US20060047312A1 - Biomaterial for suturing - Google Patents

Biomaterial for suturing Download PDF

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Publication number
US20060047312A1
US20060047312A1 US11/056,241 US5624105A US2006047312A1 US 20060047312 A1 US20060047312 A1 US 20060047312A1 US 5624105 A US5624105 A US 5624105A US 2006047312 A1 US2006047312 A1 US 2006047312A1
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Prior art keywords
biomaterial
cells
suturing
support material
cell
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Abandoned
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US11/056,241
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English (en)
Inventor
Damian Garcia Olmo
Gema Miguel
Manuel Gonzalez de la Pena
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Universidad Autonoma de Madrid
Tigenix SA
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Cellerix SA
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Priority to US11/167,061 priority Critical patent/US20060045872A1/en
Assigned to UNIVERSIDAD AUTONOMA DE MADRID reassignment UNIVERSIDAD AUTONOMA DE MADRID ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: GARCIA-OLMO, DAMIAN
Assigned to CELLERIX, S.L. reassignment CELLERIX, S.L. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: DE LA PENA, MANUEL A. GONZALEZ, MIGUEL, GEMA FERNANDEZ
Publication of US20060047312A1 publication Critical patent/US20060047312A1/en
Priority to US12/533,875 priority patent/US20090292311A1/en
Priority to US13/457,053 priority patent/US20120213750A1/en
Priority to US14/017,152 priority patent/US10548924B2/en
Priority to US15/467,984 priority patent/US10780132B2/en
Priority to US16/436,578 priority patent/US11253632B2/en
Priority to US16/722,872 priority patent/US20200206274A1/en
Abandoned legal-status Critical Current

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    • 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
    • A61L27/38—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 containing added animal cells
    • A61L27/3804—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 containing added animal cells characterised by specific cells or progenitors thereof, e.g. fibroblasts, connective tissue cells, kidney cells
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
    • 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
    • A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
    • A61L17/14—Post-treatment to improve physical properties
    • A61L17/145—Coating
    • 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
    • A61L27/38—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 containing added animal cells
    • A61L27/3839—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 containing added animal cells characterised by the site of application in the body
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N5/00—Undifferentiated human, animal or plant cells, e.g. cell lines; Tissues; Cultivation or maintenance thereof; Culture media therefor
    • C12N5/06—Animal cells or tissues; Human cells or tissues
    • C12N5/0602—Vertebrate cells
    • C12N5/0652—Cells of skeletal and connective tissues; Mesenchyme
    • C12N5/0662—Stem cells
    • C12N5/0667—Adipose-derived stem cells [ADSC]; Adipose stromal stem cells

