CA1335432C - Tissue graft composition and method - Google Patents
Tissue graft composition and methodInfo
- Publication number
- CA1335432C CA1335432C CA000605031A CA605031A CA1335432C CA 1335432 C CA1335432 C CA 1335432C CA 000605031 A CA000605031 A CA 000605031A CA 605031 A CA605031 A CA 605031A CA 1335432 C CA1335432 C CA 1335432C
- Authority
- CA
- Canada
- Prior art keywords
- graft
- tissue
- tunica
- segment
- tissue graft
- 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 - Lifetime
Links
Classifications
-
- E—FIXED CONSTRUCTIONS
- E02—HYDRAULIC ENGINEERING; FOUNDATIONS; SOIL SHIFTING
- E02D—FOUNDATIONS; EXCAVATIONS; EMBANKMENTS; UNDERGROUND OR UNDERWATER STRUCTURES
- E02D5/00—Bulkheads, piles, or other structural elements specially adapted to foundation engineering
- E02D5/02—Sheet piles or sheet pile bulkheads
- E02D5/03—Prefabricated parts, e.g. composite sheet piles
- E02D5/04—Prefabricated parts, e.g. composite sheet piles made of steel
- E02D5/08—Locking forms; Edge joints; Pile crossings; Branch pieces
-
- 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
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K35/00—Medicinal preparations containing materials or reaction products thereof with undetermined constitution
- A61K35/12—Materials from mammals; Compositions comprising non-specified tissues or cells; Compositions comprising non-embryonic stem cells; Genetically modified cells
- A61K35/37—Digestive system
- A61K35/38—Stomach; Intestine; Goblet cells; Oral mucosa; Saliva
-
- 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
- A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
-
- 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
- A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
- A61L27/3604—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix characterised by the human or animal origin of the biological material, e.g. hair, fascia, fish scales, silk, shellac, pericardium, pleura, renal tissue, amniotic membrane, parenchymal tissue, fetal tissue, muscle tissue, fat tissue, enamel
- A61L27/3629—Intestinal tissue, e.g. small intestinal submucosa
-
- 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
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/13—Hollow or container type article [e.g., tube, vase, etc.]
- Y10T428/1352—Polymer or resin containing [i.e., natural or synthetic]
- Y10T428/139—Open-ended, self-supporting conduit, cylinder, or tube-type article
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/24—Structurally defined web or sheet [e.g., overall dimension, etc.]
- Y10T428/24008—Structurally defined web or sheet [e.g., overall dimension, etc.] including fastener for attaching to external surface
Abstract
This invention relates to a method for preparation of a tissue graft composition from a segment of small intestine. A tissue graft composition is described which comprises the tunica submucosa of a segment of small intestine of a warm-blooded vertebrate wherein the tunica submucosa is delaminated from the tunica muscularis and at least the luminal portion of the tunica mucosa. The tissue graft composition has been shown to have excellent mechanical characteristics, as well as non-allergenicity and non-thrombogenicity in applications as vascular autografts, vascular allografts, and vascular heterografts.
Description
-l- 1335432 TISSUE GRAFT COMPOSITION AND METHOD
This invention relates to a novel tissue graft composition exhibiting strength, patency, infection resistance, non-immunogenicity, non-thombogenicity, and resistance to aneurysm formation surpassing many synthetic graft materials. More particularly, this invention is directed to tissue graft compositions comprising the submucosal and basilar mucosal portions of the small intestine and to methods for preparation and use of such compositions.
BACKGROUND OF THE INVENTION
Tissue graft materials have today attained considerable clinica1 and economic significance. It is estimated that in 1986 $130 million was spent for vascular grafts alone, not including coronary artery bypass grafts. Yet success rates for vascular graft procedures pale in comparison to those of most other surgical procedures. For example, a 5-year cumulative patency of 50% is considered excellent for small diameter vascular grafts. Such low success rates result, in large part, from one or more physical or functional deficiencies in the graft materials currently in clinical use.
Identification of materials suitable for tissue grafts is particularly difficult because such materials must possess a variety of disparate properties. For example, vascular graft materials must not only exhibit mechanical stability under continuous stress, but they 1335~32 also must have porosity adequate for capillarization, compliance similar to that of the host tissue, and high negative Zeta potentials (so as to be nonthrombogenic).
Further they should be non-allergenic, non-carcinogenic, and preferably inexpensive to fabricate.
Few, if any, tissue graft materials possess all of the desirable properties. Literature reports of research and development in the area of vascular grafts reflect a significant ongoing effort to overcome the shortcomings common to currently known graft materials.
Both synthetic and autogenous materials have been used for vascular grafts. Among synthetics, expanded polytetrafluoroethylene (PTFE) is a commonly used vascular graft material, particularly for small vessel bypass surgeries. However, expanded PTFE grafts are susceptible to neointimal hyperplasia and late graft thrombosis (e.g., 6-year patency rates of approximately 50% for femoropopliteal bypasses). PTFE grafts are reported to have even lower success rates when used in the venous circulation.
Another synthetic material - Dacron~ - is often used for large diameter vascular graft procedures (e.g., infrarenal aortic grafts). Knitted Dacron~, however, has a relatively high porosity and must be preclotted prior to implantation to avoid extensive hemorrhage. This preclotting procedure is not always practical or successful. Woven Dacron~, while less porous, demonstrates a compliance of only 20% of that found in a normal aorta. Finally, Dacron~ grafts perform poorly in small diameter arteries or veins where blood flow is relatively slow.
One of the more significant problems associated with use of synthetics as tissue graft materials is the fact that synthetic materials have low infection resistance. Infection rates following synthetic graft implantation are associated with a 66% mortality rate.
Synthetic materials tend to harbor microorganisms in their interstices and, when contaminated, are extremely refractory to antibacterial therapy. Explantation of infected synthetic grafts is virtually inevitable.
More recently researchers have reported preparation of synthetic skin and blood vessel equivalents utilizing living human cells. See U.S.
Patents 4,604,346, 4,546,500, 4,539,716, 4,485,097, and 4,48S,096.
Among autogenous materials, the saphenous vein, the human umbilical vein, the inverted small intestine, and the radial artery have all been used, but each of these materials has also exhibited significant shortcomings. The saphenous vein may be of an inappropriate size for certain procedures or may be unavailable because of damage by disease. In addition, the saphenous vein may have unacceptable varicosities and suffers from accelerated atherogenesis following "arteriolization." Both the umbilical grafts and the inverted small intestine grafts are plagued by early thrombosis and late aneurysm formation. Finally, the radial artery is of limited utility because it is difficult to harvest and may deteriorate after graft implantation.
It is therefore an ob~ect of thls lnventlon to provlde a tlssue graft materlal whlch does not exhlblt many of the shortcomlngs assoclated wlth many graft materlals now belng used cllnlcally.
Another ob~ect of thls lnventlon ls to provlde a method for preparlng a novel tlssue graft materlal from a sectlon of small lntestlne.
Stlll another ob~ect of thls lnventlon ls to provlde a method for use of a novel multl-purpose tlssue graft materlal ln autograftlng, allograftlng and heterograftlng appllcatlons.
Yet a further ob~ect of thls lnventlon ls to provlde a method for uslng a novel tlssue graft composltlon for blood vessel replacement.
BRIEF DESCRIPTION OF THE DRAWINGS
Flg. 1 ls a cross-sectlonal vlew of a sectlon of the small lntestlne.
DETAILED DESCRIPTION OF THE INVENTION
Thls lnventlon ls dlrected to a tlssue graft compositlon comprlslng the tunlca submucosa, the muscularls mucosa and the stratum compactum of the tunlca mucosa of a segment of lntestlnal tlssue of a warm-blooded vertebrate, sald tunlca submucosa, muscularls mucosa and stratum compactum belng delamlnated from the tunlca muscularls and the lumlnal portlon of the tunlca mucosa of sald segment of lntestlnal tlssue. Whlle the present tlssue graft composltlon has been shown to have excellent functlonal characterlstlcs ln appllcatlons as vascular autografts and vascular allografts, lt ls antlclpated that tlssue graft ,1 13~5432 compositions of this invention will find wide use even as heterografts in both vascular and in other tissue graft applications. Applicants have discovered that the subject tissue graft composition exhibits multiple physical and biological characteristics that renders it particularly adapted for tissue graft applications.
In a preferred embodiment of this invention, the tissue graft material comprises submucosa tissue and basilar mucosa tissue delaminated from a segment of the small intestine, more preferably the jejunum, a division of the small intestine extending between the duodenum and the ileum. The small intestine, prior to its manipulation (delamination) to yield graft material in accordance with this invention, is made up of a number of discrete tissue layers. Fig. 1 provides a cross-sectional view of the small intestine showing its discrete tissue layers labeled A through G (outer to inner, respectively) which collectively define the intestinal wall. The outermost tissue layer A
represents the mesenteric tissues. The mesenteric tissues are depicted as a distinct layer for illustrative purposes only. Ordinarily such tissues do not appear as a discrete layer, but rather appear as discontinuous tissue segments. Layers B and C represent the tunica serosa and the tunica muscularis, respectively. Layer D, the tunica submucosa, is a dense, irregular collagenous connective tissue often harboring numerous mast cells. Heparin derived from these mast cells is probably at least partially responsible for the lack of early thrombogenicity of the graft material.
Layers E, F, and G collectively represent the so-called tunica mucosa. Layer E is a layer of sm~oth muscle cells known as the lamina muscularis mucosa.
Layer F, the stratum compactum, consists of acellular collagen and elastin fibers. Layer G consists of the lamina epithelialis mucosa and its lamina propria, which together and arranged in villous processes, a series of finger-like outgrowths of the mucous membrane.
Following the below-detailed manipulation of the intestinal tissue segment to prepare the graft material of this invention, histologic examination reveals that the lamina epithelialis mucosa and its lamina propria have been removed, as have the tunica muscularis and the tunica serosa. The preferred graft material of this invention thus comprises the tunica submucosa D, along with basilar portions of the tunica mucosa, particularly the lamina muscularis mucosa E and the stratum compactum F. Those layers collectively are reerred to hereinafter as the Small Intestine Submucosa ("SIS").
A SIS autograft in accordance this invention can be prepared, for example, by first resecting a segment of autogeneous proximal jejunum following a midline laparotomy incision. The resected segment of jejunum is then wrapped in surgical sponges which have been soaked in physiologic saline. Upon completion of the intestinal anastomosis, the excised intestinal segment is prepared in accordance with the hereinafter described method of this invention for use as a tissue graft material. Similarly, allografts are prepared from intestinal tissue removed from organ/tissue donors of the same species. Heterografts can be prepared, f~r example, from feline, porcine, or bovine intestinal tissue retrieved from euthanized animals at slaughterhouse operations. To date, but minimal morphological differences have been found in intestinal tissues from different species. Indeed, the histologic appearance of human graft tissue in accordance with this invention was found to be almost identical to that of the dog. The only recognizable morphologic difference was a slightly less dense stratum compactum in the human tissue.
The tissue graft material of this invention is prepared by abrading intestinal tissue to remove the outer layers including both the tunica serosa and the tunica muscularis (layers B and C in Fig. 1) and the inner layers including at least the luminal portion (layer G) of the tunica mucosa (layers E through G in Fig. 1). Under conditions of mild abrasion the tunica mucosa is delaminated between the stratum compactum (layer F) and the lamina propria of layer G. More particularly, following removal of any mesenteric tissues from the intestinal segment utilizing, for e~ample, Adson-Brown forceps and Metzenbaum scissors, the tunica serosa and the tunica muscularis (the outer tissue layers) are delaminated from the intestinal segment by abrasion using a longitudinal wiping motion with a scalpel handle and moistened gauze. Following eversion of the intestinal segment, the luminal portion of the tunica mucosa is delaminated from the underlying tissue using the same wiping motion. Care is taken to prevent perforation of the submucosa. Also, any tissue "tags" from the delaminated layers remaining on the graft surface are removed. Optionally, the intestinal segment may be everted first, then stripped of the luminal layers, then reinserted to its original orientation for removal of the tunica serosa and the tunica muscularis. The graft material is a whitish, translucent tube of tissue approximately 0.1 mm thick, typically consisting of the tunica submucosa with the attached lamina muscularis mucosa and stratum compactum. For vascular graft preparation, the prepared graft is everted to its original orientation so that the stratum compactum serves as ~he luminal surface of the graft.
The prepared graft material is typically rinsed with saline and placed in a 10% neomycin sulfate solution for approximately 20 minutes, after which time the graft material is ready for use. The grafts are applied using routine surgical procedures commonly employed for tissue graft applications. For use in non-vascular tissue graft applications, the tubular graft material can be cut longitudinally and rolled out to form a "patch" of tissue. Indeed, the entire tissue delamination procedure described above can be carried out on "patches~ of intestinal tissue prepared by cutting the intestinal segment longitudinally and "unrolling" it to form a pre-graft patch. The prepared graft tissue patches can be utilized, for example, as a skin graft material or for repair of other body tissue defects lending themselves to surgical application of a tissue graft patch having the physical and functio~al characteristics of the present graft composition.
For use in vascular grafts, the diameter of the graft should be about the same as the diameter of the recipient blood vessel. This is accomplished by manipulating the tissue graft to define a cylinder having a diameter approximately the same as that of the recipient blood vessel and suturing or otherwise securing the tissue graft longitudinally to form said vascular graft. Thus, for example, a vascular graft can be prepared by selecting a sterile glass rod having an outer diameter equal to that of the recipient blood vessel and introducing the qlass rod into the graft lumen. Redundant tissue is then gathered and the desired lumen diameter achieved by suturing along the length of the graft (for example, using two continuous suture lines or a simple interrupted suture line) or by using other art-recognized tissue securing techniques.
Consistent with the objects of this invention, the SIS composition possesses mechanical properties highly desirable for tissue graft materials, including low porosity index, high compliance, and a high burst pressure point. As for porosity, one skilled in the art will appreciate that tissue graft material must be of low enough porosity to prevent intraoperative hemorrhage and yet of high enough porosity to allow extension of a newly-developed vasa vasorum through the graft material to nourish the neointima and luminal surface. Porosity of a graft material is typically measured in terms of ml -lO- 1335432 of water passed per cm2min 1 at a pressure head of 120 mm ~g. The porosity index of the SIS graft material is 10, much lower than other graft materials currently known in the art. (Woven Dacron~, for example, has a porosity index of 50). Yet despite this low porosity index, SIS is still sufficiently porous to allow neocapillarization to occur within the SIS graft. In vascular graft applications SIS compositions allow for the formation of blood-filled capillaries within the graft wall extending to the luminal surface as early as four days after surgery.
Regarding graft compliance, there has been described in the art the existence of a direct relationship between compliance and patency. Ideally a graft material should be at least as compliant as the tissue it replaces; Longitudinal compliance of the SIS
graft material was measured through use of a simple tensile test. An initial gage length was formed with two ink marks 5.0 cm apart. The elongation and applied force were measured as the samples were loaded at a tension rate of 32 cm/cm/min, yielding the following results:
Compliance of SIS graft: 0.045 cm/N per cm of length Compliance of normal dog aorta: 0.017 cm/N per cm of length Thus, SIS graft materials actually exhibit compliance qreater than that of the normal aorta. This is a significant advance over the prior art in the vascular graft area. All presently available synthetic grafts are 3 to 10 times less compliant than the natural artery and proportionately more prone to thrombosis than the natural artery. The prior art method of compensating for this compliance mismatch is to use a graft material larger in diameter than the adjacent natural artery.
This technique, however, has lead to additional problems. Blood velocity is slower through the larger diameter graft segment. Hence, there is less shear stress at the graft wall. Under such conditions, platelet and fibrin deposition and subsequent thrombosis are more likely. In contrast, because the SIS material demonstrates such high compliance, isodiametric SIS
grafts can be used without occurrence of such problems.
The present SIS graft material was found to have a burst pressure point well beyond what would be encountered physiologically. A burst pressure test was conducted by attaching a tubular SIS graft segment to two 25 mm diameter cylinders and pressurizing the graft with nitrogen gas at a constant flow rate. Two flow rates were used. At the lower flow rate, pressure initially increased, then dropped off and steadied as the gas outflow through the graft wall equilibrated with the gas inflow. At the higher flow rate, the pressure built up immediately to burst conditions at approximately 400 mm Hg, indicating that the graft material can easily withstand the continuous pulsatile pressures encountered in normal physiological vascular graft usage.
EXAMPLES
Example 1. Small Intestinal Submucosa as a Larqe Diameter Arterial Graft A series of experiments have been conducted which tested the ability of three different configurations of small intestine to serve as a vascular graft in the infrarenal aorta of the dog. The first experiment utilized a full thickness, non-inverted segment of jejunum, either with an intact mesenteric neurovascular supply or with a free, isolated segment as the graft material. The intestinal mucosa was the blood-graft interface. All 4 dogs in this experiment died within 18 hours of surgery from thrombosis of the graft segment and hemorrhage from the suture lines.
The second experiment utilized an isolated and inverted segment of jejunum as the graft with the tunica serosa serving as the blood-graft interface. There were 2 dogs in this experiment. The graft in the first dog was thrombosed within 4 hours of surgery, and the second dog died from acute hemorrhage at the proximal anastomosis site 4 days following surgery.
The third experiment tested the use of only a portion of the intestinal wall as the graft material. A
free segment of autogenous upper jejunum was harvested from each dog and then the majority of mucosa was removed by bluntly scraping the luminal surface with a scalpel handle. By the same procedure, the serosa and tunica muscularis were then removed. The tissue that remained after this seemingly brutal manipulation of the gut segment was a 100 ~ thick section of submucosa and 1 33S~32 basilar mucosa. This graft was then placed in the infrarenal aorta of 15 dogs and has been remarkably successful. The results of this third experiment are - summarized below.
Thirteen of the 15 dogs maintained patent grafts until the time of euthanasia. Eleven dogs were euthanized at various times after surgery ranging from 4 days until 1 year. The animals showed no signs of graft infection, aneurysm formation, or thrombosis. The graft failure observed in two of the dogs was caused by technical error, including misplacement of metal ligaclips and poor anastomosis technique. Two animals remain alive at the time of this writing and are being monitored for more long term graft patency.
The patency of the grafts was verified by positive contrast radiography within four to seven ~ays after the surgery and every 6 to 8 weeks thereafter. In addition, the graft patency was monitored clinically by observing the presence of a strong femoral pulse and the lack of hind limb edema.
