[go: up one dir, main page]

WO2001034065A1 - Ligament obtenu par genie tissulaire - Google Patents

Ligament obtenu par genie tissulaire Download PDF

Info

Publication number
WO2001034065A1
WO2001034065A1 PCT/US2000/031033 US0031033W WO0134065A1 WO 2001034065 A1 WO2001034065 A1 WO 2001034065A1 US 0031033 W US0031033 W US 0031033W WO 0134065 A1 WO0134065 A1 WO 0134065A1
Authority
WO
WIPO (PCT)
Prior art keywords
scaffold
forming
tissue
sheet
cells
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.)
Ceased
Application number
PCT/US2000/031033
Other languages
English (en)
Inventor
James Cho Hong Goh
Kwan-Ho Chan
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Individual
Original Assignee
Individual
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Individual filed Critical Individual
Priority to AU15987/01A priority Critical patent/AU1598701A/en
Publication of WO2001034065A1 publication Critical patent/WO2001034065A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Classifications

    • 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
    • A61F2/08—Muscles; Tendons; Ligaments

Definitions

  • This invention generally relates to apparatus and methods for the manufacture of replacement tissue using tissue engineering methods. More particularly, this invention relates to apparatus and methods for the manufacture of tissue-engineered ligaments suitable for the treatment of ligament deficiencies in patients.
  • Prosthetic ligament replacements made of carbon fibers and Gore-Tex materials do not last a long period of time. Repeated loading of a prosthetic ligament in a young active patient leads to failure of the ligament. The release of debris from a failed ligament results in chronic inflammation of the joint, and osteolysis of bone, in and around the area of ligament attachments.
  • the current standard practice is to reconstruct a torn anterior cruciate ligament by substituting the torn ligament with a patient's own tissue.
  • the middle third of the patellar tendon or the hamstring tendons are commonly used as substitution ligaments.
  • the allograft patellar tendon, hamstring tendon or Achilles tendon from a donor can be used for reconstructing the ligament.
  • donor materials are associated with a risk of infectious disease transmission such as AIDS.
  • Using a patient's own tissue is also associated with morbidity at the donor site. For example, stress fracture of the patellar, quadriceps muscle weakness and a long rehabilitation period may result from the use of a patient's own tissue.
  • harvesting and preparation of autogeneous tissue prolongs surgery time.
  • LAD Prosthetic Ligament which was used as a scaffold for tissue ingrowth.
  • the LAD Prosthetic Ligament is not bioabsorbable. Therefore, whatever initial fibrous tissue that forms on the LAD Prosthetic Ligament is not subject to accommodating increasing loads and there is no stimulus for the fibrous tissue to proliferate to support increasing loads. Furthermore, the LAD Prosthetic Ligament is not an optimal structure for tissue ingrowth. Recent progress in tissue engineering has made it possible to harvest cells from a patient's own body or a donor. The harvested cells are then grown into the desired tissues on three-dimensional scaffolds, or hydrogel carriers, made of biodegradable polymers.
  • tissue include, but are not limited to, heart muscles, fat, cartilage, and skin.
  • the tissue grown outside of the body, together with the scaffold containing the tissue, is then transplanted into the patient to correct an existing defect. After transplantation, the cells may further replicate, reorganize and mature, depending on the environment of the host bed into which the cells were transplanted.
  • mesenchymal stem cells Two good sources of cells that are suitable for tissue engineering are embryonic stem cells and mesenchymal stem cells. These stem cells, when exposed to particular bioactive factors, also known as growth factors, can be directed to differentiate into different types of cell lines in a predictable way. For example, mesenchymal stem cells can be directed to differentiate into different types of tissue such as, but not limited to, skin, tendon, ligament and bone under suitable conditions. These conditions include exposing cells to certain growth factors. It is known that mesenchymal cells are directed to differentiate into fibroblast when exposed to interleukin. Furthermore, fibroblast is only able to differentiate into fibrocytes that are the mature cells of ligament tissue.
  • Mesenchymal cells are present in very small numbers in bone marrow, periosteum, skin and muscle.