Definitions

  • This invention refers to a material for suturing and its applications. More specifically, the invention refers to a material for suturing covered with cells that contribute in a biologically active way to the tissue repair process and therefore the healing of wounds.
  • the suture has been the classical method for bringing the edges of the wound together in order to achieve the rapid tissue repair.
  • Primary intention healing by suturing consists of bringing the edges of the wound together by introducing a suture in the tissues using a metal needle joined at one of its ends, passing the needle successively between both sides of the incision, thereby passively facilitating the closure of the wound.
  • Sutures are also used in surgical practice to stop bleeding (haemostasis) and to repair organs and other structures of the human body. In some situations, these sutures are particularly delicate due to the healing difficulties of the tissues they are used on. This is the case of sutures used for the colon wall, for tendons and in microsurgery involving nerve tissue and blood vessels.
  • staples are an alternative to the classical suturing method. It enables the primary closure of the tissue to take place more rapidly, reduces the loss of blood, diminishes contamination and preserves blood flow.
  • a limiting factor in the use of staples as a method of primary intention healing is the need to have access to the upper and lower part of the tissues being joined together. Furthermore, the force exerted when inserting the staples may cause the tissue to tear.
  • One solution to this problem in a new attempt at passive contention, i.e., without contributing in a biologically active way to improving the healing and tissue repair process, is to apply bioadhesives to the area where the staples are inserted.
  • biocompatible adhesives work by facilitating the apposition of the tissues, providing a stable and regular biomechanical tension all along the incision, which helps to maintain tissue structure around the wound. They can be divided into two categories: biological adhesives, synthesized from plasmatic proteins; and synthetic polymers, primarily cyanoacrylate and its derivatives.
  • Sutures have now evolved to the point where there are sutures specifically designed for each type of operation.
  • the surgeon chooses the type of suture based on the nature of the procedure, the characteristics of the patient, the pressure which the suture must support, etc.
  • suturing thread available on the market today: absorbable, non-absorbable, monofilament and multifilament sutures, natural and synthetic, etc.
  • EP0652017 protects biomaterials, the definition of which would include suturing materials, which have been coated to prevent blood constituents from adhering to the suture and thus delaying coagulation.
  • the patent also describes the use of anticoagulants and substances with anti-inflammatory properties as the biomaterial coating.
  • U.S. Pat. No. 6,264,675 protects a suturing material composed of a suture coated with an adhesive material whose adhesive properties are activated when inserted into the tissue to be repaired, which is joined to a needle at one of its ends.
  • the bioadhesive used in this type of intervention solves one of the main problems associated with suturing, since it prevents the loss of fluids through the needle insertion points.
  • one of the disadvantages is the allergenic nature and potential toxicity of bioadhesives.
  • suturing methods described above contribute passively to the apposition of the tissues without participating in a biologically active way in the tissue healing.
  • the stromal cells of bone marrow contain, among others, a population of cells known as mesenchymal stem cells (Friedenstein et al., 1976; Caplan et al., 1991; Pittenger et al., 1999). Studies conducted on these cells have demonstrated that there are different lineages of mesenchymal cells such as adipocytes (Beresford et al., 1972), chondrocytes (Johnstone et al., 1998), mioblasts (Wakitani et al., 1995), and osteoblasts (Haynesworth et al., 1992).
  • multipotent stem cells which can be easily isolated have been identified (Zuk et al., 2001) in adipose tissue, which like bone marrow is derived from the embryonic mesoderm and is composed of a heterogeneous cell population. These cells are similar, though not identical, to the mesenchymal stem cells in bone marrow (De Ugarte et al., 2003) and can also be broken down into multiple mesenchymal cell lineages (chondrocytes, osteocytes, adipocytes, and mioblasts). Moreover, like the mesenchymal stem cells in bone marrow, they have neuron differentiating capacity (Zuk et al., 2002).
  • the ability to join biological tissues together has been one of the principal challenges of biomedical research.
  • the ideal suture is that which is resistant and easy to handle, does not induce an inflammatory response by the tissue and does not foster infection. In other words, that which not only closes the wound but also contributes to full healing.
  • This invention refers to a suturing material that makes it possible to bring the ends of the tissue together thus facilitating healing and accelerating the repair process by contributing in a biologically active way to the formation of scar tissue.
  • the use of such material also causes less inflammation of the sutured tissue which reduces the time required for the open wound to heal, minimizing the risk of infection and the loss of body fluids and consequently the number of surgical failures.
  • the biomaterial for suturing referred to in this invention is composed of a physiologically compatible material known as support material which is coated with a cellular population with proliferative and/or differentiation capacity, characteristics which are necessary to participate in the regeneration of the sutured tissue.
  • this biomaterial for suturing is not limited to bringing the two ends of the open wound together, but also contributes actively to scar tissue formation, accelerating the tissue repair process.