Eleven of the dogs maintaining patent grafts were sacrificed at various post-surgery time intervals (4, 7, 10 and 14 days, and 9, 11, 13, 17, 26, 44, and 52 weeks). Just prior to euthanasia, the animals had an additional angiogram to confirm graft patency and to provide a comparative radiograph for evaluation of graft dilatation, stenosis, and aneurysm formation. All eleven of the animals showed complete patency with no evidence of detrimental luminal changes.
133~432 Gross pathologic evaluation of these graft segments showed a glistening luminal surface with .
haphazardly arranged red and white areas and no evidence of propagating thrombus formation. There was a surrounding firm connective tissue accumulation which was confluent with the graft wall. All specimens examined prior to 6 months after surgery showed no evidence of endothelial cell growth on the surface of the graft. The surface of these grafts were covered with a flat, moderately dense and organized layer of collagen.
Histopathologic examination of the 26, 44 and 52 week specimens showed a flattened, "endothelial-like"
cell which partially covered a thin (approximately 500~) layer of densely organized fibrin. The entire tissue was infiltrated with blood-filled capillaries, and the outer border of the original graft material could not be distinguished from the surrounding connective tissue. Scanning electron microscopic examination of the luminal surface showed a layer of flattened cells, indistinguishable from endothelial cells, with extended "pseudopodia". Transmission electron microscopic evaluation of these graft segments also suggested the presence of an endothelial cell covering of the luminal surface. In addition, the presence of Factor VIII: Related Antigen, detected by immunofluorescent staining, further suggested the endothelial origin of these graft luminal surface cells. The graft material was also tested for endothelial cell presence by testing for the presence of endothelium derived relaxing factor. Acetylcholine was applied to the surface of graft specimens and the effluent collected. The effluent was shown through observation of smooth muscle relaxation in a rat aorta preparation to contain endothelium-derived relaxing factor.
The blood pressure cephalad to, distal to, and within the SIS graft was determined in each of the 10 euthanized dogs. The pressures were identical at all 3 locations in each of the dogs, reflecting a lack of adverse hemodynamic effects arising through use of the SIS graft material.
The following laboratory parameters were measured before surgery, one day after surgery, then at additional times during subsequent months in all dogs:
hematocrit, prothrombin time, activated partial thromboplastin time, platelet count, complete blood count, and an abbreviated serum chemistry profile.
Results showed all animals to be normal by these laboratory measurements at all times. These animals were given low dose heparin treatment (600 units IV) during the surgical procedure, but were not anticoagulated during the postoperative period. The lack of any changes in the coagulation tests and platelet counts was particularly encouraging in light of the relatively hyperactive coagulation system of the dog compared to man.
Example 2. Small Intestinal Submucosa as a Small Diameter Arterial ~raft This experiment involved the implantation in eighteen dogs of a total of 36 qrafts in both the S femoral artery and the carotid artery. Thirty-three o the thirty-six grafts remained patent. Identical laboratory measurements were made in these animals as were made in the first study and no abnormalities were observed. In addition, conventional 2-dimensional ultrasound imaging was used to-measure patency and cross-sectional vessel diameter.
Pathologic examination of graft tissue from a dog euthanized four days after surgery showed a nonthrombotic luminal surface and a mildly stenotic proximal anastomosis. Histologic examination revealed the early presence of blood-filled capillaries within the graft wall, a potential natural body defense to infection. Five of these dogs remain alive at the time of this writing for further evaluation. The longest surviving dog in the study is now 7 months post-surqery.
ExamPle 3. Small Intestinal Submucosa as a Venous Graft In this experiment, the SIS graft was placed in the posterior vena cava (analogous to the "inferior"
vena cava in man) of two dogs and in the anterior vena cava (analogous to the "superior" vena cava in man) of five dogs. Although the posterior vena cava grafts remained patent for only 11 and 14 days respectively, pathologic examination showed failure of the grafts to be attributable to technical errors in which the 133S~32 inferior anastomosis site was stenotic (8 mm in diameter as versus the adjacent 16 mm diameter natural vena cava and proximal graft). Moreover, the luminal surfaces of both grafts were covered with a nonthrombotic "psuedoenthelium" composed of tightly packed fibrin and immature collagenous connective tissue.
The anterior vena cava grafts remained patent until euthanasia of three of the dogs at 7, 14, and 21 days respectively, after surgery. Two of the dogs remain alive at the time of this writing with patent grafts at 7 weeks after surgery. The proximal suture line in all three dogs showed evidence of early thrombosis where a flap of the graft had been inverted and was causing turbulent blood flow, but the remainder of the graft was nonthrombotic. In addition, gross pathologic and histologic examinations revealed that the graft was lined by a glistening, smooth red surface identical in appearance to early grafts studied in previous experiments.
E~ample 4. Small Intestinal Submucosa as an Arterial Alloqraft SIS has been used as a large diameter allograft in the dog aorta. The allografts were constructed in the same manner as those described above for our study of aortic autografts. At the time of this writing the test animals are only 8 weeks post surgery, but they show no signs of graft thrombosis, infection or aneurysm formation (as documented by angiograms).
Example 5. Small Intestinal Submucosa as an Arterial Heteroqraft SIS has been used as a heterograft in the dog.
A SIS graft of feline origin was prepared in accordance with the procedures hereinbefore described and placed in a dog. At the time of this writing, the test animal was two weeks post-surgery and showing no adverse signs.
This invention relates to a novel tissue graft composition exhibiting strength, patency, infection resistance, non-immunogenicity, non-thombogenicity, and resistance to aneurysm formation surpassing many synthetic graft materials. More particularly, this invention is directed to tissue graft compositions comprising the submucosal and basilar mucosal portions of the small intestine and to methods for preparation and use of such compositions.
BACKGROUND OF THE INVENTION
Tissue graft materials have today attained considerable clinica1 and economic significance. It is estimated that in 1986 $130 million was spent for vascular grafts alone, not including coronary artery bypass grafts. Yet success rates for vascular graft procedures pale in comparison to those of most other surgical procedures. For example, a 5-year cumulative patency of 50% is considered excellent for small diameter vascular grafts. Such low success rates result, in large part, from one or more physical or functional deficiencies in the graft materials currently in clinical use.
Identification of materials suitable for tissue grafts is particularly difficult because such materials must possess a variety of disparate properties. For example, vascular graft materials must not only exhibit mechanical stability under continuous stress, but they 1335~32 also must have porosity adequate for capillarization, compliance similar to that of the host tissue, and high negative Zeta potentials (so as to be nonthrombogenic).
Further they should be non-allergenic, non-carcinogenic, and preferably inexpensive to fabricate.
Few, if any, tissue graft materials possess all of the desirable properties. Literature reports of research and development in the area of vascular grafts reflect a significant ongoing effort to overcome the shortcomings common to currently known graft materials.
Both synthetic and autogenous materials have been used for vascular grafts. Among synthetics, expanded polytetrafluoroethylene (PTFE) is a commonly used vascular graft material, particularly for small vessel bypass surgeries. However, expanded PTFE grafts are susceptible to neointimal hyperplasia and late graft thrombosis (e.g., 6-year patency rates of approximately 50% for femoropopliteal bypasses). PTFE grafts are reported to have even lower success rates when used in the venous circulation.
Another synthetic material - Dacron~ - is often used for large diameter vascular graft procedures (e.g., infrarenal aortic grafts). Knitted Dacron~, however, has a relatively high porosity and must be preclotted prior to implantation to avoid extensive hemorrhage. This preclotting procedure is not always practical or successful. Woven Dacron~, while less porous, demonstrates a compliance of only 20% of that found in a normal aorta. Finally, Dacron~ grafts perform poorly in small diameter arteries or veins where blood flow is relatively slow.
One of the more significant problems associated with use of synthetics as tissue graft materials is the fact that synthetic materials have low infection resistance. Infection rates following synthetic graft implantation are associated with a 66% mortality rate.
Synthetic materials tend to harbor microorganisms in their interstices and, when contaminated, are extremely refractory to antibacterial therapy. Explantation of infected synthetic grafts is virtually inevitable.
More recently researchers have reported preparation of synthetic skin and blood vessel equivalents utilizing living human cells. See U.S.
Patents 4,604,346, 4,546,500, 4,539,716, 4,485,097, and 4,48S,096.
Among autogenous materials, the saphenous vein, the human umbilical vein, the inverted small intestine, and the radial artery have all been used, but each of these materials has also exhibited significant shortcomings. The saphenous vein may be of an inappropriate size for certain procedures or may be unavailable because of damage by disease. In addition, the saphenous vein may have unacceptable varicosities and suffers from accelerated atherogenesis following "arteriolization." Both the umbilical grafts and the inverted small intestine grafts are plagued by early thrombosis and late aneurysm formation. Finally, the radial artery is of limited utility because it is difficult to harvest and may deteriorate after graft implantation.
It is therefore an ob~ect of thls lnventlon to provlde a tlssue graft materlal whlch does not exhlblt many of the shortcomlngs assoclated wlth many graft materlals now belng used cllnlcally.
Another ob~ect of thls lnventlon ls to provlde a method for preparlng a novel tlssue graft materlal from a sectlon of small lntestlne.
Stlll another ob~ect of thls lnventlon ls to provlde a method for use of a novel multl-purpose tlssue graft materlal ln autograftlng, allograftlng and heterograftlng appllcatlons.
Yet a further ob~ect of thls lnventlon ls to provlde a method for uslng a novel tlssue graft composltlon for blood vessel replacement.
BRIEF DESCRIPTION OF THE DRAWINGS
Flg. 1 ls a cross-sectlonal vlew of a sectlon of the small lntestlne.
DETAILED DESCRIPTION OF THE INVENTION
Thls lnventlon ls dlrected to a tlssue graft compositlon comprlslng the tunlca submucosa, the muscularls mucosa and the stratum compactum of the tunlca mucosa of a segment of lntestlnal tlssue of a warm-blooded vertebrate, sald tunlca submucosa, muscularls mucosa and stratum compactum belng delamlnated from the tunlca muscularls and the lumlnal portlon of the tunlca mucosa of sald segment of lntestlnal tlssue. Whlle the present tlssue graft composltlon has been shown to have excellent functlonal characterlstlcs ln appllcatlons as vascular autografts and vascular allografts, lt ls antlclpated that tlssue graft ,1 13~5432 compositions of this invention will find wide use even as heterografts in both vascular and in other tissue graft applications. Applicants have discovered that the subject tissue graft composition exhibits multiple physical and biological characteristics that renders it particularly adapted for tissue graft applications.
In a preferred embodiment of this invention, the tissue graft material comprises submucosa tissue and basilar mucosa tissue delaminated from a segment of the small intestine, more preferably the jejunum, a division of the small intestine extending between the duodenum and the ileum. The small intestine, prior to its manipulation (delamination) to yield graft material in accordance with this invention, is made up of a number of discrete tissue layers. Fig. 1 provides a cross-sectional view of the small intestine showing its discrete tissue layers labeled A through G (outer to inner, respectively) which collectively define the intestinal wall. The outermost tissue layer A
represents the mesenteric tissues. The mesenteric tissues are depicted as a distinct layer for illustrative purposes only. Ordinarily such tissues do not appear as a discrete layer, but rather appear as discontinuous tissue segments. Layers B and C represent the tunica serosa and the tunica muscularis, respectively. Layer D, the tunica submucosa, is a dense, irregular collagenous connective tissue often harboring numerous mast cells. Heparin derived from these mast cells is probably at least partially responsible for the lack of early thrombogenicity of the graft material.
Layers E, F, and G collectively represent the so-called tunica mucosa. Layer E is a layer of sm~oth muscle cells known as the lamina muscularis mucosa.
Layer F, the stratum compactum, consists of acellular collagen and elastin fibers. Layer G consists of the lamina epithelialis mucosa and its lamina propria, which together and arranged in villous processes, a series of finger-like outgrowths of the mucous membrane.
Following the below-detailed manipulation of the intestinal tissue segment to prepare the graft material of this invention, histologic examination reveals that the lamina epithelialis mucosa and its lamina propria have been removed, as have the tunica muscularis and the tunica serosa. The preferred graft material of this invention thus comprises the tunica submucosa D, along with basilar portions of the tunica mucosa, particularly the lamina muscularis mucosa E and the stratum compactum F. Those layers collectively are reerred to hereinafter as the Small Intestine Submucosa ("SIS").
A SIS autograft in accordance this invention can be prepared, for example, by first resecting a segment of autogeneous proximal jejunum following a midline laparotomy incision. The resected segment of jejunum is then wrapped in surgical sponges which have been soaked in physiologic saline. Upon completion of the intestinal anastomosis, the excised intestinal segment is prepared in accordance with the hereinafter described method of this invention for use as a tissue graft material. Similarly, allografts are prepared from intestinal tissue removed from organ/tissue donors of the same species. Heterografts can be prepared, f~r example, from feline, porcine, or bovine intestinal tissue retrieved from euthanized animals at slaughterhouse operations. To date, but minimal morphological differences have been found in intestinal tissues from different species. Indeed, the histologic appearance of human graft tissue in accordance with this invention was found to be almost identical to that of the dog. The only recognizable morphologic difference was a slightly less dense stratum compactum in the human tissue.
The tissue graft material of this invention is prepared by abrading intestinal tissue to remove the outer layers including both the tunica serosa and the tunica muscularis (layers B and C in Fig. 1) and the inner layers including at least the luminal portion (layer G) of the tunica mucosa (layers E through G in Fig. 1). Under conditions of mild abrasion the tunica mucosa is delaminated between the stratum compactum (layer F) and the lamina propria of layer G. More particularly, following removal of any mesenteric tissues from the intestinal segment utilizing, for e~ample, Adson-Brown forceps and Metzenbaum scissors, the tunica serosa and the tunica muscularis (the outer tissue layers) are delaminated from the intestinal segment by abrasion using a longitudinal wiping motion with a scalpel handle and moistened gauze. Following eversion of the intestinal segment, the luminal portion of the tunica mucosa is delaminated from the underlying tissue using the same wiping motion. Care is taken to prevent perforation of the submucosa. Also, any tissue "tags" from the delaminated layers remaining on the graft surface are removed. Optionally, the intestinal segment may be everted first, then stripped of the luminal layers, then reinserted to its original orientation for removal of the tunica serosa and the tunica muscularis. The graft material is a whitish, translucent tube of tissue approximately 0.1 mm thick, typically consisting of the tunica submucosa with the attached lamina muscularis mucosa and stratum compactum. For vascular graft preparation, the prepared graft is everted to its original orientation so that the stratum compactum serves as ~he luminal surface of the graft.
The prepared graft material is typically rinsed with saline and placed in a 10% neomycin sulfate solution for approximately 20 minutes, after which time the graft material is ready for use. The grafts are applied using routine surgical procedures commonly employed for tissue graft applications. For use in non-vascular tissue graft applications, the tubular graft material can be cut longitudinally and rolled out to form a "patch" of tissue. Indeed, the entire tissue delamination procedure described above can be carried out on "patches~ of intestinal tissue prepared by cutting the intestinal segment longitudinally and "unrolling" it to form a pre-graft patch. The prepared graft tissue patches can be utilized, for example, as a skin graft material or for repair of other body tissue defects lending themselves to surgical application of a tissue graft patch having the physical and functio~al characteristics of the present graft composition.
For use in vascular grafts, the diameter of the graft should be about the same as the diameter of the recipient blood vessel. This is accomplished by manipulating the tissue graft to define a cylinder having a diameter approximately the same as that of the recipient blood vessel and suturing or otherwise securing the tissue graft longitudinally to form said vascular graft. Thus, for example, a vascular graft can be prepared by selecting a sterile glass rod having an outer diameter equal to that of the recipient blood vessel and introducing the qlass rod into the graft lumen. Redundant tissue is then gathered and the desired lumen diameter achieved by suturing along the length of the graft (for example, using two continuous suture lines or a simple interrupted suture line) or by using other art-recognized tissue securing techniques.
Consistent with the objects of this invention, the SIS composition possesses mechanical properties highly desirable for tissue graft materials, including low porosity index, high compliance, and a high burst pressure point. As for porosity, one skilled in the art will appreciate that tissue graft material must be of low enough porosity to prevent intraoperative hemorrhage and yet of high enough porosity to allow extension of a newly-developed vasa vasorum through the graft material to nourish the neointima and luminal surface. Porosity of a graft material is typically measured in terms of ml -lO- 1335432 of water passed per cm2min 1 at a pressure head of 120 mm ~g. The porosity index of the SIS graft material is 10, much lower than other graft materials currently known in the art. (Woven Dacron~, for example, has a porosity index of 50). Yet despite this low porosity index, SIS is still sufficiently porous to allow neocapillarization to occur within the SIS graft. In vascular graft applications SIS compositions allow for the formation of blood-filled capillaries within the graft wall extending to the luminal surface as early as four days after surgery.
Regarding graft compliance, there has been described in the art the existence of a direct relationship between compliance and patency. Ideally a graft material should be at least as compliant as the tissue it replaces; Longitudinal compliance of the SIS
graft material was measured through use of a simple tensile test. An initial gage length was formed with two ink marks 5.0 cm apart. The elongation and applied force were measured as the samples were loaded at a tension rate of 32 cm/cm/min, yielding the following results:
Compliance of SIS graft: 0.045 cm/N per cm of length Compliance of normal dog aorta: 0.017 cm/N per cm of length Thus, SIS graft materials actually exhibit compliance qreater than that of the normal aorta. This is a significant advance over the prior art in the vascular graft area. All presently available synthetic grafts are 3 to 10 times less compliant than the natural artery and proportionately more prone to thrombosis than the natural artery. The prior art method of compensating for this compliance mismatch is to use a graft material larger in diameter than the adjacent natural artery.
This technique, however, has lead to additional problems. Blood velocity is slower through the larger diameter graft segment. Hence, there is less shear stress at the graft wall. Under such conditions, platelet and fibrin deposition and subsequent thrombosis are more likely. In contrast, because the SIS material demonstrates such high compliance, isodiametric SIS
grafts can be used without occurrence of such problems.