  • a small piece of the tissue containing a small number of mesenchymal cells is preferably harvested from the patient's own body.
  • a piece of periosteal tissue harvested from the patient or donor is morsellised into small pieces.
  • tissue culture techniques well known to those skilled in the art, the mesenchymal cells are isolated and the number of cells expanded.
  • the mesenchymal cells are then seeded onto scaffolds. These scaffolds are preferably made of biodegradable materials to make the desired tissues.
  • NUS-12 It is also another object of the present invention to provide a method to enhance the growth and alignment of the fibrocytes and the extra cellular matrix during incubation of the tissue-engineered ligament.
  • Another object of the present invention is to provide tissue-engineered ligaments that will permanently anchor to a patient's bone.
  • Yet another object of the present invention is to provide tissue-engineered ligaments that will mature and resist physiological load across the joint.
  • Still another object of the present invention is to provide a method of making tissue-engineered ligaments.
  • the present invention comprises an apparatus and method for the reconstruction of a previously torn ligament using a tissue-engineered ligament.
  • the tissue-engineered ligament includes a scaffold of biocompatible material having at least one layer and forming a sheet.
  • the scaffold is placed in a cultured medium for seeding with fibrocyte forming cells.
  • the seeded scaffold is then placed in an incubator to increase the number of cells.
  • the seeded scaffold is then formed into a slender structure suitable for implantation.
  • the method of making a tissue-engineered ligament includes forming a scaffold of biocompatible material having at least one layer forming a sheet.
  • the scaffold sheet is seeded with fibrocyte forming cells.
  • the method further includes increasing the number of cells on the seeded scaffold and forming a slender structure suitable for implantation from the scaffold.
  • the starting material for a tissue-engineered ligament 10 is a sheet 15 of biocompatible material which is preferably bioabsorbable.
  • the sheet 15 may also be a porous structure.
  • the pores of the porous structure may be partially or fully interconnected across the thickness of the sheet.
  • the pore structure essentially forms perforations when fully and directly interconnected across the thickness of the sheet.
  • a sheet of woven fabric made of a biocompatible and preferably biodegradable material is an example of such a construct.
  • the sheet may contain slits 20 which extend completely through sheet 15.
  • a method of forming a tissue-engineered ligament includes placing the biocompatible sheet 15 in a cultured medium and seeding the sheet with fibrocyte forming cells 25 (Fig. 2) .
  • slender structure 35 such as a tissue-engineered ligament suitable for implantation into a patient.
  • slits 20 permit nutrients and the like to pass readily into the interior of slender structure 35.
  • slits 20 permit cells 25 to grow through sheet 15.
  • the presence of slits 20 provides greater flexibility to slender structure 35, whereby it may function more like a natural ligament.
  • the first embodiment of the invention shown in Figs. 1-4 provides rectangular sheet 15 of biocompatible material with multiple longitudinal slits 20 precut into the material. Slits 20 start and end at a prescribed distance from the edge of rectangular sheet 15, thereby leaving uncut margins 30 connecting the adjacent strips as shown in Fig. 2.
  • the whole construct is immersed in culture medium solution (not shown) and then seeded with fibrocyte forming cells such as mesenchymal stem cells or fibroblast cells.
  • sheet 15 is rolled into a slender structure 35, preferably with the strips oriented longitudinally and the uncut edges 30 forming the ends of the slender structure.
  • Slender structure 35 is then implanted into a patient to reconstruct a missing ligament.
  • Slender structure 35 may be further incubated prior to implantation to allow for further growth of fibrous tissue.
  • slender structure 35 can be implanted in a penultimate location in a patient's body such as the peritoneal cavity, muscle bed or any other soft tissue bed. This implantation allows further growth of fibrous tissue prior to implantation in a
  • NUS-12 functional location such as the knee joint for reconstruction of the anterior cruciate ligament.