  • This innovation represents an important advantage, especially in the case of sutured internal organs and particularly for intestinal anastomosis as a result of resectioning the gastrointestinal tract or urogenital area.
  • a first aspect of the invention provides a biomaterial for suturing which is useful as a therapeutic agent in the treatment of wounds, both accidental and surgical, and in suturing tissues.
  • This biomaterial is composed of a suturing support coated with a cellular population characterized by its proliferative and/or differentiation capacity.
  • the support material for suturing includes but is not limited to staples, absorbable thread, non-absorbable thread, natural thread, synthetic thread, monofilament thread and multifilament thread (also called braids).
  • the support material for suturing includes but is not limited to absorbable thread, non-absorbable thread, natural thread, synthetic thread, monofilament thread and multifilament thread or braids joined to a metal suturing needle.
  • the support material for suturing is composed of absorbable synthetic monofilament thread joined to a metal suturing needle.
  • a second aspect of the invention refers to the use of cells with proliferative and/or differentiation capacity as the cellular population used to coat the biomaterial for suturing.
  • a preferred aspect refers to the use of stem cells as the cellular population used to coat the biomaterial for suturing.
  • a more preferred aspect refers to the use of pluripotent stem cells, capable of differentiating into any kind of tissue, as the cellular population used to coat the biomaterial for suturing.
  • a more preferred aspect refers to the use of multipotent stem cells, capable of differentiating any kind of tissue, as the cellular population used to coat the biomaterial for suturing.
  • An especially preferred aspect refers to the use of adult multipotent stem cells as the cellular population used to coat the biomaterial for suturing.
  • the invention provides a biomaterial for suturing composed of a suturing thread joined to a metal needle at one end as the support material and adult multipotent stem cells as the cellular population used for coating.
  • the adult multipotent stem cells capable of differentiating between cell types used as the coating population are isolated from human adipose tissue.
  • the preferred source of adipose tissue is subdermal fatty tissue and the preferred collection method is liposuction.
  • Another aspect of the invention refers to the use of cellular populations of an autologous, alogenic or xenogenic nature, or a combination of these.
  • the cellular population used for the coating will preferably be autologous cells.
  • An especially preferred aspect refers to the use of adult multipotent autologous stem cells isolated by liposuction as the cellular population for coating the suturing biomaterial of the invention (Example 1).
  • the advantage of using adult autologous stem cells is that they are immunocompatible by nature and therefore do not cause inflammation problems or rejection. Furthermore, there are no legal or ethical impediments to using them.
  • the biomaterial for suturing includes adult autologous stem cells as the coating material, their use being restricted to the patient from whom the cells are taken.
  • a third aspect of the invention includes the use of stem cells which have at least one characteristic of a specialized cell, as the cellular population used to coat the biomaterial for suturing to which the invention refers.
  • a preferred embodiment refers to the use of progenitor cells from a specialized cellular lineage obtained from the patient's stem cells which express at least one of the characteristics of the specialized progenitor cells as the cellular population used to coat the biomaterial for suturing to which the invention refers. This prevents the generation of inflammatory problems and rejection, as and the components of the suturing material would be concealed from the immunological system by coating it with autologous stem cells, which would undoubtedly improve the tissue repair process.
  • a preferred aspect refers to the use of stem cells that have been induced to differentiate in vitro into cells that express at least one of the characteristics of a specialized cell as the cellular population for coating the biomaterial for suturing.
  • a more preferred aspect refers to the use of multipotent stem cells which have been induced to differentiate in vitro to cells that express at least one of the characteristics of a specialized cell as the cellular population for coating the biomaterial for suturing.
  • a fourth aspect of the invention refers to a biomaterial for suturing in which the cellular population for coating has been genetically modified.
  • a preferred embodiment refers to a biomaterial for suturing in which the cellular population for coating has been genetically modified to express factors that contribute to the tissue repair process, including but not limited to growth factors, morphogenetic factors, structural proteins and cytokines.
  • a fifth aspect of the invention refers to the biomaterial of the invention in which the cellular population for the coating is composed of a heterogeneous cellular population.
  • a heterogeneous cellular population is defined as that which includes different types of cells or cells in different stages of differentiation or a combination of both.
  • a sixth aspect of the invention provides a method for obtaining the biomaterial for suturing of the invention in which the cellular population for coating is joined to the support material by adhesion.
  • a preferred aspect of the invention provides a method for obtaining a biomaterial for suturing in which the cellular population for the coating is joined to the support material by adhesion. This method involves:
  • a more preferred aspect of the invention provides a method for obtaining a biomaterial for suturing in which the support material has been previously coated with a material, the purpose of which is to improve the adhesion of the cell population.