The present SIS graft material was found to have a burst pressure point well beyond what would be encountered physiologically. A burst pressure test was conducted by attaching a tubular SIS graft segment to two 25 mm diameter cylinders and pressurizing the graft with nitrogen gas at a constant flow rate. Two flow rates were used. At the lower flow rate, pressure initially increased, then dropped off and steadied as the gas outflow through the graft wall equilibrated with the gas inflow. At the higher flow rate, the pressure built up immediately to burst conditions at approximately 400 mm Hg, indicating that the graft material can easily withstand the continuous pulsatile pressures encountered in normal physiological vascular graft usage.
EXAMPLES
Example 1. Small Intestinal Submucosa as a Larqe Diameter Arterial Graft A series of experiments have been conducted which tested the ability of three different configurations of small intestine to serve as a vascular graft in the infrarenal aorta of the dog. The first experiment utilized a full thickness, non-inverted segment of jejunum, either with an intact mesenteric neurovascular supply or with a free, isolated segment as the graft material. The intestinal mucosa was the blood-graft interface. All 4 dogs in this experiment died within 18 hours of surgery from thrombosis of the graft segment and hemorrhage from the suture lines.
The second experiment utilized an isolated and inverted segment of jejunum as the graft with the tunica serosa serving as the blood-graft interface. There were 2 dogs in this experiment. The graft in the first dog was thrombosed within 4 hours of surgery, and the second dog died from acute hemorrhage at the proximal anastomosis site 4 days following surgery.
The third experiment tested the use of only a portion of the intestinal wall as the graft material. A
free segment of autogenous upper jejunum was harvested from each dog and then the majority of mucosa was removed by bluntly scraping the luminal surface with a scalpel handle. By the same procedure, the serosa and tunica muscularis were then removed. The tissue that remained after this seemingly brutal manipulation of the gut segment was a 100 ~ thick section of submucosa and 1 33S~32 basilar mucosa. This graft was then placed in the infrarenal aorta of 15 dogs and has been remarkably successful. The results of this third experiment are - summarized below.
Thirteen of the 15 dogs maintained patent grafts until the time of euthanasia. Eleven dogs were euthanized at various times after surgery ranging from 4 days until 1 year. The animals showed no signs of graft infection, aneurysm formation, or thrombosis. The graft failure observed in two of the dogs was caused by technical error, including misplacement of metal ligaclips and poor anastomosis technique. Two animals remain alive at the time of this writing and are being monitored for more long term graft patency.
The patency of the grafts was verified by positive contrast radiography within four to seven ~ays after the surgery and every 6 to 8 weeks thereafter. In addition, the graft patency was monitored clinically by observing the presence of a strong femoral pulse and the lack of hind limb edema.
Eleven of the dogs maintaining patent grafts were sacrificed at various post-surgery time intervals (4, 7, 10 and 14 days, and 9, 11, 13, 17, 26, 44, and 52 weeks). Just prior to euthanasia, the animals had an additional angiogram to confirm graft patency and to provide a comparative radiograph for evaluation of graft dilatation, stenosis, and aneurysm formation. All eleven of the animals showed complete patency with no evidence of detrimental luminal changes.
133~432 Gross pathologic evaluation of these graft segments showed a glistening luminal surface with .
haphazardly arranged red and white areas and no evidence of propagating thrombus formation. There was a surrounding firm connective tissue accumulation which was confluent with the graft wall. All specimens examined prior to 6 months after surgery showed no evidence of endothelial cell growth on the surface of the graft. The surface of these grafts were covered with a flat, moderately dense and organized layer of collagen.
Histopathologic examination of the 26, 44 and 52 week specimens showed a flattened, "endothelial-like"
cell which partially covered a thin (approximately 500~) layer of densely organized fibrin. The entire tissue was infiltrated with blood-filled capillaries, and the outer border of the original graft material could not be distinguished from the surrounding connective tissue. Scanning electron microscopic examination of the luminal surface showed a layer of flattened cells, indistinguishable from endothelial cells, with extended "pseudopodia". Transmission electron microscopic evaluation of these graft segments also suggested the presence of an endothelial cell covering of the luminal surface. In addition, the presence of Factor VIII: Related Antigen, detected by immunofluorescent staining, further suggested the endothelial origin of these graft luminal surface cells. The graft material was also tested for endothelial cell presence by testing for the presence of endothelium derived relaxing factor. Acetylcholine was applied to the surface of graft specimens and the effluent collected. The effluent was shown through observation of smooth muscle relaxation in a rat aorta preparation to contain endothelium-derived relaxing factor.
The blood pressure cephalad to, distal to, and within the SIS graft was determined in each of the 10 euthanized dogs. The pressures were identical at all 3 locations in each of the dogs, reflecting a lack of adverse hemodynamic effects arising through use of the SIS graft material.
The following laboratory parameters were measured before surgery, one day after surgery, then at additional times during subsequent months in all dogs:
hematocrit, prothrombin time, activated partial thromboplastin time, platelet count, complete blood count, and an abbreviated serum chemistry profile.
Results showed all animals to be normal by these laboratory measurements at all times. These animals were given low dose heparin treatment (600 units IV) during the surgical procedure, but were not anticoagulated during the postoperative period. The lack of any changes in the coagulation tests and platelet counts was particularly encouraging in light of the relatively hyperactive coagulation system of the dog compared to man.
Example 2. Small Intestinal Submucosa as a Small Diameter Arterial ~raft This experiment involved the implantation in eighteen dogs of a total of 36 qrafts in both the S femoral artery and the carotid artery. Thirty-three o the thirty-six grafts remained patent. Identical laboratory measurements were made in these animals as were made in the first study and no abnormalities were observed. In addition, conventional 2-dimensional ultrasound imaging was used to-measure patency and cross-sectional vessel diameter.
Pathologic examination of graft tissue from a dog euthanized four days after surgery showed a nonthrombotic luminal surface and a mildly stenotic proximal anastomosis. Histologic examination revealed the early presence of blood-filled capillaries within the graft wall, a potential natural body defense to infection. Five of these dogs remain alive at the time of this writing for further evaluation. The longest surviving dog in the study is now 7 months post-surqery.
ExamPle 3. Small Intestinal Submucosa as a Venous Graft In this experiment, the SIS graft was placed in the posterior vena cava (analogous to the "inferior"
vena cava in man) of two dogs and in the anterior vena cava (analogous to the "superior" vena cava in man) of five dogs. Although the posterior vena cava grafts remained patent for only 11 and 14 days respectively, pathologic examination showed failure of the grafts to be attributable to technical errors in which the 133S~32 inferior anastomosis site was stenotic (8 mm in diameter as versus the adjacent 16 mm diameter natural vena cava and proximal graft). Moreover, the luminal surfaces of both grafts were covered with a nonthrombotic "psuedoenthelium" composed of tightly packed fibrin and immature collagenous connective tissue.
The anterior vena cava grafts remained patent until euthanasia of three of the dogs at 7, 14, and 21 days respectively, after surgery. Two of the dogs remain alive at the time of this writing with patent grafts at 7 weeks after surgery. The proximal suture line in all three dogs showed evidence of early thrombosis where a flap of the graft had been inverted and was causing turbulent blood flow, but the remainder of the graft was nonthrombotic. In addition, gross pathologic and histologic examinations revealed that the graft was lined by a glistening, smooth red surface identical in appearance to early grafts studied in previous experiments.
E~ample 4. Small Intestinal Submucosa as an Arterial Alloqraft SIS has been used as a large diameter allograft in the dog aorta. The allografts were constructed in the same manner as those described above for our study of aortic autografts. At the time of this writing the test animals are only 8 weeks post surgery, but they show no signs of graft thrombosis, infection or aneurysm formation (as documented by angiograms).
Example 5. Small Intestinal Submucosa as an Arterial Heteroqraft SIS has been used as a heterograft in the dog.
A SIS graft of feline origin was prepared in accordance with the procedures hereinbefore described and placed in a dog. At the time of this writing, the test animal was two weeks post-surgery and showing no adverse signs.
Claims (6)
1. A tissue graft composition comprising the tunica submucosa, the muscularis mucosa and the stratum compactum of the tunica mucosa of a segment of intestinal tissue of a warm-blooded vertebrate, said tunica submucosa, muscularis mucosa and stratum compactum being delaminated from the tunica muscularis and the luminal portion of the tunica mucosa of said segment of intestinal tissue.
2. The tissue graft composition of claim 1 formed into a cylinder having a predetermined luminal diameter and sutured along the length of the cylinder.
3. The tissue graft composition of claim 2 wherein the stratum compactum forms the luminal surface of the cylinder.
4. The tissue graft composition of claim 1 wherein the segment of intestinal tissue is excised from the jejunum.
5. The tissue graft composition of claim 4 formed into a cylinder having a predetermined luminal diameter and sutured along the length of the cylinder.
6. The tissue graft composition of claim 5 wherein the stratum compactum forms the luminal surface of the cylinder.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US07/217,299 US4902508A (en) | 1988-07-11 | 1988-07-11 | Tissue graft composition |
US217,299 | 1988-07-11 |
Publications (1)
Publication Number | Publication Date |
---|---|
CA1335432C true CA1335432C (en) | 1995-05-02 |
Family
ID=22810477
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA000605031A Expired - Lifetime CA1335432C (en) | 1988-07-11 | 1989-07-07 | Tissue graft composition and method |
Country Status (25)
Country | Link |
---|---|
US (1) | US4902508A (en) |
EP (1) | EP0424463B1 (en) |
JP (1) | JP2539934B2 (en) |
KR (1) | KR0131821B1 (en) |
CN (1) | CN1018893B (en) |
AR (1) | AR244539A1 (en) |
AT (1) | ATE112963T1 (en) |
AU (1) | AU613499B2 (en) |
BR (1) | BR8907538A (en) |
CA (1) | CA1335432C (en) |
CH (2) | CH681506A5 (en) |
DE (1) | DE68918943T2 (en) |
DK (1) | DK175719B2 (en) |
ES (1) | ES2019146A6 (en) |
FI (1) | FI910113A0 (en) |
HU (1) | HU207448B (en) |
IE (1) | IE67279B1 (en) |
IL (1) | IL90622A (en) |
MX (1) | MX171671B (en) |
NZ (1) | NZ229797A (en) |
OA (1) | OA09633A (en) |
PH (1) | PH26921A (en) |
PT (1) | PT91096B (en) |
WO (1) | WO1990000395A1 (en) |
ZA (1) | ZA894551B (en) |
Families Citing this family (618)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6171338B1 (en) * | 1988-11-10 | 2001-01-09 | Biocon, Oy | Biodegradable surgical implants and devices |
US5281422A (en) * | 1991-09-24 | 1994-01-25 | Purdue Research Foundation | Graft for promoting autogenous tissue growth |
DE69325649T2 (en) * | 1992-03-13 | 1999-11-18 | Atrium Medical Corp | OBJECTS OF EXPANDED FLUOROPOLYMER (e.g. POLYTETRAFLUORETHYLENE) WITH CONTROLLED POROSITY AND ITS PRODUCTION |
US5800537A (en) | 1992-08-07 | 1998-09-01 | Tissue Engineering, Inc. | Method and construct for producing graft tissue from an extracellular matrix |
DE69333466T2 (en) * | 1992-08-07 | 2004-08-19 | TEI Biosciences, Inc., Boston | PRODUCTION OF TRANSPLANT TISSUE FROM EXTRACELLULAR MATRIX |
US5300306A (en) * | 1992-09-29 | 1994-04-05 | Alvarado Carlos A | Tissue-equivalent membrane from bovine esophageal tissue |
US5641518A (en) * | 1992-11-13 | 1997-06-24 | Purdue Research Foundation | Method of repairing bone tissue |
US6653291B1 (en) * | 1992-11-13 | 2003-11-25 | Purdue Research Foundation | Composition and method for production of transformed cells |
US5275826A (en) * | 1992-11-13 | 1994-01-04 | Purdue Research Foundation | Fluidized intestinal submucosa and its use as an injectable tissue graft |
US5352463A (en) * | 1992-11-13 | 1994-10-04 | Badylak Steven F | Tissue graft for surgical reconstruction of a collagenous meniscus and method therefor |
CA2183056C (en) * | 1994-02-18 | 2001-07-10 | Paul L. Termin | Bioremodelable collagen graft prosthesis |
US6334872B1 (en) * | 1994-02-18 | 2002-01-01 | Organogenesis Inc. | Method for treating diseased or damaged organs |
US5942496A (en) * | 1994-02-18 | 1999-08-24 | The Regent Of The University Of Michigan | Methods and compositions for multiple gene transfer into bone cells |
US6074840A (en) * | 1994-02-18 | 2000-06-13 | The Regents Of The University Of Michigan | Recombinant production of latent TGF-beta binding protein-3 (LTBP-3) |
US5962427A (en) * | 1994-02-18 | 1999-10-05 | The Regent Of The University Of Michigan | In vivo gene transfer methods for wound healing |
US5763416A (en) * | 1994-02-18 | 1998-06-09 | The Regent Of The University Of Michigan | Gene transfer into bone cells and tissues |
US20020193338A1 (en) * | 1994-02-18 | 2002-12-19 | Goldstein Steven A. | In vivo gene transfer methods for wound healing |
US6551618B2 (en) | 1994-03-15 | 2003-04-22 | University Of Birmingham | Compositions and methods for delivery of agents for neuronal regeneration and survival |
DE69534640T2 (en) * | 1994-04-29 | 2006-08-10 | Scimed Life Systems, Inc., Maple Grove | Stent with collagen |
US6475232B1 (en) * | 1996-12-10 | 2002-11-05 | Purdue Research Foundation | Stent with reduced thrombogenicity |
US5702419A (en) * | 1994-09-21 | 1997-12-30 | Wake Forest University | Expandable, intraluminal stents |
US5562946A (en) * | 1994-11-02 | 1996-10-08 | Tissue Engineering, Inc. | Apparatus and method for spinning and processing collagen fiber |
US5891558A (en) * | 1994-11-22 | 1999-04-06 | Tissue Engineering, Inc. | Biopolymer foams for use in tissue repair and reconstruction |
US5709934A (en) * | 1994-11-22 | 1998-01-20 | Tissue Engineering, Inc. | Bipolymer foams having extracellular matrix particulates |
US5695998A (en) * | 1995-02-10 | 1997-12-09 | Purdue Research Foundation | Submucosa as a growth substrate for islet cells |
US6485723B1 (en) * | 1995-02-10 | 2002-11-26 | Purdue Research Foundation | Enhanced submucosal tissue graft constructs |
US5723010A (en) * | 1995-03-31 | 1998-03-03 | Toyo Boseki Kabushiki Kaisha | Medical device and method for producing the same |
US5554389A (en) * | 1995-04-07 | 1996-09-10 | Purdue Research Foundation | Urinary bladder submucosa derived tissue graft |
US5733337A (en) * | 1995-04-07 | 1998-03-31 | Organogenesis, Inc. | Tissue repair fabric |
US5711969A (en) * | 1995-04-07 | 1998-01-27 | Purdue Research Foundation | Large area submucosal tissue graft constructs |
US20020095218A1 (en) | 1996-03-12 | 2002-07-18 | Carr Robert M. | Tissue repair fabric |
