts Inst Technology | Crosslinked collagen-mucopolysaccharide composite materials |
JPS5413694A (en) * | 1977-07-01 | 1979-02-01 | Sumitomo Electric Industries | Composite blood vessel prosthesis and method of producing same |
DE2853614A1 (en) * | 1978-01-25 | 1979-07-26 | Bentley Lab | IMPLANT |
AU516741B2 (en) * | 1978-05-23 | 1981-06-18 | Bio Nova Neo Technics Pty. Ltd. | Vascular prostheses |
JPS6037735B2 (en) * | 1978-10-18 | 1985-08-28 | 住友電気工業株式会社 | Artificial blood vessel |
SE424401B (en) * | 1979-06-06 | 1982-07-19 | Bowald S | BLODKERLSPROTES |
US4416028A (en) * | 1981-01-22 | 1983-11-22 | Ingvar Eriksson | Blood vessel prosthesis |
US4539716A (en) * | 1981-03-19 | 1985-09-10 | Massachusetts Institute Of Technology | Fabrication of living blood vessels and glandular tissues |
US4546500A (en) * | 1981-05-08 | 1985-10-15 | Massachusetts Institute Of Technology | Fabrication of living blood vessels and glandular tissues |
ATE13477T1 (en) * | 1981-07-02 | 1985-06-15 | Intermedicat Gmbh | PROCESS FOR THE PRODUCTION OF SCLEROPROTEIN TRANSPLANTS WITH INCREASED BIOLOGICAL STABILITY. |
IT1154510B (en) * | 1981-08-14 | 1987-01-21 | Bentley Lab | CONNECTOR DEVICE IMPLANTABLE IN THE BODY AND DEVICE OF VASCULAR IMPLANTATION ASSOCIATED WITH IT |
US4442133A (en) * | 1982-02-22 | 1984-04-10 | Greco Ralph S | Antibiotic bonding of vascular prostheses and other implants |
NL8202894A (en) * | 1982-07-16 | 1984-02-16 | Rijksuniversiteit | POLYESTER FILAMENT MATERIAL. |
US5110852A (en) * | 1982-07-16 | 1992-05-05 | Rijksuniversiteit Te Groningen | Filament material polylactide mixtures |
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US4695281A (en) * | 1983-03-25 | 1987-09-22 | Koken Co., Ltd. | Medical material |
EP0128501B1 (en) * | 1983-06-06 | 1989-03-29 | Kanegafuchi Kagaku Kogyo Kabushiki Kaisha | Artificial vessel and process for preparing the same |
US4670286A (en) * | 1983-09-20 | 1987-06-02 | Allied Corporation | Method of forming prosthetic devices |
FR2556210B1 (en) * | 1983-12-08 | 1988-04-15 | Barra Jean Aubert | VENOUS PROSTHESIS AND PROCESS FOR PRODUCING THE SAME |
US4842575A (en) * | 1984-01-30 | 1989-06-27 | Meadox Medicals, Inc. | Method for forming impregnated synthetic vascular grafts |
US5197977A (en) * | 1984-01-30 | 1993-03-30 | Meadox Medicals, Inc. | Drug delivery collagen-impregnated synthetic vascular graft |
US5108424A (en) * | 1984-01-30 | 1992-04-28 | Meadox Medicals, Inc. | Collagen-impregnated dacron graft |
IL74179A (en) * | 1984-01-30 | 1992-05-25 | Meadox Medicals Inc | Collagen synthetic vascular graft |
DE3546875C2 (en) * | 1984-01-30 | 1996-05-09 | Meadox Medicals Inc | Synthetic vascular grafts |
IL74180A (en) * | 1984-01-30 | 1992-06-21 | Meadox Medicals Inc | Drug delivery collagen-impregnated synthetic vascular graft |
GB2156677A (en) * | 1984-03-31 | 1985-10-16 | Wessex Medical Group Ltd | Bioprosthetic conduits |
EP0169259A1 (en) * | 1984-07-25 | 1986-01-29 | Surgical Patent Products Inc. Ltd. | Vascular prostheses for dry preservation, method of conditioning and their use in surgery |
US5037377A (en) * | 1984-11-28 | 1991-08-06 | Medtronic, Inc. | Means for improving biocompatibility of implants, particularly of vascular grafts |
GB8430265D0 (en) * | 1984-11-30 | 1985-01-09 | Vascutek Ltd | Vascular graft |
US4744792A (en) * | 1985-01-22 | 1988-05-17 | Richards Medical Company | Middle ear ventilating tube |
US4629458A (en) * | 1985-02-26 | 1986-12-16 | Cordis Corporation | Reinforcing structure for cardiovascular graft |
US4997440A (en) * | 1985-04-25 | 1991-03-05 | American Cyanamid Company | Vascular graft with absorbable and nonabsorbable components |