  • Said coating material of the support material includes but is not limited to peptides, antigens, proteins, antibodies, sugars and lipids. In an even more preferred aspect, said coating material would be extracellular matrix proteins from eukaryote cells or antibodies.
  • Another preferred aspect provides a method for obtaining the biomaterial for suturing which involves genetically modifying the cellular population of choice after expanding that cellular population.
  • An eighth aspect involves the use of the biomaterial for suturing of the invention in therapy.
  • a preferred aspect involves the use of the biomaterial for suturing to bring tissue edges together, which includes but is not limited to therapeutic applications in hemostasis, organ transplants, surgery of the gastrointestinal tract, surgery of the urogenital tract, surgery of the respiratory tract, eye surgery, vascular surgery, plastic and reconstructive surgery, surgery on muscle tissue, epithelial tissue, nerve tissues and the repair of tendons, osseous tissue and cartilaginous tissue.
  • a more preferred aspect of the invention refers to the use of the sutures coated with autologous stem cells in those cases where local inflammatory reaction generated by the suture could be harmful to the results of the surgical procedure.
  • An even more preferred aspect refers to the use of the biomaterial for suturing in bringing the edges of the tissue together in any surgical activities where an improvement to local scar formation capacity is desired.
  • An even more preferred aspect involves the use of the biomaterial for suturing to bring the edges of tissue together in intestinal anastomosis.
  • Another preferred aspect involves the use of the biomaterial for suturing to hold prostheses in place such as cardiac valves or neurosurgical valves.
  • Another aspect of the invention refers to the use of any prosthetic material (or device) used in medicine which is implanted in the human body and which frequently leads to biocompatibility problems, such as implant valves and surgical prostheses, which have been coated with cells.
  • FIGS. 1 a - 1 e show a phase contrast photomicrograph, in visible mode, of the different fragments of suturing thread used as support material in Example 1.
  • FIG. 1 a shows the absorbable thread type vicryl (Ethicon) ref. V460;
  • FIG. 1 b shows the type of absorbable thread type monocryl (Ethicon) ref. Y3110;
  • FIG. 1 c shows the type of absorbable thread Dexon II (USS-DG) Ref. 9819-41;
  • FIG. 1 d shows the type of absorbable thread Safil quick (B/Braun) ref. 0046030 and
  • FIG. 1 e shows the type of non-absorbable thread Ethilon (Ethicon) ref. W1621.
  • FIGS. 2 a - 2 e show a phase contrast photomicrograph, in ultraviolet mode, the degree of cellular coating achieved in the fragments of suturing thread used in example one after one week of incubation.
  • FIG. 2 a shows the absorbable thread type vicryl (Ethicon) ref. V460;
  • FIG. 2 b shows the type of absorbable thread type monocryl (Ethicon) ref. Y3110;
  • FIG. 2 c shows the type of absorbable thread Dexon II (USS-DG) Ref. 9819-41;
  • FIG. 2 d shows the type of absorbable thread Safil quick (B/Braun) ref. 0046030 and
  • FIG. 2 e shows the type of non-absorbable thread Ethilon (Ethicon) ref. W1621.
  • FIGS. 3 a - 3 b show the general appearance of the abdominal cavity of rats after being laparotomized on the fourth post-operative date.
  • a comparison of the general appearance (inflammation, general adhesions . . . ) enables us to differentiate two patterns in the evolution of scar tissue formation of the anastomotic suture.
  • FIG. 3 a shows a photograph of one of the rats (no. 1) in group A (surgery performed with the biomaterial for suturing of the invention).
  • FIG. 3 b shows a photograph of one of the rats (no. 3) in group B (surgery performed with Vicryl® 4/0 thread)
  • FIGS. 4 a - 4 b show a photograph of a colic segment which contained the anastomosis once a catheter had been introduced at the proximal end, before determining the rupture pressure.
  • FIG. 4 a shows a photograph of the colic segment of one of the rats (no. 1) in group A (surgery performed using the biomaterial for suturing of the invention).
  • FIG. 4 b shows a photograph of the colic segment of one of the rats (no. 3) in group B (surgery performed with Vicryl® 4/0 thread).
  • FIG. 5 shows a diagram that illustrates the variation in the physical resistance of a colic suture in the presence of increased intraluminal pressures, depending on how much time has elapsed.
  • the invention provides a biomaterial for suturing comprising a support material for suturing, preferably a suturing thread, and a cellular population covering the support material.
  • the cellular population used for coating is characterized by its proliferative and/or differentiation capacity.
  • the invention provides a biomaterial for suturing composed of a suturing thread joined to a metal needle at one of the ends as the support material and adult autologous stem cells obtained by liposuction for the cellular population.
  • the object of this experiment was to study the capacity of a certain type of cell to adhere to different types of suturing threads acting as the support material for the biomaterial for suturing of this invention.
  • Adherent adult human lipo-derived stem cells were used as the cellular population for coating, after first being transduced with retrovial vectors that code for Cop-GFP, green fluorescent protein, used as a gene marker.
  • the adipose tissue was obtained by liposuction.
  • a cannula with a blunt end was introduced into the subcutaneous space through a small periumbilical incision (less than 0.5 cm in diameter).
  • the suction was performed by moving the cannula along the adipose tissue compartment located under the abdominal wall, thus aiding the mechanical disruption of the adipose tissue.
  • a saline and epinephrine solution was injected as a vasoconstriction agent. 80-100 ml of raw lipoaspirate cells were obtained from each patient using this procedure.
  • the lipoaspirate was then washed with a phosphate and saline solution (PBS).
  • PBS phosphate and saline solution
  • the adipose tissue was then disrupted by digestion of the extracellular matrix with type II collagenase in saline solution (5 mg/ml) at 37° for 30 minutes to release the cellular fraction.