WO1996031232A1 (en) * | 1995-04-07 | 1996-10-10 | Purdue Research Foundation | Tissue graft and method for urinary bladder reconstruction |
US5569273A (en) * | 1995-07-13 | 1996-10-29 | C. R. Bard, Inc. | Surgical mesh fabric |
US5911942A (en) * | 1995-11-02 | 1999-06-15 | Tissue Engineering, Inc. | Method for spinning and processing collagen fiber |
US5755791A (en) * | 1996-04-05 | 1998-05-26 | Purdue Research Foundation | Perforated submucosal tissue graft constructs |
US5788625A (en) * | 1996-04-05 | 1998-08-04 | Depuy Orthopaedics, Inc. | Method of making reconstructive SIS structure for cartilaginous elements in situ |
US5668288A (en) * | 1996-04-16 | 1997-09-16 | Depuy Orthopaedics, Inc. | Polyester ionomers for implant fabrication |
US5730933A (en) * | 1996-04-16 | 1998-03-24 | Depuy Orthopaedics, Inc. | Radiation sterilization of biologically active compounds |
US5733868A (en) * | 1996-04-16 | 1998-03-31 | Depuy Orthopaedics, Inc. | Poly(amino acid) adhesive tissue grafts |
US6299905B1 (en) | 1996-04-16 | 2001-10-09 | Depuy Orthopaedics, Inc. | Bioerodable polymeric adhesives for tissue repair |
CA2263144A1 (en) * | 1996-08-16 | 1998-02-19 | Children's Medical Center Corporation | Bladder submucosa seeded with cells for tissue reconstruction |
US6171344B1 (en) | 1996-08-16 | 2001-01-09 | Children's Medical Center Corporation | Bladder submucosa seeded with cells for tissue reconstruction |
EP0925077B1 (en) * | 1996-08-23 | 2003-10-15 | Cook Biotech, Inc. | Method for obtaining a purified collagen-based matrix from submucosa tissue |
US8716227B2 (en) * | 1996-08-23 | 2014-05-06 | Cook Biotech Incorporated | Graft prosthesis, materials and methods |
US6666892B2 (en) * | 1996-08-23 | 2003-12-23 | Cook Biotech Incorporated | Multi-formed collagenous biomaterial medical device |
US20060025786A1 (en) * | 1996-08-30 | 2006-02-02 | Verigen Transplantation Service International (Vtsi) Ag | Method for autologous transplantation |
US20020173806A1 (en) * | 1996-08-30 | 2002-11-21 | Verigen Transplantation Service International (Vtsi) Ag | Method for autologous transplantation |
EP1430899B1 (en) * | 1996-09-16 | 2010-07-07 | Purdue Research Foundation | Graft from submucosal intestinal tissue for repairing neurological tissue |
AU731768B2 (en) * | 1996-09-16 | 2001-04-05 | Purdue Research Foundation | Composition and method for repairing neurological tissue |
US5902228A (en) * | 1996-10-11 | 1999-05-11 | Cornell Research Foundation, Inc. | Method and apparatus for support and tubularization of surgical grafts |
JP4676580B2 (en) * | 1996-11-05 | 2011-04-27 | パーデュー・リサーチ・ファウンデーション | Myocardial graft composition |
US6696270B2 (en) | 1996-12-10 | 2004-02-24 | Purdue Research Foundation | Gastric submucosal tissue as a novel diagnostic tool |
AU774634B2 (en) * | 1996-12-10 | 2004-07-01 | Purdue Research Foundation | Tubular submucosal graft constructs |
US6379710B1 (en) * | 1996-12-10 | 2002-04-30 | Purdue Research Foundation | Biomaterial derived from vertebrate liver tissue |
EP1014887B1 (en) | 1996-12-10 | 2006-04-19 | Purdue Research Foundation | Stent with reduced thrombogenicity |
WO1998025635A1 (en) * | 1996-12-10 | 1998-06-18 | Purdue Research Foundation | Submucosal tissue inhibition of neoplastic cell growth |
AU743779B2 (en) | 1996-12-10 | 2002-02-07 | Cook Biotech, Inc. | Tubular grafts from purified submucosa |
JP4302188B2 (en) * | 1996-12-10 | 2009-07-22 | パーデュー・リサーチ・ファウンデーション | Gastric submucosa-derived tissue graft |
WO1998025549A1 (en) | 1996-12-10 | 1998-06-18 | Purdue Research Foundation | Artificial vascular valves |
WO1998025964A1 (en) | 1996-12-10 | 1998-06-18 | Purdue Research Foundation | Submucosa extracts |
US7923250B2 (en) | 1997-07-30 | 2011-04-12 | Warsaw Orthopedic, Inc. | Methods of expressing LIM mineralization protein in non-osseous cells |
CA2297489A1 (en) | 1997-07-30 | 1999-02-11 | Emory University | Novel bone mineralization proteins, dna, vectors, expression systems |
EP1011699B1 (en) * | 1997-09-11 | 2001-12-05 | Purdue Research Foundation | Galactosidase modified submucosal tissue |
US6254627B1 (en) * | 1997-09-23 | 2001-07-03 | Diseno Y Desarrollo Medico S.A. De C.V. | Non-thrombogenic stent jacket |
US6306138B1 (en) | 1997-09-24 | 2001-10-23 | Ethicon, Inc. | ACL fixation pin and method |
US6485969B1 (en) | 1997-12-23 | 2002-11-26 | Purdue Research Foundation | Biomaterial derived from follicle basement membranes |
US7070607B2 (en) * | 1998-01-27 | 2006-07-04 | The Regents Of The University Of California | Bioabsorbable polymeric implants and a method of using the same to create occlusions |
US6444229B2 (en) | 1998-02-27 | 2002-09-03 | Purdue Research Foundation | Submucosa gel compositions |
US7452371B2 (en) * | 1999-06-02 | 2008-11-18 | Cook Incorporated | Implantable vascular device |
JP4341049B2 (en) * | 1998-06-05 | 2009-10-07 | オルガノジェネシス インク. | Tubular graft prosthesis made by biotechnology |
CA2334228C (en) | 1998-06-05 | 2010-09-28 | Organogenesis Inc. | Bioengineered vascular graft support prostheses |
JP4341050B2 (en) * | 1998-06-05 | 2009-10-07 | オルガノジェネシス インク. | Vascular graft prosthesis made by bioengineering |
JP4606583B2 (en) * | 1998-06-05 | 2011-01-05 | オルガノジェネシス インク. | Planar sheet transplant prosthesis using biotechnological techniques |
US6933326B1 (en) | 1998-06-19 | 2005-08-23 | Lifecell Coporation | Particulate acellular tissue matrix |
US6458109B1 (en) * | 1998-08-07 | 2002-10-01 | Hill-Rom Services, Inc. | Wound treatment apparatus |
WO2000032254A1 (en) * | 1998-12-01 | 2000-06-08 | Purdue Research Foundation | Method for vocal cord reconstruction |
DK1051116T3 (en) | 1998-12-01 | 2009-02-02 | Univ Washington | Embolization device |
US8882850B2 (en) * | 1998-12-01 | 2014-11-11 | Cook Biotech Incorporated | Multi-formed collagenous biomaterial medical device |
US6918396B1 (en) | 1998-12-01 | 2005-07-19 | Purdue Research Foundation | Method for vocal cord reconstruction |
WO2000032250A1 (en) * | 1998-12-01 | 2000-06-08 | Cook Biotech, Inc. | A multi-formed collagenous biomaterial medical device |
WO2000032209A2 (en) * | 1998-12-01 | 2000-06-08 | Purdue Research Foundation | Submucosa modulation of mammalian immune response |
US20020165611A1 (en) | 1998-12-22 | 2002-11-07 | Robert-Jan Enzerink | Graft material convenience package |
US20020095157A1 (en) * | 1999-07-23 | 2002-07-18 | Bowman Steven M. | Graft fixation device combination |
US6179840B1 (en) | 1999-07-23 | 2001-01-30 | Ethicon, Inc. | Graft fixation device and method |
EP1207819B1 (en) * | 1999-08-06 | 2009-03-04 | Cook Biotech, Inc. | Tubular graft construct |
US6764462B2 (en) | 2000-11-29 | 2004-07-20 | Hill-Rom Services Inc. | Wound treatment apparatus |
US6824533B2 (en) | 2000-11-29 | 2004-11-30 | Hill-Rom Services, Inc. | Wound treatment apparatus |
US20040043006A1 (en) * | 2002-08-27 | 2004-03-04 | Badylak Stephen F. | Tissue regenerative composition |
WO2001045765A1 (en) * | 1999-12-22 | 2001-06-28 | Acell, Inc. | Tissue regenerative composition |
US6579538B1 (en) | 1999-12-22 | 2003-06-17 | Acell, Inc. | Tissue regenerative compositions for cardiac applications, method of making, and method of use thereof |
US6576265B1 (en) | 1999-12-22 | 2003-06-10 | Acell, Inc. | Tissue regenerative composition, method of making, and method of use thereof |
US6461364B1 (en) * | 2000-01-05 | 2002-10-08 | Integrated Vascular Systems, Inc. | Vascular sheath with bioabsorbable puncture site closure apparatus and methods of use |
US8758400B2 (en) * | 2000-01-05 | 2014-06-24 | Integrated Vascular Systems, Inc. | Closure system and methods of use |
US9579091B2 (en) * | 2000-01-05 | 2017-02-28 | Integrated Vascular Systems, Inc. | Closure system and methods of use |
US6391048B1 (en) * | 2000-01-05 | 2002-05-21 | Integrated Vascular Systems, Inc. | Integrated vascular device with puncture site closure component and sealant and methods of use |
US7842068B2 (en) * | 2000-12-07 | 2010-11-30 | Integrated Vascular Systems, Inc. | Apparatus and methods for providing tactile feedback while delivering a closure device |
US7635390B1 (en) * | 2000-01-14 | 2009-12-22 | Marctec, Llc | Joint replacement component having a modular articulating surface |
WO2001054176A1 (en) | 2000-01-18 | 2001-07-26 | Xros, Inc., Nortel Networks | Wafer bonding techniques to minimize built-in stress of silicon microstructures and micro-mirrors |
US6866686B2 (en) * | 2000-01-28 | 2005-03-15 | Cryolife, Inc. | Tissue graft |
DE60128069D1 (en) | 2000-01-31 | 2007-06-06 | Cook Biotech Inc | STENT VALVE FLAP |
AU2001238038B2 (en) | 2000-02-03 | 2005-08-25 | Cook Biotech, Inc. | Implantable vascular device |
AU2001240956A1 (en) * | 2000-03-09 | 2001-09-17 | Diseno Y Desarrollo Medico, S.A. De C.V. | Stent with cover connectors |
US7686842B2 (en) | 2000-05-04 | 2010-03-30 | Oregon Health Sciences University | Endovascular stent graft |
ATE407647T1 (en) * | 2000-05-22 | 2008-09-15 | Arthur C Coffey | WOUND DRESSING WITH SIS LAYER AND VACUUM CHAMBER |
US7410637B2 (en) * | 2000-06-20 | 2008-08-12 | Phycotransgenics, Llc | Transgenic algae for delivering antigens to an animal |
US8366787B2 (en) | 2000-08-04 | 2013-02-05 | Depuy Products, Inc. | Hybrid biologic-synthetic bioabsorbable scaffolds |
US6638312B2 (en) * | 2000-08-04 | 2003-10-28 | Depuy Orthopaedics, Inc. | Reinforced small intestinal submucosa (SIS) |
US6616686B2 (en) * | 2000-09-08 | 2003-09-09 | James Coleman | Surgical staples and methods for stapling |
EP1320390A2 (en) * | 2000-09-18 | 2003-06-25 | Organogenesis Inc. | Bioengineered flat sheet graft prosthesis and its use |
US6626918B1 (en) * | 2000-10-06 | 2003-09-30 | Medical Technology Group | Apparatus and methods for positioning a vascular sheath |
US6855135B2 (en) | 2000-11-29 | 2005-02-15 | Hill-Rom Services, Inc. | Vacuum therapy and cleansing dressing for wounds |
DE10060443A1 (en) * | 2000-11-29 | 2002-06-06 | Biotronik Mess & Therapieg | Stent, in particular in the form of a coronary stent contains at least one wall section consisting of a human or animal tissue possessing sufficient elasticity |
US6685681B2 (en) * | 2000-11-29 | 2004-02-03 | Hill-Rom Services, Inc. | Vacuum therapy and cleansing dressing for wounds |
US7211101B2 (en) | 2000-12-07 | 2007-05-01 | Abbott Vascular Devices | Methods for manufacturing a clip and clip |
US8690910B2 (en) | 2000-12-07 | 2014-04-08 | Integrated Vascular Systems, Inc. | Closure device and methods for making and using them |
US7905900B2 (en) * | 2003-01-30 | 2011-03-15 | Integrated Vascular Systems, Inc. | Clip applier and methods of use |
US6623510B2 (en) * | 2000-12-07 | 2003-09-23 | Integrated Vascular Systems, Inc. | Closure device and methods for making and using them |
US7806904B2 (en) * | 2000-12-07 | 2010-10-05 | Integrated Vascular Systems, Inc. | Closure device |
US6752831B2 (en) | 2000-12-08 | 2004-06-22 | Osteotech, Inc. | Biocompatible osteogenic band for repair of spinal disorders |
US8758438B2 (en) * | 2000-12-08 | 2014-06-24 | Warsaw Orthopedic, Inc. | Implant for orthopedic applications |
US6852330B2 (en) * | 2000-12-21 | 2005-02-08 | Depuy Mitek, Inc. | Reinforced foam implants with enhanced integrity for soft tissue repair and regeneration |
CA2365376C (en) * | 2000-12-21 | 2006-03-28 | Ethicon, Inc. | Use of reinforced foam implants with enhanced integrity for soft tissue repair and regeneration |
US6599323B2 (en) * | 2000-12-21 | 2003-07-29 | Ethicon, Inc. | Reinforced tissue implants and methods of manufacture and use |
US20030211793A1 (en) * | 2001-03-05 | 2003-11-13 | Eugene Bell | Injectable bio-compatible material and methods of use |
JP2004529711A (en) * | 2001-05-07 | 2004-09-30 | クロスカート インコーポレイテッド | Submucosal xenograft |
IES20010547A2 (en) * | 2001-06-07 | 2002-12-11 | Christy Cummins | Surgical Staple |
AU2002310364B2 (en) * | 2001-06-08 | 2006-02-23 | Morris Innovative Research, Inc. | Method and apparatus for sealing access |
US20070038244A1 (en) * | 2001-06-08 | 2007-02-15 | Morris Edward J | Method and apparatus for sealing access |
US7993365B2 (en) | 2001-06-08 | 2011-08-09 | Morris Innovative, Inc. | Method and apparatus for sealing access |
US20060004408A1 (en) * | 2001-06-08 | 2006-01-05 | Morris Edward J | Method and apparatus for sealing access |
AU2002320189B2 (en) * | 2001-06-28 | 2007-04-26 | Cook Biotech Incorporated | Graft prosthesis devices containing renal capsule collagen |
CA2452040C (en) * | 2001-06-29 | 2011-03-22 | Cook Biotech Incorporated | Porous sponge matrix medical devices and methods |
WO2003007789A2 (en) * | 2001-07-16 | 2003-01-30 | Depuy Products, Inc. | Porous extracellular matrix scaffold and method |
JP4197157B2 (en) * | 2001-07-16 | 2008-12-17 | デピュイ・プロダクツ・インコーポレイテッド | Cartilage repair and reproduction apparatus and method |
US7819918B2 (en) * | 2001-07-16 | 2010-10-26 | Depuy Products, Inc. | Implantable tissue repair device |
US8025896B2 (en) * | 2001-07-16 | 2011-09-27 | Depuy Products, Inc. | Porous extracellular matrix scaffold and method |
US7361195B2 (en) | 2001-07-16 | 2008-04-22 | Depuy Products, Inc. | Cartilage repair apparatus and method |
US7201917B2 (en) * | 2001-07-16 | 2007-04-10 | Depuy Products, Inc. | Porous delivery scaffold and method |
WO2003007790A2 (en) * | 2001-07-16 | 2003-01-30 | Depuy Products, Inc. | Hybrid biologic/synthetic porous extracellular matrix scaffolds |
US7163563B2 (en) * | 2001-07-16 | 2007-01-16 | Depuy Products, Inc. | Unitary surgical device and method |
WO2003007847A1 (en) | 2001-07-16 | 2003-01-30 | Depuy Products, Inc. | Hybrid biologic-synthetic bioabsorable scaffolds |
WO2003007784A2 (en) * | 2001-07-16 | 2003-01-30 | Depuy Products, Inc. | Meniscus regeneration device and method |
WO2003007839A2 (en) | 2001-07-16 | 2003-01-30 | Depuy Products, Inc. | Devices form naturally occurring biologically derived |
US7833283B2 (en) * | 2001-08-16 | 2010-11-16 | Purdue Research Foundation | Material and method for promoting tissue growth |
US7622129B1 (en) | 2002-08-05 | 2009-11-24 | Purdue Research Foundation | Nano-structured polymers for use as implants |
US7708741B1 (en) | 2001-08-28 | 2010-05-04 | Marctec, Llc | Method of preparing bones for knee replacement surgery |
US6776784B2 (en) * | 2001-09-06 | 2004-08-17 | Core Medical, Inc. | Clip apparatus for closing septal defects and methods of use |
US20070112358A1 (en) * | 2001-09-06 | 2007-05-17 | Ryan Abbott | Systems and Methods for Treating Septal Defects |
US20090054912A1 (en) * | 2001-09-06 | 2009-02-26 | Heanue Taylor A | Systems and Methods for Treating Septal Defects |
US20060052821A1 (en) * | 2001-09-06 | 2006-03-09 | Ovalis, Inc. | Systems and methods for treating septal defects |
US6702835B2 (en) * | 2001-09-07 | 2004-03-09 | Core Medical, Inc. | Needle apparatus for closing septal defects and methods for using such apparatus |
US20050267495A1 (en) * | 2004-05-17 | 2005-12-01 | Gateway Medical, Inc. | Systems and methods for closing internal tissue defects |
US20070129755A1 (en) * | 2005-12-05 | 2007-06-07 | Ovalis, Inc. | Clip-based systems and methods for treating septal defects |
CA2462877A1 (en) * | 2001-10-11 | 2003-04-17 | Hill-Rom Services, Inc. | Waste container for negative pressure therapy |
WO2003035125A2 (en) * | 2001-10-26 | 2003-05-01 | Cook Biotech Incorporated | Medical graft device with meshed structure |
AU2002340463A1 (en) * | 2001-11-16 | 2003-06-10 | Children's Medical Center Corporation | Augmentation of organ function |
EP1467661A4 (en) * | 2001-12-19 | 2008-11-05 | Nmt Medical Inc | Septal occluder and associated methods |
US7318833B2 (en) * | 2001-12-19 | 2008-01-15 | Nmt Medical, Inc. | PFO closure device with flexible thrombogenic joint and improved dislodgement resistance |
US20030118560A1 (en) * | 2001-12-20 | 2003-06-26 | Kelly Sheila J. | Composite biocompatible matrices |
US7195624B2 (en) * | 2001-12-26 | 2007-03-27 | Hill-Rom Services, Inc. | Vented vacuum bandage with irrigation for wound healing and method |