GB8516421D0 (en) * | 1985-06-28 | 1985-07-31 | Biotechnology Interface Ltd | Fibronectins |
CA1292597C (en) * | 1985-12-24 | 1991-12-03 | Koichi Okita | Tubular prothesis having a composite structure |
EP0323144A3 (en) * | 1987-12-28 | 1990-05-16 | Vyzkumny Ustav Potravinarskeho Prumyslu | Method of manufacturing at least single-layer tubular blood vessel endoprosthesis, especially of a small internal diameter, and extruding nozzle for carrying out this method |
US5192311A (en) * | 1988-04-25 | 1993-03-09 | Angeion Corporation | Medical implant and method of making |
US4927410A (en) * | 1988-11-18 | 1990-05-22 | University Of South Florida | Method for fabricating prosthesis material |
US5256418A (en) * | 1990-04-06 | 1993-10-26 | Organogenesis, Inc. | Collagen constructs |
CS277367B6 (en) * | 1990-12-29 | 1993-01-13 | Krajicek Milan | Three-layered vascular prosthesis |
US5383927A (en) * | 1992-05-07 | 1995-01-24 | Intervascular Inc. | Non-thromogenic vascular prosthesis |
US20020055710A1 (en) * | 1998-04-30 | 2002-05-09 | Ronald J. Tuch | Medical device for delivering a therapeutic agent and method of preparation |
US5480423A (en) | 1993-05-20 | 1996-01-02 | Boston Scientific Corporation | Prosthesis delivery |
EP1217101B8 (en) | 1994-04-29 | 2006-02-01 | Boston Scientific Scimed, Inc. | Stent with collagen |
WO1995029646A1 (en) * | 1994-04-29 | 1995-11-09 | Boston Scientific Corporation | Medical prosthetic stent and method of manufacture |
EP0698396B1 (en) * | 1994-08-12 | 2001-12-12 | Meadox Medicals, Inc. | Vascular graft impregnated with a heparin-containing collagen sealant |
US5665114A (en) * | 1994-08-12 | 1997-09-09 | Meadox Medicals, Inc. | Tubular expanded polytetrafluoroethylene implantable prostheses |
JP3799626B2 (en) * | 1995-04-25 | 2006-07-19 | 有限会社ナイセム | Cardiovascular repair material and method for producing the same |
US5928279A (en) * | 1996-07-03 | 1999-07-27 | Baxter International Inc. | Stented, radially expandable, tubular PTFE grafts |
US7241309B2 (en) | 1999-04-15 | 2007-07-10 | Scimed Life Systems, Inc. | Self-aggregating protein compositions and use as sealants |
US6177609B1 (en) | 1997-03-10 | 2001-01-23 | Meadox Medicals, Inc. | Self-aggregating protein compositions and use as sealants |
US6106454A (en) * | 1997-06-17 | 2000-08-22 | Medtronic, Inc. | Medical device for delivering localized radiation |
US6203536B1 (en) * | 1997-06-17 | 2001-03-20 | Medtronic, Inc. | Medical device for delivering a therapeutic substance and method therefor |
US6013099A (en) | 1998-04-29 | 2000-01-11 | Medtronic, Inc. | Medical device for delivering a water-insoluble therapeutic salt or substance |
US6129757A (en) | 1998-05-18 | 2000-10-10 | Scimed Life Systems | Implantable members for receiving therapeutically useful compositions |
US20040030377A1 (en) * | 2001-10-19 | 2004-02-12 | Alexander Dubson | Medicated polymer-coated stent assembly |
WO2002074189A2 (en) * | 2001-03-20 | 2002-09-26 | Nicast Ltd. | Electrospinning nonwoven materials with rotating electrode |
US20070031607A1 (en) * | 2000-12-19 | 2007-02-08 | Alexander Dubson | Method and apparatus for coating medical implants |
US7244272B2 (en) | 2000-12-19 | 2007-07-17 | Nicast Ltd. | Vascular prosthesis and method for production thereof |
US20020084178A1 (en) * | 2000-12-19 | 2002-07-04 | Nicast Corporation Ltd. | Method and apparatus for manufacturing polymer fiber shells via electrospinning |
WO2005065578A2 (en) * | 2004-01-06 | 2005-07-21 | Nicast Ltd. | Vascular prosthesis with anastomotic member |
US7794490B2 (en) * | 2004-06-22 | 2010-09-14 | Boston Scientific Scimed, Inc. | Implantable medical devices with antimicrobial and biodegradable matrices |