  • the collagenase was inactivated by adding an equivalent volume of DMEM medium with 10% fetal bovine serum.
  • the cellular suspension was centrifuged at 250 g for 10 minutes to obtain a cell deposit.
  • the cells were resuspended in DMEM medium with 10% fetal bovine serum.
  • NH4Cl was added at a final concentration of 0.16M and the cell; incubated for 10 minutes at room temperature to induce the lysis of erythrocytes present.
  • the suspension was centrifuged at 250-400 g and resuspended in DMEM-10% FBS with 1% ampicillin-streptomycin. Finally, the cells were inoculated at a rate of 20-30,000 cells per cm2 onto dishes.
  • the cells were kept in culture for 20-24 hours at 370 in an atmosphere with 5% CO2. After 24 hours of incubation, the dishes were washed with PBS to eliminate the cells that had not adhered and cellular remains.
  • Cop-GFP is a copepod green fluorescent protein (pontellina plumata) which makes it easy to identify and select the cells infected by direct fluorescence. The fluorescent protein does not enter the cellular nucleus. This is an advantage since the cells that are expressing the Cop-GFP protein can be easily distinguished from interfering fluorescent particles.
  • suturing threads Five different types were selected for testing as support material. Fragments measuring approximately 1 cm long were cut, introducing 2 thread fragments per bowl, on culturing dishes with 24 bowls.
  • the object of this test was to determine the characteristics of the biomaterial for suturing provided by this invention and the advantages it offers compared to conventional sutures by performing colical anastomosis in rats.
  • BDIX rats 12 adult BDIX rats with weights ranging between 130-260 grams were used in the experiment. Two to obtain the stem cells from the 4 rats from the subdermal adipose tissue and ten to study the colic sutures. The cell-coated threads were prepared following a protocol similar to that illustrated in example 1.
  • the BDIX rats are syngenic which means that they are genetically identical and immunologically compatible. Each rat was identified by a number from 1 to 10 and each one was assigned a batch of sutures with the same number.
  • the sample was divided into two groups depending on the suturing material used for the anastomosis:
  • the rats were laparotomized under general anaesthesia after 24 hours of fasting with “ad libitum” water.
  • the colon was completely sectioned at the mid-point of the transversal colon, taking care not to damage the margin vascularization and to prevent haemorrhaging.
  • the single layer everted anastomosis was then performed with 3 stitches. Each stitch was tied three times. When the anastomosis was complete, the colon was put back into the abdominal cavity and the laparotomy closed with 0 silk thread on two planes.
  • the animals were sacrificed by decapitation on the fourth day after surgery. With the animal in asystole, the abdomen was opened to evaluate the dehiscence, dilation, obstruction, general adhesions, difficulty in separating general adhesions and determination of adhered structures.
  • the measurement of resistance to intraluminal pressure can be expressed as the rupture pressure, i.e., the pressure at which an anastomosis subject to growing intraluminal pressure is disrupted or as the rupture tension which expresses the circular tension to which the wall is subjected at the time of the rupture.
  • the distal end was closed with a 1/0 silk suture.
  • the proximal end was similarly closed after introducing an intravenous perfusion catheter.
  • the catheter is connected to a three-stage valve or “T” system in which one of the lines goes to the capsule of a pressure transducer that registers the pressure variations and sends the signals to a digital polygraph system. The data are then sent to a computer for analysis and storage.
  • the other line is connect to a perfusion pump filled with physiological solution tinted with methylene blue to observe the time and place of the rupture.
  • Colic anastomosis was performed on 10 adult BDIX broken down into two groups, A and B, according to the suturing material used. Two of the animals used to evaluate the healing of the anastomosis, one from each group, had to be excluded from the study. During the surgery, one of the animals suffered a torn mesosigmoid while in another animal the anastomosis was torn when introducing the catheter in the distal end of the colic when measuring the rupture pressure.
  • Table 2 shows the results obtained for the different variable analysed in the evaluation of the anastomotic suture.
  • the adhesions are pathologically important since they alter the normal physiology of serous surfaces.
  • the animals in Group A showed a more regional pattern of adhesions which were easier to separate and a lower number of adhered structures, which implies a reduction of the complications caused by intraperitoneal adhesions: intestinal obstruction, chronic abdominal pain and infertility.
  • intestinal obstruction a component of the body
  • chronic abdominal pain a component of the body
  • infertility The use of a foreign matter in the abdominal cavity produces a high level of adhesions (Ellis H, 1962, Zarapico et al, 1972).
  • the decrease in the adhesions observed in the trial could have been due to the fact that the biomaterial of the invention is not recognized as something foreign by the body.
  • the average resistance of the anastomosis calculated as the rupture pressure, is 46.1575 mmHg, which is higher than the average resistance observed in Group B: 47.7325 mmHg.
  • the suture using the biomaterial of the invention showed greater resistance to pressure than the suture using conventional thread. Furthermore, the maximum rupture resistance value was seen in one of the animals in Group A and the lowest value was observed in Group B. The higher resistance to rupture of the anastomotic suture implies a lower risk of dehiscence, separation of part of the anastomosis, which is a serious complication and one of the leading causes of post-operative death in colic surgery.