US7534927B2 (en) * | 2001-12-26 | 2009-05-19 | Hill-Rom Services, Inc. | Vacuum bandage packing |
WO2003057307A1 (en) * | 2001-12-26 | 2003-07-17 | Hill-Rom Services, Inc. | Wound vacuum therapy dressing kit |
AU2003202264A1 (en) * | 2002-01-11 | 2003-07-30 | Clarian Health Partners, Inc. | Composition and method for inhibiting hypersensitivity |
AU2003202261A1 (en) * | 2002-01-11 | 2003-07-30 | Purdue Research Foundation | Biomaterial derived from vertebrate liver tissue |
US7220265B2 (en) * | 2002-01-14 | 2007-05-22 | Nmt Medical, Inc. | Patent foramen ovale (PFO) closure method and device |
US6749621B2 (en) | 2002-02-21 | 2004-06-15 | Integrated Vascular Systems, Inc. | Sheath apparatus and methods for delivering a closure device |
US20030171801A1 (en) * | 2002-03-06 | 2003-09-11 | Brian Bates | Partially covered intraluminal support device |
US8529956B2 (en) | 2002-03-18 | 2013-09-10 | Carnell Therapeutics Corporation | Methods and apparatus for manufacturing plasma based plastics and bioplastics produced therefrom |
US20100254900A1 (en) * | 2002-03-18 | 2010-10-07 | Campbell Phil G | Biocompatible polymers and Methods of use |
WO2003082076A2 (en) * | 2002-03-25 | 2003-10-09 | Nmt Medical, Inc. | Patent foramen ovale (pfo) closure clips |
US6939369B2 (en) * | 2002-04-03 | 2005-09-06 | Cook Incorporated | Intraluminal graft assembly and vessel repair system |
AU2002359824A1 (en) | 2002-04-10 | 2003-10-27 | Hill-Rom Services, Inc. | Access openings in vacuum bandage |
EP1494594B1 (en) | 2002-04-15 | 2011-07-06 | Cook Biotech Incorporated | Apparatus and method for producing a reinforced surgical staple line |
CA2483908C (en) * | 2002-05-02 | 2012-02-21 | Purdue Research Foundation | Vascularization enhanced graft constructs |
CA2484614A1 (en) * | 2002-05-02 | 2003-11-13 | Cook Biotech Incorporated | Cell-seeded extracellular matrix grafts |
EP1503789A4 (en) * | 2002-05-02 | 2006-08-02 | Purdue Research Foundation | Vascularization enhanced graft constructs |
NZ536563A (en) * | 2002-05-02 | 2008-03-28 | Purdue Research Foundation | Vascularization enhanced graft constructs |
US20040117004A1 (en) * | 2002-05-16 | 2004-06-17 | Osborne Thomas A. | Stent and method of forming a stent with integral barbs |
US7828839B2 (en) * | 2002-05-16 | 2010-11-09 | Cook Incorporated | Flexible barb for anchoring a prosthesis |
WO2003101346A1 (en) * | 2002-05-29 | 2003-12-11 | William A. Cook Australia Pty. Ltd. | Multi-piece prosthesis deployment apparatus |
AU2003253620A1 (en) | 2002-06-03 | 2003-12-19 | Nmt Medical, Inc. | Device with biological tissue scaffold for intracardiac defect closure |
DE60325355D1 (en) * | 2002-06-04 | 2009-01-29 | Abbott Vascular Inc | SURGICAL CLOSURE AND MOUNTING DEVICE FOR VASCULAR SEALING |
JP2005528181A (en) | 2002-06-05 | 2005-09-22 | エヌエムティー メディカル インコーポレイテッド | Patent foramen ovale (PFO) occlusion device with radial and circumferential supports |
EP2165675B1 (en) | 2002-06-26 | 2018-03-07 | Cook Medical Technologies LLC | Stent-graft fastening |
US7160326B2 (en) * | 2002-06-27 | 2007-01-09 | Depuy Products, Inc. | Method and apparatus for implantation of soft tissue implant |
US20040166169A1 (en) * | 2002-07-15 | 2004-08-26 | Prasanna Malaviya | Porous extracellular matrix scaffold and method |
WO2004014452A2 (en) * | 2002-08-12 | 2004-02-19 | Osteotech, Inc. | Synthesis of a bone-polymer composite material |
EP2517674B1 (en) | 2002-08-15 | 2016-03-16 | Cook Medical Technologies LLC | Implantable vascular device |
US7550004B2 (en) * | 2002-08-20 | 2009-06-23 | Cook Biotech Incorporated | Endoluminal device with extracellular matrix material and methods |
EP1545644B2 (en) | 2002-08-21 | 2018-02-28 | KCI Medical Resources | Wound packing for preventing wound closure |
CA2496905A1 (en) * | 2002-09-06 | 2004-03-18 | Cook Biotech Incorporated | Tissue graft prosthesis devices containing juvenile or small diameter submucosa |
US20040136968A1 (en) * | 2002-09-27 | 2004-07-15 | Verigen Ag | Autologous cells on a support matrix for tissue repair |
US7824701B2 (en) * | 2002-10-18 | 2010-11-02 | Ethicon, Inc. | Biocompatible scaffold for ligament or tendon repair |
US20040078090A1 (en) * | 2002-10-18 | 2004-04-22 | Francois Binette | Biocompatible scaffolds with tissue fragments |
WO2004037333A1 (en) | 2002-10-25 | 2004-05-06 | Nmt Medical, Inc. | Expandable sheath tubing |
US7682392B2 (en) * | 2002-10-30 | 2010-03-23 | Depuy Spine, Inc. | Regenerative implants for stabilizing the spine and devices for attachment of said implants |
CA2503349A1 (en) * | 2002-11-06 | 2004-05-27 | Nmt Medical, Inc. | Medical devices utilizing modified shape memory alloy |
AU2003287689A1 (en) * | 2002-11-07 | 2004-06-03 | Nmt Medical, Inc. | Patent foramen ovale (pfo) closure with magnetic force |
US7627373B2 (en) * | 2002-11-30 | 2009-12-01 | Cardiac Pacemakers, Inc. | Method and apparatus for cell and electrical therapy of living tissue |
US20040158289A1 (en) * | 2002-11-30 | 2004-08-12 | Girouard Steven D. | Method and apparatus for cell and electrical therapy of living tissue |
US20040191226A1 (en) * | 2002-12-04 | 2004-09-30 | Badylak Stephen F. | Method for repair of body wall |
US20040187877A1 (en) * | 2002-12-04 | 2004-09-30 | Badylak Stephen F. | Method for repair of liver tissue |
DE60326000D1 (en) * | 2002-12-04 | 2009-03-12 | Cook Inc | METHOD AND DEVICE FOR TREATMENT IN AORTASE ACTION |
CA2503666A1 (en) * | 2002-12-09 | 2004-06-24 | Nmt Medical, Inc. | Septal closure devices |
US20050251267A1 (en) * | 2004-05-04 | 2005-11-10 | John Winterbottom | Cell permeable structural implant |
EP1583487B1 (en) | 2003-01-14 | 2016-11-02 | The Cleveland Clinic Foundation | Branched vessel endoluminal device |
US9125733B2 (en) | 2003-01-14 | 2015-09-08 | The Cleveland Clinic Foundation | Branched vessel endoluminal device |
US8202293B2 (en) | 2003-01-30 | 2012-06-19 | Integrated Vascular Systems, Inc. | Clip applier and methods of use |
US8905937B2 (en) * | 2009-02-26 | 2014-12-09 | Integrated Vascular Systems, Inc. | Methods and apparatus for locating a surface of a body lumen |
US8821534B2 (en) | 2010-12-06 | 2014-09-02 | Integrated Vascular Systems, Inc. | Clip applier having improved hemostasis and methods of use |
US7857828B2 (en) * | 2003-01-30 | 2010-12-28 | Integrated Vascular Systems, Inc. | Clip applier and methods of use |
US8398656B2 (en) | 2003-01-30 | 2013-03-19 | Integrated Vascular Systems, Inc. | Clip applier and methods of use |
US8758398B2 (en) | 2006-09-08 | 2014-06-24 | Integrated Vascular Systems, Inc. | Apparatus and method for delivering a closure element |
ES2541909T3 (en) | 2003-02-04 | 2015-07-28 | Warsaw Orthopedic, Inc. | Osteoimplant polyurethanes |
US7985414B2 (en) * | 2003-02-04 | 2011-07-26 | Warsaw Orthopedic, Inc. | Polyurethanes for osteoimplants |
US20040176855A1 (en) * | 2003-03-07 | 2004-09-09 | Acell, Inc. | Decellularized liver for repair of tissue and treatment of organ deficiency |
US20040175366A1 (en) * | 2003-03-07 | 2004-09-09 | Acell, Inc. | Scaffold for cell growth and differentiation |
US8197837B2 (en) | 2003-03-07 | 2012-06-12 | Depuy Mitek, Inc. | Method of preparation of bioabsorbable porous reinforced tissue implants and implants thereof |
US7658747B2 (en) * | 2003-03-12 | 2010-02-09 | Nmt Medical, Inc. | Medical device for manipulation of a medical implant |
US7524332B2 (en) * | 2003-03-17 | 2009-04-28 | Cook Incorporated | Vascular valve with removable support component |
WO2004096085A2 (en) * | 2003-03-27 | 2004-11-11 | Purdue Research Foundation | Nanofibers as a neural biomaterial |
EP1610728B1 (en) * | 2003-04-01 | 2011-05-25 | Cook Incorporated | Percutaneously deployed vascular valves |
FR2853394B1 (en) * | 2003-04-03 | 2006-03-10 | Valeo Vision | PROJECTION DEVICE FOR A MOTOR VEHICLE LIGHTING PORTIC POINTS |
US7067123B2 (en) | 2003-04-29 | 2006-06-27 | Musculoskeletal Transplant Foundation | Glue for cartilage repair |
US20050222687A1 (en) * | 2004-04-02 | 2005-10-06 | Gordana Vunjak-Novakovic | Cartilage implant assembly and method for implantation |
US20050064042A1 (en) * | 2003-04-29 | 2005-03-24 | Musculoskeletal Transplant Foundation | Cartilage implant plug with fibrin glue and method for implantation |
US20090291112A1 (en) * | 2003-05-16 | 2009-11-26 | Truncale Katherine G | Allograft osteochondral plug combined with cartilage particle mixture |
US7901457B2 (en) | 2003-05-16 | 2011-03-08 | Musculoskeletal Transplant Foundation | Cartilage allograft plug |
US7488348B2 (en) * | 2003-05-16 | 2009-02-10 | Musculoskeletal Transplant Foundation | Cartilage allograft plug |
US7105001B2 (en) * | 2003-05-21 | 2006-09-12 | Mandelbaum Jon A | Surgical method and composition utilizing submucosal tissue to prevent incisional hernias |
US20040260315A1 (en) * | 2003-06-17 | 2004-12-23 | Dell Jeffrey R. | Expandable tissue support member and method of forming the support member |
AU2004253508A1 (en) | 2003-06-25 | 2005-01-13 | Acell, Inc. | Conditioned matrix compositions for tissue restoration |
US8226715B2 (en) | 2003-06-30 | 2012-07-24 | Depuy Mitek, Inc. | Scaffold for connective tissue repair |
US8480706B2 (en) | 2003-07-14 | 2013-07-09 | W.L. Gore & Associates, Inc. | Tubular patent foramen ovale (PFO) closure device with catch system |
EP1651116B1 (en) * | 2003-07-14 | 2013-06-26 | W.L. Gore & Associates, Inc. | Tubular patent foramen ovale (pfo) closure device with catch system |
US9861346B2 (en) | 2003-07-14 | 2018-01-09 | W. L. Gore & Associates, Inc. | Patent foramen ovale (PFO) closure device with linearly elongating petals |
EP1659992B1 (en) * | 2003-07-31 | 2013-03-27 | Cook Medical Technologies LLC | Prosthetic valve devices and methods of making such devices |
US10583220B2 (en) * | 2003-08-11 | 2020-03-10 | DePuy Synthes Products, Inc. | Method and apparatus for resurfacing an articular surface |
WO2005018728A2 (en) * | 2003-08-19 | 2005-03-03 | Nmt Medical, Inc. | Expandable sheath tubing |
US8021692B2 (en) | 2003-08-25 | 2011-09-20 | Cook Biotech Incorporated | Graft materials containing bioactive substances, and methods for their manufacture |
AU2004270239C1 (en) * | 2003-09-04 | 2011-07-07 | Cook Biotech Incorporated | Extracellular matrix composite materials, and manufacture and use thereof |
US7645229B2 (en) * | 2003-09-26 | 2010-01-12 | Armstrong David N | Instrument and method for endoscopic visualization and treatment of anorectal fistula |
US8043357B2 (en) | 2003-10-10 | 2011-10-25 | Cook Medical Technologies Llc | Ring stent |
CA2540830C (en) | 2003-10-10 | 2012-08-14 | William A. Cook Australia Pty. Ltd. | Fenestrated stent grafts |
WO2005034807A1 (en) | 2003-10-10 | 2005-04-21 | William A. Cook Australia Pty. Ltd | Composite stent graft |
ATE440564T1 (en) * | 2003-10-10 | 2009-09-15 | Cleveland Clinic Foundation | ENDOLUMINAL PROSTHESIS WITH CONNECTABLE MODULES |
US6976679B2 (en) * | 2003-11-07 | 2005-12-20 | The Boeing Company | Inter-fluid seal assembly and method therefor |
US7316822B2 (en) | 2003-11-26 | 2008-01-08 | Ethicon, Inc. | Conformable tissue repair implant capable of injection delivery |
US8389588B2 (en) * | 2003-12-04 | 2013-03-05 | Kensey Nash Corporation | Bi-phasic compressed porous reinforcement materials suitable for implant |
US8133500B2 (en) * | 2003-12-04 | 2012-03-13 | Kensey Nash Bvf Technology, Llc | Compressed high density fibrous polymers suitable for implant |
US20050125015A1 (en) * | 2003-12-04 | 2005-06-09 | Mcnally-Heintzelman Karen M. | Tissue-handling apparatus, system and method |
US20050125033A1 (en) * | 2003-12-04 | 2005-06-09 | Mcnally-Heintzelman Karen M. | Wound closure apparatus |
US7901461B2 (en) * | 2003-12-05 | 2011-03-08 | Ethicon, Inc. | Viable tissue repair implants and methods of use |
US20050273119A1 (en) | 2003-12-09 | 2005-12-08 | Nmt Medical, Inc. | Double spiral patent foramen ovale closure clamp |
EP1701672A4 (en) * | 2003-12-19 | 2011-04-27 | Osteotech Inc | Tissue-derived mesh for orthopedic regeneration |
ATE468815T1 (en) * | 2004-01-21 | 2010-06-15 | Cook Inc | IMPLANTABLE TRANSPLANT FOR CLOSING A FISTULA |
US8262694B2 (en) * | 2004-01-30 | 2012-09-11 | W.L. Gore & Associates, Inc. | Devices, systems, and methods for closure of cardiac openings |
WO2005077433A1 (en) * | 2004-02-09 | 2005-08-25 | Cook Biotech Incorporated | Stent graft devices having collagen coating |
US8337545B2 (en) | 2004-02-09 | 2012-12-25 | Cook Medical Technologies Llc | Woven implantable device |
US11395865B2 (en) * | 2004-02-09 | 2022-07-26 | DePuy Synthes Products, Inc. | Scaffolds with viable tissue |
GB2451776B (en) | 2004-02-17 | 2009-04-08 | Cook Biotech Inc | Medical devices and methods useful for applying bolster material |
US7840263B2 (en) * | 2004-02-27 | 2010-11-23 | Cardiac Pacemakers, Inc. | Method and apparatus for device controlled gene expression |
US7871419B2 (en) * | 2004-03-03 | 2011-01-18 | Nmt Medical, Inc. | Delivery/recovery system for septal occluder |
NZ549953A (en) | 2004-03-17 | 2010-11-26 | Revivicor Inc | Tissue products derived from animals lacking any expression of functional alpha 1,3 galactosyltransferase |
US7449027B2 (en) * | 2004-03-29 | 2008-11-11 | Cook Incorporated | Modifying fluid flow in a body vessel lumen to promote intraluminal flow-sensitive processes |
GB2429162B (en) | 2004-03-29 | 2009-03-25 | Cook Biotech Inc | Methods for producing medical graft products with differing regions |
US20050234509A1 (en) * | 2004-03-30 | 2005-10-20 | Mmt Medical, Inc. | Center joints for PFO occluders |
JP2007532153A (en) * | 2004-03-31 | 2007-11-15 | クック インコーポレイテッド | Graft material based on ECM |
DE602005025324D1 (en) * | 2004-03-31 | 2011-01-27 | Cook Inc | STENT STORAGE DEVICE |
US9498322B2 (en) * | 2004-03-31 | 2016-11-22 | Cook Medical Technologies Llc | Multi-portion endoluminal prosthesis |
DE602005020754D1 (en) * | 2004-03-31 | 2010-06-02 | Cook Inc | TRANSPLANT MATERIAL AND VASCOPY THERAPY WITH EXTRACELLULAR COLLAGEN MATRIX AND ITS MANUFACTURING PROCESS |
WO2005096988A1 (en) * | 2004-04-01 | 2005-10-20 | Cook Incorporated | A device for retracting the walls of a body vessel with remodelable material |
US20050267524A1 (en) * | 2004-04-09 | 2005-12-01 | Nmt Medical, Inc. | Split ends closure device |
US8657881B2 (en) * | 2004-04-20 | 2014-02-25 | Depuy Mitek, Llc | Meniscal repair scaffold |
US8137686B2 (en) | 2004-04-20 | 2012-03-20 | Depuy Mitek, Inc. | Nonwoven tissue scaffold |
US8221780B2 (en) * | 2004-04-20 | 2012-07-17 | Depuy Mitek, Inc. | Nonwoven tissue scaffold |
US7922759B1 (en) * | 2004-04-22 | 2011-04-12 | Cook Medical Technologies Llc | Apparatus and methods for vascular treatment |
US8361110B2 (en) * | 2004-04-26 | 2013-01-29 | W.L. Gore & Associates, Inc. | Heart-shaped PFO closure device |
US7569233B2 (en) * | 2004-05-04 | 2009-08-04 | Depuy Products, Inc. | Hybrid biologic-synthetic bioabsorbable scaffolds |
US20050249772A1 (en) * | 2004-05-04 | 2005-11-10 | Prasanna Malaviya | Hybrid biologic-synthetic bioabsorbable scaffolds |
US7842053B2 (en) | 2004-05-06 | 2010-11-30 | Nmt Medical, Inc. | Double coil occluder |
US8308760B2 (en) * | 2004-05-06 | 2012-11-13 | W.L. Gore & Associates, Inc. | Delivery systems and methods for PFO closure device with two anchors |
US7704268B2 (en) * | 2004-05-07 | 2010-04-27 | Nmt Medical, Inc. | Closure device with hinges |
US8257389B2 (en) * | 2004-05-07 | 2012-09-04 | W.L. Gore & Associates, Inc. | Catching mechanisms for tubular septal occluder |
IES20040368A2 (en) * | 2004-05-25 | 2005-11-30 | James E Coleman | Surgical stapler |
US7764995B2 (en) | 2004-06-07 | 2010-07-27 | Cardiac Pacemakers, Inc. | Method and apparatus to modulate cellular regeneration post myocardial infarct |
CA2570142A1 (en) * | 2004-07-07 | 2006-02-09 | Cook Incorporated | Graft, stent graft and method for manufacture |
CA2575240A1 (en) | 2004-07-30 | 2006-02-09 | Cook Biotech Incorporated | Graft with increased resistance to enzymatic degradation |
US20060029633A1 (en) * | 2004-08-03 | 2006-02-09 | Arthrotek, Inc | Biological patch for use in medical procedures |