  • slender structure 35 from sheet 15 is also possible. Examples include, but are not limited to, folding sheet 15 back and forth in an accordion style fold 40 with a width 45 corresponding to the desired width of tissue-engineered ligament 10 as shown in Figs. 5-8, or cutting sheet 15 into strips 50 corresponding to a desired width 55 of tissue- engineered ligament 10 and stacking one strip 50 on top of another, thereby forming stack 60 as shown in Figs. 9-12.
  • the fibrocyte forming cells can be harvested from a human donor.
  • fibrocyte forming cells are harvested from the patient's own body.
  • Fibrocyte forming cells which include mesenchymal stem cells or fibroblast cells, can be derived from a number of sources such as skin, bone marrow and periosteum.
  • the biocompatible material of sheet 15, which is preferably also a bioabsorbable material, can be, but is not limited to, one or more of the following: polyglycolic acid, polylactic acid, a mixture of PGA/PLA, chitin and collagen. This material may also
  • NUS-12 be porous.
  • Sheet 15 may comprise a uniform structure, a woven structure, a composite structure (e.g., a sheet with incorporated filaments, including aligned filaments such as for reinforcement), etc.
  • Flat sheets 15 of autograft or allograft tissue may also be used.
  • fascia lata One example is fascia lata.
  • the fascia lata tissue can be preprocessed to reduce reaction. Several methods, including freeze-drying, exist for preprocessing fascia lata.
  • the biocompatible material of sheet 15 may also be coated with collagen and other factors to promote adhesion of the fibrocyte forming cells 25.
  • the expansion of the number of cells can be promoted by the addition of growth factors to the biocompatible material of sheet 15 or the culture medium.
  • fibroblast growth factors such as interleukin may be added to the biocompatible material or the culture medium.
  • the strength of the cultured fibrous tissue is made stronger by orientating the growth of the fibrocytes and deposition of the collagen fibers in the longitudinal direction of the slender structure.
  • the fibrocytes are induced to orientate longitudinally by incorporating longitudinal microchannels 201 (Fig. 2A) , with a width and depth of the order 1 to 200 microns, on the surface of the biocompatible material of sheet 15.
  • the longitudinal microchannels 201 encourage the fibrocytes to cluster along the microchannels and, additionally, urges the fibrocyte cells to orient themselves parallel to the axis of the microchannels.
  • the application of cyclic loading to the biocompatible materials during incubation further enhances orientation of the cells and collagen fibers. Cyclic loading can also increase the growth of the fibrous tissue.
  • the cyclic loading can be applied to the biocompatible material in the rolled or unrolled configuration. It is to be noted that when the slender structure is loaded in longitudinal tension, the strips 105 will be taut and fluid will be forced out through the perforations or slits. When the tension is released or lessened, the slender structure tends to assume a slightly larger diameter, thus permitting fluid to flow into the slender structure through the slits or perforations. Such cyclic loading will create an environment of circulating fluid providing fresh nutrient fluid to the cells within the slender structure. Additionally, the cells suspended in the fluid for seeding are carried by the circulating fluid into the interior of the slender structure 35 thereby increasing the chance of cells attaching in the interior of the slender structure 35.
  • fibrocyte forming cells 25 on the biocompatible material of sheet 15 are cultured and, when a sufficient expansion of cells 25 is achieved, slits 20 are then made in the sheets as described above. Some of cells 25 will be damaged during the creation of slits 20. This damage is compensated for by the more efficient cell expansion on an uninterrupted (i.e., slit-less) flat surface during the incubation period.
  • the mesenchymal stem cells or fibroblast can be genetically altered to increase local production of desired growth factors. This can be done by viral transfection or by incorporating plasmid genes into the matrix of the biocompatible material.
  • the ligament 10 is ready for transplantation into a patient after incubating cells 25 attached to scaffold sheet 15. Incubation usually occurs for a period of time ranging from one to twelve weeks to allow substantial growth and expansion of cells 25.
  • two bone tunnels 65 are prepared during surgery on opposite sides of the joint using techniques well known in the art.
  • the ligament 10 is then fixed in the bone tunnels 65 with an interference screw 70 at both ends. This is similar to the fixation of hamstring ligaments with an interference screw in standard arthroscopic anterior cruciate reconstruction.