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US11/056,241 2004-08-25 2005-02-14 Biomaterial for suturing Abandoned US20060047312A1 (en)

Priority Applications (7)

Application Number Priority Date Filing Date Title
US11/167,061 US20060045872A1 (en) 2004-08-25 2005-06-24 Use of adipose tissue-derived stromal stem cells in treating fistula
US12/533,875 US20090292311A1 (en) 2004-08-25 2009-07-31 Biomaterial for Suturing
US13/457,053 US20120213750A1 (en) 2004-08-25 2012-04-26 Use of adipose tissue-derived stromal stem cells in treating fistula
US14/017,152 US10548924B2 (en) 2004-08-25 2013-09-03 Use of adipose tissue-derived stromal stem cells in treating fistula
US15/467,984 US10780132B2 (en) 2004-08-25 2017-03-23 Use of adipose tissue-derived stromal stem cells in treating fistula
US16/436,578 US11253632B2 (en) 2004-08-25 2019-06-10 Biomaterial for suturing
US16/722,872 US20200206274A1 (en) 2004-08-25 2019-12-20 Use of adipose tissue-derived stromal stem cells in treating fistula

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
ESP200402083 2004-08-25
ES200402083A ES2264862B8 (es) 2004-08-25 2004-08-25 Biomaterial para sutura.

Related Child Applications (3)

Application Number Title Priority Date Filing Date
US11/065,461 Continuation-In-Part US20060073124A1 (en) 2004-08-25 2005-02-25 Identification and isolation of multipotent cells from non-osteochondral mesenchymal tissue
US11/167,061 Continuation-In-Part US20060045872A1 (en) 2004-08-25 2005-06-24 Use of adipose tissue-derived stromal stem cells in treating fistula
US12/533,875 Continuation US20090292311A1 (en) 2004-08-25 2009-07-31 Biomaterial for Suturing

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US10322206B2 (en) 2016-03-29 2019-06-18 Worcester Polytechnic Institute Compositions and methods for wound healing

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ES2264862A1 (es) 2007-01-16
WO2006035083A1 (es) 2006-04-06
DK1803472T3 (en) 2017-01-23
US20090292311A1 (en) 2009-11-26
US11253632B2 (en) 2022-02-22
EP1803472A1 (en) 2007-07-04
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EP1634608A1 (en) 2006-03-15
ES2264862B8 (es) 2017-01-20

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