US8257715B1 (en) | 2004-08-26 | 2012-09-04 | University Of Notre Dame | Tissue vaccines and uses thereof |
EP1827247B8 (en) * | 2004-09-24 | 2020-05-06 | W.L. Gore & Associates, Inc. | Occluder device double securement system for delivery/recovery of such occluder device |
US20080220044A1 (en) * | 2007-03-06 | 2008-09-11 | Semler Eric J | Cancellous construct with support ring for repair of osteochondral defects |
US7837740B2 (en) | 2007-01-24 | 2010-11-23 | Musculoskeletal Transplant Foundation | Two piece cancellous construct for cartilage repair |
US20090149893A1 (en) * | 2007-12-05 | 2009-06-11 | Semler Eric J | Cancellous Bone Implant for Cartilage Repair |
WO2006050459A2 (en) * | 2004-10-28 | 2006-05-11 | Cook Incorporated | Methods and systems for modifying vascular valves |
US7458987B2 (en) * | 2004-10-29 | 2008-12-02 | Cook Incorporated | Vascular valves having implanted and target configurations and methods of preparing the same |
US7513866B2 (en) * | 2004-10-29 | 2009-04-07 | Depuy Products, Inc. | Intestine processing device and associated method |
US7905826B2 (en) * | 2004-11-03 | 2011-03-15 | Cook Incorporated | Methods for modifying vascular vessel walls |
US8329202B2 (en) | 2004-11-12 | 2012-12-11 | Depuy Products, Inc. | System and method for attaching soft tissue to an implant |
US7744621B2 (en) * | 2004-12-06 | 2010-06-29 | Cook Incorporated | Inflatable occlusion devices, methods, and systems |
WO2006062976A2 (en) | 2004-12-07 | 2006-06-15 | Cook Incorporated | Methods for modifying vascular vessel walls |
US20060134071A1 (en) * | 2004-12-20 | 2006-06-22 | Jeffrey Ross | Use of extracellular matrix and electrical therapy |
US7981065B2 (en) * | 2004-12-20 | 2011-07-19 | Cardiac Pacemakers, Inc. | Lead electrode incorporating extracellular matrix |
US8060219B2 (en) * | 2004-12-20 | 2011-11-15 | Cardiac Pacemakers, Inc. | Epicardial patch including isolated extracellular matrix with pacing electrodes |
US8874204B2 (en) * | 2004-12-20 | 2014-10-28 | Cardiac Pacemakers, Inc. | Implantable medical devices comprising isolated extracellular matrix |
US7354627B2 (en) | 2004-12-22 | 2008-04-08 | Depuy Products, Inc. | Method for organizing the assembly of collagen fibers and compositions formed therefrom |
EP1833384B1 (en) * | 2004-12-30 | 2017-08-16 | Cook Medical Technologies LLC | Inverting occlusion devices and systems |
US8128680B2 (en) | 2005-01-10 | 2012-03-06 | Taheri Laduca Llc | Apparatus and method for deploying an implantable device within the body |
US8287583B2 (en) | 2005-01-10 | 2012-10-16 | Taheri Laduca Llc | Apparatus and method for deploying an implantable device within the body |
US20070150051A1 (en) * | 2005-01-10 | 2007-06-28 | Duke Fiduciary, Llc | Vascular implants and methods of fabricating the same |
US20060206139A1 (en) * | 2005-01-19 | 2006-09-14 | Tekulve Kurt J | Vascular occlusion device |
US20060246033A1 (en) * | 2005-03-02 | 2006-11-02 | Cook Biotech Incorporated | Injectable bulking agent compositions |
US8303647B2 (en) * | 2005-03-03 | 2012-11-06 | Cook Medical Technologies Llc | Medical valve leaflet structures with peripheral region receptive to tissue ingrowth |
US9138445B2 (en) * | 2005-03-09 | 2015-09-22 | Cook Biotech Incorporated | Medical graft materials with adherent extracellular matrix fibrous mass |
WO2006099016A2 (en) * | 2005-03-09 | 2006-09-21 | Providence Health System | A composite multi-layered vascular graft prosthesis |
US7840266B2 (en) * | 2005-03-11 | 2010-11-23 | Cardiac Pacemakers, Inc. | Integrated lead for applying cardiac resynchronization therapy and neural stimulation therapy |
US8277480B2 (en) | 2005-03-18 | 2012-10-02 | W.L. Gore & Associates, Inc. | Catch member for PFO occluder |
US8454678B2 (en) * | 2005-03-19 | 2013-06-04 | Cook Biotech Incorporated | Prosthetic implants including ECM composite material |
US8197534B2 (en) * | 2005-03-31 | 2012-06-12 | Cook Medical Technologies Llc | Valve device with inflatable chamber |
US20060229670A1 (en) * | 2005-04-01 | 2006-10-12 | Bates Brian L | Method and a medical closure system for sealing a puncture |
WO2006113501A1 (en) | 2005-04-13 | 2006-10-26 | The Cleveland Clinic Foundation | Endoluminal prosthesis |
EP1980275B1 (en) | 2005-04-29 | 2016-01-27 | Cook Biotech, Inc. | Fistula graft with deformable sheet-form material |
JP4995811B2 (en) | 2005-04-29 | 2012-08-08 | クック・バイオテック・インコーポレーテッド | Acupuncture positive displacement implants and related methods and systems |
AU2006244393B2 (en) * | 2005-05-05 | 2012-06-21 | Cook Biotech Incorporated | Implantable materials and methods for inhibiting tissue adhesion formation |
US8518436B2 (en) * | 2005-05-16 | 2013-08-27 | Purdue Research Foundation | Engineered extracellular matrices |
WO2006125055A2 (en) * | 2005-05-17 | 2006-11-23 | Cook Incorporated | Prosthetic valve devices and methods of making and using such devices |
US20060276883A1 (en) * | 2005-06-01 | 2006-12-07 | Cook Incorporated | Tapered and distally stented elephant trunk stent graft |
US20080109058A1 (en) * | 2005-06-01 | 2008-05-08 | Cook Incorporated | Intraoperative Anastomosis Method |
WO2007002260A2 (en) * | 2005-06-21 | 2007-01-04 | Cook Incorporated | Implantable graft to close a fistula |
US20060292227A1 (en) * | 2005-06-23 | 2006-12-28 | Mcpherson Timothy B | Extracellular matrix material particles and methods of preparation |
US8926633B2 (en) | 2005-06-24 | 2015-01-06 | Abbott Laboratories | Apparatus and method for delivering a closure element |
US8313497B2 (en) | 2005-07-01 | 2012-11-20 | Abbott Laboratories | Clip applier and methods of use |
US20080312686A1 (en) * | 2005-07-01 | 2008-12-18 | Abbott Laboratories | Antimicrobial closure element and closure element applier |
US9271817B2 (en) * | 2005-07-05 | 2016-03-01 | Cook Biotech Incorporated | Tissue augmentation devices and methods |
US8579936B2 (en) * | 2005-07-05 | 2013-11-12 | ProMed, Inc. | Centering of delivery devices with respect to a septal defect |
US7850985B2 (en) | 2005-07-05 | 2010-12-14 | Cook Biotech Incorporated | Tissue augmentation devices and methods |
US7815926B2 (en) * | 2005-07-11 | 2010-10-19 | Musculoskeletal Transplant Foundation | Implant for articular cartilage repair |
WO2007014088A2 (en) * | 2005-07-25 | 2007-02-01 | Cook Incorporated | Intraluminal prosthesis and stent |
US7595062B2 (en) | 2005-07-28 | 2009-09-29 | Depuy Products, Inc. | Joint resurfacing orthopaedic implant and associated method |
EP2093256A3 (en) | 2005-07-28 | 2009-10-14 | Carnegie Mellon University | Biocompatible polymers and methods of use |
US20070038295A1 (en) * | 2005-08-12 | 2007-02-15 | Cook Incorporated | Artificial valve prosthesis having a ring frame |
US20070038299A1 (en) * | 2005-08-12 | 2007-02-15 | Arthrotek, Inc | Multilayer microperforated implant |
US9456811B2 (en) * | 2005-08-24 | 2016-10-04 | Abbott Vascular Inc. | Vascular closure methods and apparatuses |
US20070060895A1 (en) | 2005-08-24 | 2007-03-15 | Sibbitt Wilmer L Jr | Vascular closure methods and apparatuses |
US8920442B2 (en) * | 2005-08-24 | 2014-12-30 | Abbott Vascular Inc. | Vascular opening edge eversion methods and apparatuses |
US8771340B2 (en) * | 2005-08-25 | 2014-07-08 | Cook Medical Technologies Llc | Methods and devices for the endoluminal deployment and securement of prostheses |
US8470022B2 (en) * | 2005-08-31 | 2013-06-25 | Cook Biotech Incorporated | Implantable valve |
EP1928512B1 (en) * | 2005-09-01 | 2012-11-14 | Cook Medical Technologies LLC | Attachment of material to an implantable frame by cross-linking |
US7846179B2 (en) * | 2005-09-01 | 2010-12-07 | Ovalis, Inc. | Suture-based systems and methods for treating septal defects |
US9259267B2 (en) | 2005-09-06 | 2016-02-16 | W.L. Gore & Associates, Inc. | Devices and methods for treating cardiac tissue |
WO2007030433A2 (en) * | 2005-09-06 | 2007-03-15 | Nmt Medical, Inc. | Removable intracardiac rf device |
US20070088388A1 (en) * | 2005-09-19 | 2007-04-19 | Opolski Steven W | Delivery device for implant with dual attachment sites |
CA2623106C (en) | 2005-09-19 | 2013-12-24 | Histogenics Corporation | Cell-support matrix having narrowly defined uniformly vertically and non-randomly organized porosity and pore density and a method for preparation thereof |
US7503928B2 (en) | 2005-10-21 | 2009-03-17 | Cook Biotech Incorporated | Artificial valve with center leaflet attachment |
WO2007120186A2 (en) * | 2005-10-24 | 2007-10-25 | Nmt Medical, Inc. | Radiopaque bioabsorbable occluder |
US7563277B2 (en) | 2005-10-24 | 2009-07-21 | Cook Incorporated | Removable covering for implantable frame projections |
US8778362B2 (en) | 2005-10-27 | 2014-07-15 | University Of Notre Dame | Anti-tumor/cancer heterologous acellular collagenous preparations and uses thereof |
US9308252B2 (en) * | 2005-10-27 | 2016-04-12 | Cook Biotech, Inc. | Extracellular matrix materials as vaccine adjuvants for diseases associated with infectious pathogens or toxins |
US8778360B2 (en) * | 2005-10-27 | 2014-07-15 | University Of Notre Dame | Extracellular matrix cancer vaccine adjuvant |
US8802113B2 (en) * | 2005-10-27 | 2014-08-12 | University Of Notre Dame | Extracellular matrix cancer vaccine adjuvant |
WO2007053592A2 (en) * | 2005-10-31 | 2007-05-10 | Cook Incorporated | Composite stent graft |
US20070100350A1 (en) * | 2005-10-31 | 2007-05-03 | Deffenbaugh Daren L | Suture anchor cartridge holder, suture anchor cartridge and associated method |
US20070100351A1 (en) * | 2005-10-31 | 2007-05-03 | Deffenbaugh Daren L | Multiple suture anchor delivery device, suture anchor delivery kit and associated method |
US20070100352A1 (en) * | 2005-10-31 | 2007-05-03 | Deffenbaugh Daren L | Cartridge suture anchor delivery device, suture anchor delivery device and associated method |
US20070112360A1 (en) * | 2005-11-15 | 2007-05-17 | Patrick De Deyne | Bioprosthetic device |
CA2630452C (en) * | 2005-12-02 | 2011-02-22 | Cook Incorporated | Devices, systems, and methods for occluding a defect |
EP1962695A1 (en) * | 2005-12-22 | 2008-09-03 | NMT Medical, Inc. | Catch members for occluder devices |
WO2007079081A1 (en) * | 2005-12-29 | 2007-07-12 | Med Institute, Inc. | Endoluminal device including a mechanism for proximal or distal fixation, and sealing and methods of use thereof |
US7815923B2 (en) | 2005-12-29 | 2010-10-19 | Cook Biotech Incorporated | Implantable graft material |
WO2007081530A2 (en) * | 2006-01-03 | 2007-07-19 | Med Institute, Inc. | Endoluminal medical device for local delivery of cathepsin inhibitors |
US20070166396A1 (en) | 2006-01-06 | 2007-07-19 | University Of Pittsburgh | Extracellular matrix based gastroesophageal junction reinforcement device |
US9532943B2 (en) | 2010-12-20 | 2017-01-03 | Cormatrix Cardiovascular, Inc. | Drug eluting patch for the treatment of localized tissue disease or defect |
WO2007084725A2 (en) | 2006-01-19 | 2007-07-26 | Osteotech, Inc. | Injectable and moldable bone substitute materials |
AU2007210970B2 (en) * | 2006-01-31 | 2013-09-05 | Cook Biotech Incorporated | Fistula grafts and related methods and systems for treating fistulae |
WO2007098234A2 (en) * | 2006-02-21 | 2007-08-30 | Med Institute, Inc. | Graft material for prostheses |
US7648527B2 (en) * | 2006-03-01 | 2010-01-19 | Cook Incorporated | Methods of reducing retrograde flow |
US8870913B2 (en) | 2006-03-31 | 2014-10-28 | W.L. Gore & Associates, Inc. | Catch system with locking cap for patent foramen ovale (PFO) occluder |
CA2647505C (en) * | 2006-03-31 | 2014-07-29 | Nmt Medical, Inc. | Deformable flap catch mechanism for occluder device |
US8551135B2 (en) * | 2006-03-31 | 2013-10-08 | W.L. Gore & Associates, Inc. | Screw catch mechanism for PFO occluder and method of use |
CN101484090B (en) * | 2006-04-19 | 2011-04-27 | 威廉A·库克澳大利亚有限公司 | Twin bifurcated stent graft |
US8808310B2 (en) * | 2006-04-20 | 2014-08-19 | Integrated Vascular Systems, Inc. | Resettable clip applier and reset tools |
DE112007001197T5 (en) | 2006-05-16 | 2009-04-16 | Purdue Research Foundation, West Lafayette | Three-dimensional purified collagen matrices |
US20070269476A1 (en) * | 2006-05-16 | 2007-11-22 | Voytik-Harbin Sherry L | Engineered extracellular matrices control stem cell behavior |
EP2478872B1 (en) | 2006-05-30 | 2018-07-04 | Cook Medical Technologies LLC | Artificial valve prosthesis |
WO2007147127A2 (en) | 2006-06-15 | 2007-12-21 | Cook Incorporated | Methods, systems, and devices for the delivery of endoluminal prostheses |
CA2662901A1 (en) | 2006-06-21 | 2007-12-27 | Cook Incorporated | Fistula grafts and related methods and systems useful for treating gastrointestinal fistulae |
US8974542B2 (en) | 2006-06-27 | 2015-03-10 | University of Pittsburgh—of the Commonwealth System of Higher Education | Biodegradable elastomeric patch for treating cardiac or cardiovascular conditions |
US8556930B2 (en) | 2006-06-28 | 2013-10-15 | Abbott Laboratories | Vessel closure device |
US8535719B2 (en) * | 2006-07-07 | 2013-09-17 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Biohybrid elastomeric scaffolds and methods of use thereof |
US20080109070A1 (en) * | 2006-08-10 | 2008-05-08 | Wagner William R | Biodegradable elastomeric scaffolds containing microintegrated cells |
AU2007286657B2 (en) | 2006-08-24 | 2012-11-15 | Cook Medical Technologies Llc | Devices and methods for occluding a fistula |
US8870914B2 (en) * | 2006-09-12 | 2014-10-28 | Cook Medical Technologies Llc | Medical device and a method for sealing a puncture or an opening |
US20080063627A1 (en) * | 2006-09-12 | 2008-03-13 | Surmodics, Inc. | Tissue graft materials containing biocompatible agent and methods of making and using same |
AU2007297611B2 (en) | 2006-09-21 | 2013-02-07 | Purdue Research Foundation | Collagen preparation and method of isolation |
US20080082083A1 (en) * | 2006-09-28 | 2008-04-03 | Forde Sean T | Perforated expandable implant recovery sheath |
US8529959B2 (en) | 2006-10-17 | 2013-09-10 | Carmell Therapeutics Corporation | Methods and apparatus for manufacturing plasma based plastics and bioplastics produced therefrom |
EP2079490B1 (en) | 2006-10-23 | 2012-08-29 | Cook Biotech Incorporated | Processed ecm materials with enhanced component profiles |
US20080103505A1 (en) * | 2006-10-26 | 2008-05-01 | Hendrik Raoul Andre Fransen | Containment device for site-specific delivery of a therapeutic material and methods of use |
US7871440B2 (en) * | 2006-12-11 | 2011-01-18 | Depuy Products, Inc. | Unitary surgical device and method |
CA2674859A1 (en) * | 2007-01-10 | 2008-07-17 | Cook Biotech Incorporated | Implantable devices useful for reinforcing a surgically created stoma |
US8343536B2 (en) | 2007-01-25 | 2013-01-01 | Cook Biotech Incorporated | Biofilm-inhibiting medical products |
US9526642B2 (en) * | 2007-02-09 | 2016-12-27 | Taheri Laduca Llc | Vascular implants and methods of fabricating the same |
JP5662683B2 (en) | 2007-02-09 | 2015-02-04 | タヘリ ラドュカ エルエルシー | Apparatus and method for deploying an implantable device in a body |
WO2008101083A2 (en) | 2007-02-15 | 2008-08-21 | Cook Incorporated | Artificial valve prostheses with a free leaflet portion |
US8361503B2 (en) | 2007-03-02 | 2013-01-29 | University of Pittsburgh—of the Commonwealth System of Higher Education | Extracellular matrix-derived gels and related methods |
US8435551B2 (en) * | 2007-03-06 | 2013-05-07 | Musculoskeletal Transplant Foundation | Cancellous construct with support ring for repair of osteochondral defects |
WO2008124603A1 (en) | 2007-04-05 | 2008-10-16 | Nmt Medical, Inc. | Septal closure device with centering mechanism |
GB2461461B (en) * | 2007-04-06 | 2012-07-25 | Cook Biotech Inc | Fistula plugs having increased column strength and fistula plug delivery apparatuses and methods |
US9138562B2 (en) | 2007-04-18 | 2015-09-22 | W.L. Gore & Associates, Inc. | Flexible catheter system |
US8492332B2 (en) * | 2007-04-19 | 2013-07-23 | Fibralign Corporation | Oriented collagen-based materials, films and methods of making same |