  • other surgical techniques well known in the art may be used to secure the tissue-engineered ligament 10 within the knee joint. Without harvesting autologous tissue, such as the patellar tendon or hamstring tendons, the complexity and time required for completing this surgery is greatly reduced. Also any morbidity associated with the harvesting of autologous tendon is eliminated.
  • tissue-engineered ligament 10 After successful implantation of tissue-engineered ligament 10, further growth of the fibroblast and fibrocytes will further anchor ligament 10 in the bone tunnels 65 by tissue ingrowth. Also repeated cyclic loading will encourage hypertrophy of tissue- engineering ligament 10. With time, the scaffold sheet 15 will be gradually absorbed and the entire load across the joint will eventually be carried by tissue- engineered ligament 10. Ligament 10 is a live tissue and will eventually mature into a more stable structure capable of resisting normal transient increases in physiologic load.
  • fixation can be enhanced by molding threads 75 into the ends 80 of slender structure 35 using a molding device 85 before implantation. Threaded ends 75 of tissue-engineered ligament 10 engage the thread of interference screw 70, as seen in Fig. 17. Advancement of interference screw 70 urges threaded end 75 of tissue-engineered ligament 10 against the wall of bone tunnel 65 and causes threads 75 of end 80 of tissue-engineered ligament 10 to embed into bone tunnel 65. This action further enhances fixation.
  • a rigid body (not shown) secured to the end of the tissue-engineered ligament may be provided for an interference screw to press against to provide fixation. The rigid body may contain threads corresponding to the screw. Alternatively, the rigid body may not have any threads.
  • the starting material is a thin rectangular sheet 15 of a biocompatible material including a biodegradable polymeric material, a natural material, and/or an allograft or autograft fascia lata material.
  • biodegradable polymeric materials include, but are not limited to, PGA, PLA, or mixture of PLA/PGA, etc.
  • natural materials include, but are not limited to chitin, chitosan, etc.
  • sections 85 at both ends of sheet 15 may be thicker than the rest of sheet 15.
  • sections 85 have a specific male pattern 90 on one side and matching female pattern 95 on the other.
  • the matching male and female patterns 90, 95 contact and inter-digitate when sheet 15 is rolled up. These inter-digitations at both ends of the sheet prevent sliding between adjacent layers of the rolled-up structure to maintain a stable, slender structure 35.
  • the slightly greater thickness at both ends helps to separate the layers to provide room for cellular growth between the layers.
  • a middle thinner portion 100 of sheet 10 has many tiny strips 105. These strips 105 are made with multiple longitudinal slits pre-cut into the material.
  • the slits start and end at a prescribed distance from the edge of the rectangular material to leave uncut margins 30 connecting the adjacent strips 105. These uncut margins 30 form the earlier mentioned thicker sections preferably having interlocking patterns.
  • Each of the tiny strips 105 has longitudinal microchannels 201. These microchannels each have a width and depth of the order of 1 to 200 microns.
  • the sheet may be hydrophilised and coated with collagen and growth factors such as TGF beta, IGF, etc.
  • Cell seeding may be performed using various methods consistent with the present invention. Several such methods will now be set forth by way of example but not limitation.
  • One method involves clamping sheet 15 at both ends 80 of the thicker, uncut sections and immersing the sheet in a culture medium 110.
  • Sheet 15 is initially held in tension and mesenchymal stem cells or fibroblasts are introduced into culture medium 110 and onto strips 105.
  • Cells 25 are allowed to attach to strips 105 and proliferate.
  • Nutrients and growth factors are added periodically as desired.
  • the mesenchymal stem cells or fibroblast can be genetically altered to increase local production of desired growth factors. This can be done by viral transfection or by incorporating plasmid genes into the matrix of the biocompatible material.
  • the mesenchymal stem cells are directed to differentiate into fibroblasts and subsequently to fibrocytes. Differentiation occurs under suitable conditions such as exposure to growth factors. Matrix materials are then produced by the fibrocytes.