US8029563B2 (en) | 2004-11-29 | 2011-10-04 | Gore Enterprise Holdings, Inc. | Implantable devices with reduced needle puncture site leakage |
US20100331947A1 (en) * | 2005-02-17 | 2010-12-30 | Alon Shalev | Inflatable Medical Device |
DE102009037134A1 (en) | 2009-07-31 | 2011-02-03 | Aesculap Ag | Tubular implant for replacement of natural blood vessels |
CA2906621A1 (en) | 2013-03-15 | 2014-09-25 | Baxter International Inc. | Immobilization of active agent on a substrate |
WO2014197768A1 (en) * | 2013-06-07 | 2014-12-11 | Baxter International Inc. | Immobilization of an active agent on a substrate using compounds including trihydroxyphenyl groups |
US9814560B2 (en) | 2013-12-05 | 2017-11-14 | W. L. Gore & Associates, Inc. | Tapered implantable device and methods for making such devices |
CN104027844A (en) * | 2014-04-04 | 2014-09-10 | 张志辉 | Novel method for coating artificial blood vessel with Astragalus polysaccharide |
AU2016270380B2 (en) | 2015-06-05 | 2019-04-04 | W. L. Gore & Associates, Inc. | A low bleed implantable prosthesis with a taper |
WO2018007849A1 (en) | 2016-07-05 | 2018-01-11 | Carlos Alvarado | Serous membrane for ocular surface disorders |
CZ308556B6 (en) * | 2017-07-26 | 2020-11-25 | Vseobecna Fakultni Nemocnice V Praze | Composite vascular replacement and manufacturing method |
DK3658990T3 (en) | 2017-07-28 | 2024-01-29 | Stratasys Ltd | FORMULATIONS USABLE IN ADDITIVE MANUFACTURING OF A THREE-DIMENSIONAL OBJECT FROM A SOFT MATERIAL |
JP7348162B2 (en) | 2017-07-28 | 2023-09-20 | ストラタシス リミテッド | Additive manufacturing methods using materials with soft tissue properties |
EP3658359B1 (en) | 2017-07-28 | 2023-11-15 | Stratasys Ltd. | Method and system for fabricating object featuring properties of a hard tissue |
CN111148483B (en) * | 2017-07-28 | 2022-11-15 | 斯特拉塔西斯公司 | Method and system for manufacturing an object with vascular properties |
CN110141681B (en) * | 2019-05-24 | 2021-09-10 | 深圳齐康医疗器械有限公司 | Wound repair material for cell suspension transplantation and preparation method thereof |
Family Cites Families (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB591509A (en) * | 1945-03-26 | 1947-08-20 | Raymond Nigel Roy | A soluble lumen suture support |
US3106483A (en) * | 1961-07-27 | 1963-10-08 | Us Catheter & Instr Corp | Synthetic blood vessel grafts |
US3108357A (en) * | 1962-06-20 | 1963-10-29 | William J Liebig | Compound absorbable prosthetic implants, fabrics and yarns therefor |
US3272204A (en) * | 1965-09-22 | 1966-09-13 | Ethicon Inc | Absorbable collagen prosthetic implant with non-absorbable reinforcing strands |
-
1963
- 1963-12-12 CH CH1526263A patent/CH472219A/en not_active IP Right Cessation
- 1963-12-12 DE DE1491218A patent/DE1491218C3/en not_active Expired
- 1963-12-13 BR BR155428/63A patent/BR6355428D0/en unknown
- 1963-12-16 GB GB49509/63A patent/GB1018288A/en not_active Expired
-
1964
- 1964-04-15 US US359973A patent/US3425418A/en not_active Expired - Lifetime
- 1964-06-12 BE BE649183A patent/BE649183A/xx unknown
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE3608158A1 (en) * | 1986-03-12 | 1987-09-17 | Braun Melsungen Ag | VESSELED PROSTHESIS IMPREGNATED WITH CROSSLINED GELATINE AND METHOD FOR THE PRODUCTION THEREOF |
Also Published As
Publication number | Publication date |
---|---|
GB1018288A (en) | 1966-01-26 |
DE1491218B2 (en) | 1972-06-08 |
US3425418A (en) | 1969-02-04 |
DE1491218A1 (en) | 1969-04-03 |
BR6355428D0 (en) | 1973-07-19 |
CH472219A (en) | 1969-05-15 |
BE649183A (en) | 1964-10-01 |
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Legal Events
Date | Code | Title | Description |
---|---|---|---|
SH | Request for examination between 03.10.1968 and 22.04.1971 | ||
C3 | Grant after two publication steps (3rd publication) |