NZ580786A (en) * | 2007-04-24 | 2012-05-25 | Univ Western Australia | Tenocyte containing bioscaffolds and treatment using the same |
US8591930B2 (en) * | 2007-04-27 | 2013-11-26 | Cook Biotech Incorporated | Growth factor modified extracellular matrix material preparation and methods for preparation and use thereof |
US9283302B2 (en) | 2011-12-16 | 2016-03-15 | Cormatrix Cardiovascular, Inc. | Extracellular matrix encasement structures and methods |
US20080279833A1 (en) | 2007-05-10 | 2008-11-13 | Matheny Robert G | Laminate sheet articles for tissue regeneration |
ES2612538T3 (en) | 2007-05-29 | 2017-05-17 | Christopher B. Reid | Methods for production and uses of multipotent cell populations, pluripotent cell populations, differentiated cell populations, and HIV resistant cell populations |
US20090142400A1 (en) * | 2007-05-31 | 2009-06-04 | Hiles Michael C | Analgesic coated medical product |
US8226681B2 (en) * | 2007-06-25 | 2012-07-24 | Abbott Laboratories | Methods, devices, and apparatus for managing access through tissue |
US8535349B2 (en) * | 2007-07-02 | 2013-09-17 | Cook Biotech Incorporated | Fistula grafts having a deflectable graft body portion |
US20090024106A1 (en) * | 2007-07-17 | 2009-01-22 | Morris Edward J | Method and apparatus for maintaining access |
JP5264907B2 (en) | 2007-08-08 | 2013-08-14 | ザ クリーブランド クリニック ファウンデイション | Endovascular prosthetic device and endovascular prosthetic system using the same |
US9113851B2 (en) | 2007-08-23 | 2015-08-25 | Cook Biotech Incorporated | Fistula plugs and apparatuses and methods for fistula plug delivery |
US20090069843A1 (en) * | 2007-09-10 | 2009-03-12 | Agnew Charles W | Fistula plugs including a hydration resistant component |
US8029560B2 (en) * | 2007-09-12 | 2011-10-04 | Cook Medical Technologies Llc | Enhanced remodelable materials for occluding bodily vessels |
US20090136553A1 (en) * | 2007-09-25 | 2009-05-28 | Gerlach Jorg C | Triggerably dissolvable hollow fibers for controlled delivery |
US9023342B2 (en) | 2007-09-27 | 2015-05-05 | Carlos A. Alvarado | Tissue grafting method |
US20100135964A1 (en) * | 2007-09-27 | 2010-06-03 | Alvarado Carlos A | Tissue grafting method |
US10500309B2 (en) * | 2007-10-05 | 2019-12-10 | Cook Biotech Incorporated | Absorbable adhesives and their formulation for use in medical applications |
US20090112238A1 (en) * | 2007-10-26 | 2009-04-30 | Vance Products Inc., D/B/A Cook Urological Inc. | Fistula brush device |
WO2009061848A2 (en) * | 2007-11-07 | 2009-05-14 | Ovalis, Inc. | Systems devices and methods for achieving transverse orientation in the treatment of septal defects |
JP5214223B2 (en) * | 2007-11-15 | 2013-06-19 | 船井電機株式会社 | projector |
US7846199B2 (en) * | 2007-11-19 | 2010-12-07 | Cook Incorporated | Remodelable prosthetic valve |
US8057532B2 (en) * | 2007-11-28 | 2011-11-15 | Cook Medical Technologies Llc | Implantable frame and valve design |
CA2708615C (en) * | 2007-12-10 | 2019-12-31 | Purdue Research Foundation | Collagen-based matrices with stem cells |
US8893947B2 (en) * | 2007-12-17 | 2014-11-25 | Abbott Laboratories | Clip applier and methods of use |
US20090157101A1 (en) | 2007-12-17 | 2009-06-18 | Abbott Laboratories | Tissue closure system and methods of use |
US8257434B2 (en) | 2007-12-18 | 2012-09-04 | Cormatrix Cardiovascular, Inc. | Prosthetic tissue valve |
US8679176B2 (en) | 2007-12-18 | 2014-03-25 | Cormatrix Cardiovascular, Inc | Prosthetic tissue valve |
US20090157177A1 (en) * | 2007-12-18 | 2009-06-18 | Matheny Robert G | Sewing Ring for a Prosthetic Tissue Valve |
US20090157170A1 (en) * | 2007-12-18 | 2009-06-18 | Matheny Robert G | Trileaflet Semi-Lunar Prosthetic Tissue Valve |
US7841502B2 (en) * | 2007-12-18 | 2010-11-30 | Abbott Laboratories | Modular clip applier |
US7815687B2 (en) * | 2007-12-18 | 2010-10-19 | Med Institute, Inc. | Method of promoting cell proliferation and ingrowth by injury to the native tissue |
US20090187215A1 (en) * | 2007-12-19 | 2009-07-23 | Abbott Laboratories | Methods and apparatus to reduce a dimension of an implantable device in a smaller state |
US8211165B1 (en) | 2008-01-08 | 2012-07-03 | Cook Medical Technologies Llc | Implantable device for placement in a vessel having a variable size |
US9283266B2 (en) * | 2008-02-28 | 2016-03-15 | University Of Notre Dame | Metastasis inhibition preparations and methods |
EP2259809B1 (en) * | 2008-02-29 | 2016-05-25 | Cook Biotech Incorporated | Coated embolization device |
WO2009111069A1 (en) * | 2008-03-05 | 2009-09-11 | Musculoskeletal Transplant Foundation | Cancellous constructs, cartilage particles and combinations of cancellous constructs and cartilage particles |
US20130165967A1 (en) | 2008-03-07 | 2013-06-27 | W.L. Gore & Associates, Inc. | Heart occlusion devices |
US20100008965A1 (en) * | 2008-04-01 | 2010-01-14 | Pavalko Fredrick M | Biocompatible medical products having enhanced anti-thrombogenic properties |
US8128686B2 (en) * | 2008-04-18 | 2012-03-06 | Cook Medical Technologies Llc | Branched vessel prosthesis |
CA2721507C (en) | 2008-04-18 | 2017-10-03 | Collplant Ltd. | Methods of generating and using procollagen |
EP2113261B1 (en) * | 2008-04-29 | 2013-11-06 | Proxy Biomedical Limited | A Tissue Repair Implant |
GB2471632B (en) * | 2008-05-02 | 2012-04-18 | Cook Biotech Inc | Self deploying SIS in needle |
US20110184439A1 (en) * | 2008-05-09 | 2011-07-28 | University Of Pittsburgh-Of The Commonwealth System Of Higher Education | Biological Matrix for Cardiac Repair |
US9282965B2 (en) * | 2008-05-16 | 2016-03-15 | Abbott Laboratories | Apparatus and methods for engaging tissue |
US20090318956A1 (en) * | 2008-05-20 | 2009-12-24 | Belef W Martin | Wire-Like And Other Devices For Treating Septal Defects And Systems And Methods For Delivering The Same |
WO2009146369A1 (en) | 2008-05-29 | 2009-12-03 | Cook Biotech Incorporated | Devices and methods for treating rectovaginal and other fistulae |
CA2728240C (en) * | 2008-06-10 | 2016-11-15 | Cook Biotech Incorporated | Quilted implantable graft |
US9295757B2 (en) * | 2008-06-10 | 2016-03-29 | Cook Biotech Incorporated | Quilted implantable graft |
US8118832B1 (en) | 2008-06-16 | 2012-02-21 | Morris Innovative, Inc. | Method and apparatus for sealing access |
JP2011526811A (en) * | 2008-07-01 | 2011-10-20 | クック・バイオテック・インコーポレイテッド | Isolated extracellular matrix material containing subserosa fascia |
WO2010014021A1 (en) | 2008-07-30 | 2010-02-04 | Mesynthes Limited | Tissue scaffolds derived from forestomach extracellular matrix |
US10086079B2 (en) | 2008-08-11 | 2018-10-02 | Fibralign Corporation | Biocomposites and methods of making the same |
US8513382B2 (en) * | 2008-08-11 | 2013-08-20 | Fibralign Corporation | Biocomposites and methods of making the same |
EP3184552B1 (en) | 2008-09-02 | 2020-08-12 | Tautona Group LP | Threads of hyaluronic acid, methods of making thereof and uses thereof |
CN101366975B (en) * | 2008-09-03 | 2011-07-20 | 陕西瑞盛生物科技有限公司 | Preparation method for cellfree intestinum tenue submucosa biological material |
US20110190680A1 (en) | 2008-09-29 | 2011-08-04 | Yoram Vodovotz | Self-Regulating Device for Modulating Inflammation |
US8398676B2 (en) * | 2008-10-30 | 2013-03-19 | Abbott Vascular Inc. | Closure device |
WO2010065843A2 (en) | 2008-12-05 | 2010-06-10 | University Of Pittsburgh-Of The Commonwealth System Of Higher Education | Biologic scaffold for prevention of pulmonary fibrosis |
US8734502B2 (en) | 2008-12-17 | 2014-05-27 | Cook Medical Technologies Llc | Tapered stent and flexible prosthesis |
US8858594B2 (en) * | 2008-12-22 | 2014-10-14 | Abbott Laboratories | Curved closure device |
US8323312B2 (en) * | 2008-12-22 | 2012-12-04 | Abbott Laboratories | Closure device |
WO2010078478A1 (en) | 2008-12-31 | 2010-07-08 | Cook Biotech Incorporated | Tissue adjuvants and medical products including the same |
US8469779B1 (en) | 2009-01-02 | 2013-06-25 | Lifecell Corporation | Method for debristling animal skin |
US9089311B2 (en) * | 2009-01-09 | 2015-07-28 | Abbott Vascular Inc. | Vessel closure devices and methods |
US9486191B2 (en) | 2009-01-09 | 2016-11-08 | Abbott Vascular, Inc. | Closure devices |
US20100179589A1 (en) * | 2009-01-09 | 2010-07-15 | Abbott Vascular Inc. | Rapidly eroding anchor |
US9414820B2 (en) * | 2009-01-09 | 2016-08-16 | Abbott Vascular Inc. | Closure devices, systems, and methods |
US9173644B2 (en) | 2009-01-09 | 2015-11-03 | Abbott Vascular Inc. | Closure devices, systems, and methods |
US20100185234A1 (en) * | 2009-01-16 | 2010-07-22 | Abbott Vascular Inc. | Closure devices, systems, and methods |
US20100183523A1 (en) * | 2009-01-22 | 2010-07-22 | Wagner Richard E | Dental composition and method |
WO2010088678A2 (en) | 2009-02-02 | 2010-08-05 | Cook Biotech Incorporated | Medical bead products |
WO2010096458A1 (en) * | 2009-02-18 | 2010-08-26 | Cormatrix Cardiovascular, Inc. | Compositions and methods for preventing cardiac arrhythmia |
US9277999B2 (en) * | 2009-02-27 | 2016-03-08 | University of Pittsburgh—of the Commonwealth System of Higher Education | Joint bioscaffolds |
US8672993B2 (en) * | 2009-03-26 | 2014-03-18 | Cook Medical Technologies Llc | Pararenal stent graft |
WO2010129162A1 (en) | 2009-05-06 | 2010-11-11 | Hansa Medical Products, Inc. | Self-adjusting medical device |
US20120029556A1 (en) | 2009-06-22 | 2012-02-02 | Masters Steven J | Sealing device and delivery system |
US8956389B2 (en) | 2009-06-22 | 2015-02-17 | W. L. Gore & Associates, Inc. | Sealing device and delivery system |
US8652500B2 (en) | 2009-07-22 | 2014-02-18 | Acell, Inc. | Particulate tissue graft with components of differing density and methods of making and using the same |
US8298586B2 (en) | 2009-07-22 | 2012-10-30 | Acell Inc | Variable density tissue graft composition |
US20110054492A1 (en) | 2009-08-26 | 2011-03-03 | Abbott Laboratories | Medical device for repairing a fistula |
CN102481390B (en) * | 2009-09-02 | 2017-03-08 | 生命细胞公司 | Blood vessel graft from acellular tissue matrix |
WO2011031827A2 (en) | 2009-09-09 | 2011-03-17 | Cook Biotech Incorporated | Manufacture of extracellular matrix products using supercritical or near supercritical fluids |
US8663086B2 (en) | 2009-09-28 | 2014-03-04 | Cook Biotech Incorporated | Medical reinforcement graft |
US8716438B2 (en) | 2009-10-09 | 2014-05-06 | University of Pittsburgh—of the Commonwealth System of Higher Education | Matricryptic ECM peptides for tissue reconstruction |
US8846059B2 (en) | 2009-12-08 | 2014-09-30 | University Of Notre Dame | Extracellular matrix adjuvant and methods for prevention and/or inhibition of ovarian tumors and ovarian cancer |
US20110150934A1 (en) * | 2009-12-18 | 2011-06-23 | University Of Notre Dame | Ovarian Tumor Tissue Cell Preparations/Vaccines for the Treatment/Inhibition of Ovarian Tumors and Ovarian Cancer |
US8329219B2 (en) | 2009-12-22 | 2012-12-11 | Cook Biotech Incorporated | Methods for producing ECM-based biomaterials |
WO2011087743A2 (en) | 2009-12-22 | 2011-07-21 | University Of Pittsburgh-Of The Commonwealth System Of Higher Education | Decellularized adipose cell growth scaffold |
US8303624B2 (en) * | 2010-03-15 | 2012-11-06 | Abbott Cardiovascular Systems, Inc. | Bioabsorbable plug |
AU2010201676B1 (en) | 2010-04-23 | 2010-07-22 | Cook Medical Technologies Llc | Curve forming stent graft |
US9901659B2 (en) | 2010-05-27 | 2018-02-27 | University of Pittsburgh—of the Commonwealth System of Higher Education | Wet-electrospun biodegradable scaffold and uses therefor |
US20130197893A1 (en) | 2010-06-07 | 2013-08-01 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Methods for modeling hepatic inflammation |
US10065046B2 (en) | 2010-07-15 | 2018-09-04 | Fibralign Corporation | Conductive biopolymer implant for enhancing tissue repair and regeneration using electromagnetic fields |
EP2598181B1 (en) | 2010-07-31 | 2021-04-21 | Cook Medical Technologies LLC | Collagenous tissue pocket for an implantable medical device, and manufacturing method therefor |
US8758399B2 (en) | 2010-08-02 | 2014-06-24 | Abbott Cardiovascular Systems, Inc. | Expandable bioabsorbable plug apparatus and method |
US8603116B2 (en) | 2010-08-04 | 2013-12-10 | Abbott Cardiovascular Systems, Inc. | Closure device with long tines |
US9101455B2 (en) | 2010-08-13 | 2015-08-11 | Cook Medical Technologies Llc | Preloaded wire for endoluminal device |
CA2747610C (en) | 2010-08-13 | 2014-09-16 | Cook Medical Technologies Llc | Precannulated fenestration |
WO2012024390A2 (en) | 2010-08-17 | 2012-02-23 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Biohybrid composite scaffold |
EP3610861A1 (en) | 2010-08-24 | 2020-02-19 | The Regents of the University of California | Compositions and methods for cardiac therapy |
EP2613818B1 (en) | 2010-09-10 | 2019-02-13 | Fibralign Corp. | Biodegradable multilayer constructs |
EP2621549B1 (en) | 2010-09-28 | 2015-10-21 | Cook Biotech Incorporated | Device for treating fistulae and other bodily openings and passageways |
DE112011102907T5 (en) | 2010-10-01 | 2013-06-20 | Cook Biotech Incorporated | Kits, components and methods for tissue reconstruction |
EP2525742B1 (en) | 2010-10-29 | 2015-03-18 | Cook Medical Technologies LLC | Medical device delivery system and deployment method |
US9198787B2 (en) | 2010-12-31 | 2015-12-01 | Cook Medical Technologies Llc | Conformable prosthesis delivery system and method for deployment thereof |
AU2011200858B1 (en) | 2011-02-28 | 2012-04-05 | Cook Medical Technologies Llc | Stent graft with valve arrangement |
US9149276B2 (en) | 2011-03-21 | 2015-10-06 | Abbott Cardiovascular Systems, Inc. | Clip and deployment apparatus for tissue closure |
US9375513B2 (en) | 2011-04-14 | 2016-06-28 | Lifecell Corporation | Regenerative materials |
SG194880A1 (en) | 2011-05-27 | 2013-12-30 | Cormatrix Cardiovascular Inc | Sterilized, acellular extracellular matrix compositions and methods ofmaking thereof |
BR112013030482A2 (en) | 2011-05-27 | 2016-09-27 | Cormatrix Cardiovascular Inc | method of regeneration of an atrioventricular valve and duct of extracellular matrix material |
WO2012170538A2 (en) | 2011-06-06 | 2012-12-13 | Cook Medical Technologies Llc | Vascular occlusion devices and methods |
US8915941B2 (en) | 2011-06-14 | 2014-12-23 | Cook Medical Technologies Llc | Fistula closure devices and methods |
US10022263B2 (en) | 2011-07-14 | 2018-07-17 | Cook Medical Technologies Llc | Sling-based treatment of obstructive sleep apnea |
US9089523B2 (en) | 2011-07-28 | 2015-07-28 | Lifecell Corporation | Natural tissue scaffolds as tissue fillers |
US9770232B2 (en) | 2011-08-12 | 2017-09-26 | W. L. Gore & Associates, Inc. | Heart occlusion devices |
JP2014529470A (en) | 2011-09-01 | 2014-11-13 | クック・メディカル・テクノロジーズ・リミテッド・ライアビリティ・カンパニーCook Medical Technologies Llc | Aneurysm occlusion clip |
US8728148B2 (en) | 2011-11-09 | 2014-05-20 | Cook Medical Technologies Llc | Diameter reducing tie arrangement for endoluminal prosthesis |
US20130138219A1 (en) | 2011-11-28 | 2013-05-30 | Cook Medical Technologies Llc | Biodegradable stents having one or more coverings |
US9332976B2 (en) | 2011-11-30 | 2016-05-10 | Abbott Cardiovascular Systems, Inc. | Tissue closure device |
JP5902827B2 (en) | 2011-12-09 | 2016-04-13 | アセル,インコーポレイテッド | Hemostatic device |
BR112014014975B1 (en) | 2011-12-20 | 2019-06-25 | Lifecell Corporation | A method of producing a fabric composition |
EP2793964B1 (en) | 2011-12-20 | 2019-03-20 | LifeCell Corporation | Sheet tissue products |
EP2985007B1 (en) | 2011-12-22 | 2019-11-13 | Cook Medical Technologies LLC | Preloaded wire for endoluminal device |
US9271821B2 (en) | 2012-01-24 | 2016-03-01 | Lifecell Corporation | Elongated tissue matrices |
WO2013119630A1 (en) | 2012-02-06 | 2013-08-15 | Cook Medical Technologies Llc | Artificial device deployment apparatus |
US10940167B2 (en) | 2012-02-10 | 2021-03-09 | Cvdevices, Llc | Methods and uses of biological tissues for various stent and other medical applications |
US9504458B2 (en) | 2012-02-17 | 2016-11-29 | Cook Biotech Incorporated | Methods and systems for treating complex fistulae |
EP2841116A1 (en) | 2012-04-24 | 2015-03-04 | Lifecell Corporation | Flowable tissue matrices |
ES2753156T3 (en) | 2012-07-13 | 2020-04-07 | Lifecell Corp | Improved adipose tissue treatment procedures |
US9308107B2 (en) | 2012-08-27 | 2016-04-12 | Cook Medical Technologies Llc | Endoluminal prosthesis and delivery device |
EP3332816B1 (en) | 2012-09-26 | 2020-11-04 | LifeCell Corporation | Processed adipose tissue |
US20140121750A1 (en) | 2012-10-31 | 2014-05-01 | Cook Medical Technologies Llc | Fixation Process For Nesting Stents |
US9669190B2 (en) * | 2012-11-28 | 2017-06-06 | Cook Medical Technologies Llc | Selectively positionable catheter cuff |
EP2745813A1 (en) | 2012-12-18 | 2014-06-25 | Cook Medical Technologies LLC | Preloaded wire for endoluminal device |
US9364209B2 (en) | 2012-12-21 | 2016-06-14 | Abbott Cardiovascular Systems, Inc. | Articulating suturing device |
US9861466B2 (en) | 2012-12-31 | 2018-01-09 | Cook Medical Technologies Llc | Endoluminal prosthesis |
US10828019B2 (en) | 2013-01-18 | 2020-11-10 | W.L. Gore & Associates, Inc. | Sealing device and delivery system |
CA2899724A1 (en) | 2013-02-06 | 2014-08-14 | Lifecell Corporation | Methods for localized modification of tissue products |
EP2953659B1 (en) | 2013-02-08 | 2019-10-16 | Acell, Inc. | Methods of manufacturing bioactive gels from extracellular matrix material |
AU2014214700B2 (en) | 2013-02-11 | 2018-01-18 | Cook Medical Technologies Llc | Expandable support frame and medical device |
EP2809264A4 (en) | 2013-03-01 | 2015-09-09 | Cormatrix Cardiovascular Inc | Two-piece prosthetic valve |
JP6205436B2 (en) | 2013-03-01 | 2017-09-27 | コーマトリックス カーディオバスキュラー, インコーポレイテッドCorMatrix Cardiovascular, Inc. | Anchored cardiovascular valve |
EP2964162B1 (en) | 2013-03-07 | 2018-01-17 | Cook Medical Technologies LLC | Tissue ingrowth intestinal bypass sleeve |
US9993330B2 (en) | 2013-03-13 | 2018-06-12 | Cook Medical Technologies Llc | Endoluminal prosthesis system |
US11065368B2 (en) | 2013-03-15 | 2021-07-20 | Cook Biotech Incorporated | Drug eluting graft constructs and methods |
US10973856B2 (en) | 2013-03-15 | 2021-04-13 | Cook Biotech Incorporated | ECM implant compositions and methods |
US9308084B2 (en) | 2013-05-03 | 2016-04-12 | Cormatrix Cardiovascular, Inc | Prosthetic tissue valves and methods for anchoring same to cardiovascular structures |
US10199950B1 (en) | 2013-07-02 | 2019-02-05 | Vlt, Inc. | Power distribution architecture with series-connected bus converter |
US9861662B2 (en) | 2013-07-03 | 2018-01-09 | University of Pittsburgh—of the Commonwealth System of Higher Education | Bone-derived extra cellular matrix gel |
CA2919504A1 (en) | 2013-08-01 | 2015-02-05 | Christine BRONIKOWSKI | Tissue adjustment implant |
US20150080940A1 (en) | 2013-09-13 | 2015-03-19 | Cook Medical Technologies Llc | Anti-tumor macrophage m1 morphology inducer |
US9878071B2 (en) | 2013-10-16 | 2018-01-30 | Purdue Research Foundation | Collagen compositions and methods of use |
AU2013254913B1 (en) | 2013-11-04 | 2014-09-25 | Cook Medical Technologies Llc | Stent graft with valve arrangement |
EP2893884A1 (en) | 2014-01-08 | 2015-07-15 | Cook Medical Technologies LLC | ECM strip to plug percutaneous heart valve leaks |
US10286119B2 (en) | 2014-01-24 | 2019-05-14 | University of Pittsburgh—of the Commonwealth System of Higher Education | Extracellular matrix mesh coating |
JP6681872B2 (en) | 2014-03-21 | 2020-04-15 | ユニバーシティ オブ ピッツバーグ −オブ ザ コモンウェルス システム オブ ハイヤー エデュケイション | Method for preparing final sterile hydrogel derived from extracellular matrix |
US9808230B2 (en) | 2014-06-06 | 2017-11-07 | W. L. Gore & Associates, Inc. | Sealing device and delivery system |
EP3197513B1 (en) | 2014-09-25 | 2023-08-02 | Acell, Inc. | Porous foams derived from extracellular matrix, porous foam ecm medical devices, and methods of use and making thereof |
US10959826B2 (en) | 2014-10-16 | 2021-03-30 | Cook Medical Technology LLC | Support structure for scalloped grafts |
US10077420B2 (en) | 2014-12-02 | 2018-09-18 | Histogenics Corporation | Cell and tissue culture container |
US10183152B2 (en) | 2014-12-12 | 2019-01-22 | Cook Medical Technologies Llc | Cinching peritoneal dialysis catheter |
NZ732814A (en) | 2014-12-22 | 2023-12-22 | Aroa Biosurgery Ltd | Laminated tissue graft product |
US9238090B1 (en) | 2014-12-24 | 2016-01-19 | Fettech, Llc | Tissue-based compositions |
US11129711B2 (en) | 2015-02-27 | 2021-09-28 | University of Pittsburgh—of the Commonwealth System of Higher Education | Double component mandrel for electrospun stentless, multi-leaflet valve fabrication |
US10583004B2 (en) | 2015-02-27 | 2020-03-10 | University of Pittsburgh — Of the Commonwealth System of Higher Education | Retrievable self-expanding non-thrombogenic low-profile percutaneous atrioventricular valve prosthesis |
WO2016172365A1 (en) | 2015-04-21 | 2016-10-27 | Purdue Research Foundation Office Of Technology Commercialization | Cell-collagen-silica composites and methods of making and using the same |
US10736991B2 (en) | 2015-09-18 | 2020-08-11 | University of Pittsburgh—of the Commonwealth System of Higher Education | Non-gelling soluble extracellular matrix with biological activity |
US10173027B2 (en) | 2015-10-07 | 2019-01-08 | Cook Medical Technologies Llc | Methods, medical devices and kits for modifying the luminal profile of a body vessel |
US20190046211A1 (en) | 2015-12-02 | 2019-02-14 | Cook Biotech Incorporated | Filamentous graft implants and methods of their manufacture and use |
WO2017100625A2 (en) | 2015-12-10 | 2017-06-15 | Cook Biotech Incorporated | Poly(ester urea) fiber devices and related methods |
WO2017151862A1 (en) | 2016-03-02 | 2017-09-08 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Matrix bound nanovesicles and their use |
US11389566B2 (en) | 2016-03-14 | 2022-07-19 | Regentys Corporation | Method and composition for treating inflammatory bowel disease |
US11331348B2 (en) | 2016-04-28 | 2022-05-17 | University of Pittsburgh—of the Commonwealth System of Higher Education | Compositions comprising extracellular matrix of primitive animal species and related methods |
WO2017210109A1 (en) | 2016-06-03 | 2017-12-07 | Lifecell Corporation | Methods for localized modification of tissue products |
EP3269328A3 (en) | 2016-06-08 | 2018-01-24 | Cook Medical Technologies LLC | Cardiac valve implant |
WO2018007849A1 (en) | 2016-07-05 | 2018-01-11 | Carlos Alvarado | Serous membrane for ocular surface disorders |
EP4335413A2 (en) | 2016-07-11 | 2024-03-13 | Cormatrix Cardiovascular, Inc. | Prosthetic tissue valves |
WO2018017611A1 (en) | 2016-07-18 | 2018-01-25 | Cook Biotech Incorporated | Implantable pouch with segmental lamination structure, and related methods of manufacture and use |
US20180071526A1 (en) | 2016-09-10 | 2018-03-15 | Cook Biotech Incorporated | Electrostimulative graft products, and related methods of use and manufacture |
US10500079B2 (en) | 2016-10-27 | 2019-12-10 | Cook Medical Technologies Llc | Preloaded branch wire loop constraint |
EP3320881B1 (en) | 2016-11-10 | 2019-09-04 | Cook Medical Technologies LLC | Diameter reduction constraint arrangement for a stent graft in combination with a stent graft |
US11191632B2 (en) | 2016-11-10 | 2021-12-07 | Cook Medical Technologies Llc | Temporary diameter reduction constraint arrangement for a stent graft in combination with a stent graft |
AU2017382173A1 (en) | 2016-12-22 | 2019-06-06 | Lifecell Corporation | Devices and methods for tissue cryomilling |
EP3585313A4 (en) | 2017-02-23 | 2020-12-30 | University of Pittsburgh - of The Commonwealth System of Higher Education | Stentless biopolymer heart valve replacement capable of living tissue regeneration |
EP3589294B1 (en) | 2017-03-02 | 2022-10-26 | University of Pittsburgh - Of the Commonwealth System of Higher Education | Extracellular matrix (ecm) hydrogel and soluble fraction thereof for use in the treatment of cancer |
EP4252842A3 (en) | 2017-03-02 | 2023-10-25 | University of Pittsburgh- Of the Commonwealth System of Higher Education | Ecm hydrogel for treating esophageal inflammation |
US11389569B2 (en) | 2017-04-03 | 2022-07-19 | University of Pittsburgh—of the Commonwealth System of Higher Education | Biodegradable, porous, thermally responsive injectable hydrogel as soft tissue defect filler |
EP3615568A4 (en) | 2017-04-25 | 2021-01-20 | Purdue Research Foundation | 3-dimensional (3d) tissue-engineered muscle for tissue restoration |
KR20190141775A (en) | 2017-05-05 | 2019-12-24 | 유니버시티 오브 피츠버그 - 오브 더 커먼웰쓰 시스템 오브 하이어 에듀케이션 | Application to the eye of a substrate-bound vesicle |
WO2019006218A1 (en) | 2017-06-29 | 2019-01-03 | Oconnor Peter | Implantable medical devices for tissue repositioning |
WO2019079195A1 (en) | 2017-10-16 | 2019-04-25 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Genetically modified mesenchymal stem cells for use in cardiovascular prosthetics |
CN115252910A (en) | 2017-10-18 | 2022-11-01 | 生命细胞公司 | Adipose tissue products and methods of production |
US11123375B2 (en) | 2017-10-18 | 2021-09-21 | Lifecell Corporation | Methods of treating tissue voids following removal of implantable infusion ports using adipose tissue products |
US11246994B2 (en) | 2017-10-19 | 2022-02-15 | Lifecell Corporation | Methods for introduction of flowable acellular tissue matrix products into a hand |
EP3697462B1 (en) | 2017-10-19 | 2023-07-12 | LifeCell Corporation | Flowable acellular tissue matrix products and methods of production |
US11291570B2 (en) | 2018-04-27 | 2022-04-05 | Cook Medical Technologies Llc | Hybrid stent and delivery system |
AU2018214103B1 (en) | 2018-08-09 | 2018-10-04 | Cook Medical Technologies Llc | A stent-graft |
JP2022513073A (en) | 2018-11-19 | 2022-02-07 | ザ ユナイテッド ステイツ オブ アメリカ アズ リプリゼンテッド バイ ザ セクレタリー、デパートメント オブ ヘルス アンド ヒューマン サービシーズ | Biodegradable tissue replacement implants and their use |
CA3130684A1 (en) | 2019-03-13 | 2020-09-17 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Acoustic extracellular matrix hydrogels and their use |
EP3976127A1 (en) | 2019-05-30 | 2022-04-06 | LifeCell Corporation | Biologic breast implant |
WO2021185728A1 (en) | 2020-03-16 | 2021-09-23 | Biosearch, S.A. | Biocomposites comprising probiotics, collagen and bacterial extracellular polysaccharide and uses thereof |
US11849951B2 (en) | 2020-07-27 | 2023-12-26 | Cook Biotech Incorporated | System and methods for supplying surgical staple line reinforcement |
AU2021315935A1 (en) | 2020-07-27 | 2023-03-30 | Cook Biotech Incorporated | Adhesive for surgical staple line reinforcement |
US11826490B1 (en) | 2020-12-29 | 2023-11-28 | Acell, Inc. | Extracellular matrix sheet devices with improved mechanical properties and method of making |
CA3220433A1 (en) | 2021-05-28 | 2022-12-01 | Arvydas Maminishkis | Biodegradable tissue scaffold with secondary matrix to host weakly adherent cells |
EP4347795A1 (en) | 2021-05-28 | 2024-04-10 | The United States of America, as represented by The Secretary, Department of Health and Human Services | Methods to generate macular, central and peripheral retinal pigment epithelial cells |
WO2023215885A1 (en) | 2022-05-05 | 2023-11-09 | Cook Biotech Incorporated | Subtissue implant material |
WO2023215883A1 (en) | 2022-05-05 | 2023-11-09 | Cook Biotech Incorporated | Photocrosslinkable synthetic polymers |
Family Cites Families (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
AT261800B (en) * | 1966-08-22 | 1968-05-10 | Braun Internat Gmbh B | Process for the manufacture of tubular, smooth or threaded tissue-blood vessel prostheses |
US4502159A (en) * | 1982-08-12 | 1985-03-05 | Shiley Incorporated | Tubular prostheses prepared from pericardial tissue |
-
1988
- 1988-07-11 US US07/217,299 patent/US4902508A/en not_active Expired - Lifetime
-
1989
- 1989-06-15 ZA ZA894551A patent/ZA894551B/en unknown
- 1989-06-15 IL IL9062289A patent/IL90622A/en unknown
- 1989-06-23 BR BR898907538A patent/BR8907538A/en not_active IP Right Cessation
- 1989-06-23 EP EP89908901A patent/EP0424463B1/en not_active Expired - Lifetime
- 1989-06-23 CH CH902/90A patent/CH681506A5/de not_active IP Right Cessation
- 1989-06-23 HU HU894789A patent/HU207448B/en not_active IP Right Cessation
- 1989-06-23 WO PCT/US1989/002776 patent/WO1990000395A1/en active IP Right Grant
- 1989-06-23 CH CH3792/91A patent/CH681856A5/de not_active IP Right Cessation
- 1989-06-23 JP JP1508210A patent/JP2539934B2/en not_active Expired - Lifetime
- 1989-06-23 DE DE68918943T patent/DE68918943T2/en not_active Expired - Lifetime
- 1989-06-23 AT AT89908901T patent/ATE112963T1/en not_active IP Right Cessation
- 1989-06-23 KR KR1019900700514A patent/KR0131821B1/en not_active IP Right Cessation
- 1989-06-27 AU AU37091/89A patent/AU613499B2/en not_active Expired
- 1989-06-30 PH PH38883A patent/PH26921A/en unknown
- 1989-07-03 NZ NZ229797A patent/NZ229797A/en unknown
- 1989-07-06 MX MX016707A patent/MX171671B/en unknown
- 1989-07-07 PT PT91096A patent/PT91096B/en not_active IP Right Cessation
- 1989-07-07 CA CA000605031A patent/CA1335432C/en not_active Expired - Lifetime
- 1989-07-10 DK DK198903405A patent/DK175719B2/en not_active IP Right Cessation
- 1989-07-10 CN CN89104864A patent/CN1018893B/en not_active Expired
- 1989-07-10 ES ES8902418A patent/ES2019146A6/en not_active Expired - Fee Related
- 1989-07-11 IE IE222289A patent/IE67279B1/en not_active IP Right Cessation
- 1989-07-11 AR AR89314366A patent/AR244539A1/en active
-
1990
- 1990-12-21 OA OA59928A patent/OA09633A/en unknown
-
1991
- 1991-01-09 FI FI910113A patent/FI910113A0/en unknown
Also Published As
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA1335432C (en) | Tissue graft composition and method | |
US4956178A (en) | Tissue graft composition | |
Badylak et al. | Small intestinal submucosa as a large diameter vascular graft in the dog | |
JP5930402B2 (en) | Vascular graft derived from acellular tissue matrix | |
Lantz et al. | Small intestinal submucosa as a small-diameter arterial graft in the dog | |
Lantz et al. | Small intestinal submucosa as a vascular graft: a review | |
DE60133377T2 (en) | DEZELLULARIZED VASCULAR TRESES | |
NZ245286A (en) | Graft for a nerve or vessel made from amnion and/or chorion | |
Wesolow | The healing of arterial prostheses-the state of the art | |
Marois et al. | In vivo evaluation of hydrophobic and fibrillar microporous polyetherurethane urea graft | |
Salles et al. | Early experience with crimped bovine pericardial conduit for arterial reconstruction | |
RU2037317C1 (en) | Tissular transplant | |
TW476652B (en) | Artificial blood vessel | |
JP5610268B2 (en) | Method for decellularization of biological tissue with hypertonic electrolyte solution | |
Fahner et al. | Morphological and functional alterations in glycerol preserved rat aortic allografts | |
KR101582202B1 (en) | Vascular Patch using Cocoon and Method for manufacturing thereof | |
Jarrell et al. | Perspectives in vascular surgery--biocompatible vascular surfaces: the past and future role of endothelial cells. | |
Osinowo et al. | The use of glycerol-preserved homologous dura mater grafts in cardiac surgery: the Southampton experience | |
JPH04300559A (en) | Composite artificial blood vessel | |
KITTLE et al. | A Preliminary Investigation of Dermal Heterografts (Leather) as Prostheses for Vascular Defects | |
Godart et al. | Patency and development of stenosis in modified Blalock-Taussig shunts constructed using expanded polytetrafluoroethylene | |
Schulte-Wrede et al. | Lyophilized veins studied by scanning electron microscopy | |
Guidoin et al. | Processed human umbilical veins as arterial substitutes—evaluation in canine models | |
ZECH et al. | Experimental Vascular Grafts: VII. Effects of Growth on Pericardial Autografts | |
Ochsner et al. | Experimental Evaluation of a Marlex Vascular Prosthesis. |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
MKEX | Expiry |