  • a cyclic tensile load introduced through sheet 15 stimulates the fibrocytes to orientate and align in the direction of tension. Fibrous tissue forms on sheet 15 over a period of time and sheet 15 is then rolled up along strips 105.
  • the ends 80 of sheet 15 are crimped and then clamped in a cyclic loading machine as schematically depicted in Fig. 19. Further cyclic tensile load is applied to the structure immersed in culture medium 110 to promote growth, organization and maturation of cells 25. Tissue-engineered ligament 10 is then implanted into a patient when there is sufficient maturation.
  • Example II Another method for cell seeding involves clamping sheet 15 at both ends 80 of the patterned sections 90, 95 and immersing sheet 15 in culture medium solution 110.
  • Sheet 15 is initially held in tension and mesenchymal stem cells or fibroblasts are introduced into solution 110 and onto strips 105.
  • Cells 25 are allowed to attach to strips 105 and proliferate. Nutrients and growth factors are added periodically.
  • the mesenchymal stem cells or fibroblast can be genetically altered to increase local production of desired growth factors. This can be done by viral transfection or by incorporating plasmid genes into the matrix of the biocompatible material.
  • sheet 15 is rolled-up along the strips 105 to form a slender structure 35. Ends 80 are then crimped and then clamped. As the rolled-up slender structure 35 continues to be immersed in culture medium 110, a cyclic tensile load is applied to structure 35. The mesenchymal stem cells now differentiate into fibroblasts and secretion of matrix materials takes place. The fibroblasts form fibrocytes and these fibrocytes become aligned in the direction of tension. Over a period of time, the fibrocytes mature into fibrous tissue which forms over rolled-up slender structure 35.
  • Example III A third method involves forming a slender structure 35 by any of the methods previously described. Both ends 80 are crimped and clamped, and immersed in culture medium solution 110. The slender structure 35 is initially held in slight tension and
  • NUS-12 mesenchymal stem cells are introduced into the solution and onto the slender structure 35.
  • the cells attach to strips 105 and proliferate.
  • Nutrients and growth factors are added periodically as desired.
  • the mesenchymal stem cells or fibroblast can be genetically altered to increase local production of desired growth factors. This can be done by viral transfection or by incorporating plasmid genes into the matrix of the biocompatible material.
  • the mesenchymal stem cells are directed to differentiate into fibroblasts and subsequently to fibrocytes under suitable conditions, including exposure to growth factors. Matrix materials are then produced by the fibrocytes.
  • a cyclic tensile load is introduced to slender structure 35. As the ends of the slender structure 35 move towards and away from one another, the space between strips 105 opens and closes, thereby permitting cells and nutrients to flow between the strips, and thereby giving the cells the opportunity to attach to the interior of the structure. This loading also stimulates cells 25 further.
  • the fibrocytes orientate and align in the direction of tension. Over a period of time, the fibrocytes mature into fibrous tissue which forms over slender structure 35.
  • in-vitro tissue-engineered ligament is ready for implantation once ligamentous tissue has formed on slender structure 35.
  • Crimped ends 80 of in-vitro tissue-engineered ligament 10 are then inserted and secured into bone tunnels 65.
  • tissue-engineered ligament 10 is secured with interference screws 70.
  • other methods well known in the art may be used.
  • scaffold sheet 15 of tissue-engineered ligament 10 supports loading across the joint.
  • the load is gradually transferred to the newly formed tissue.
  • the entire load is transferred to the newly formed tissue of ligament 10.

Landscapes

  • Health & Medical Sciences (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Rehabilitation Therapy (AREA)
  • Rheumatology (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Materials For Medical Uses (AREA)

Abstract

La présente invention concerne un appareil et un procédé destiné à la reconstruction d'un ligament déchiré à l'aide d'un ligament (10) obtenu par génie tissulaire. Ce ligament (10) obtenu par génie tissulaire comprend un échafaudage de matériaux biocompatibles à une couche au moins et formant une feuille (15). Cet échafaudage est placé dans un milieu de culture en vue d'un ensemencement avec des cellules (25) formant des fibrocytes. L'échafaudage ensemencé est ensuite placé dans un incubateur de façon à accroître le nombre de cellules. Cet échafaudage ensemencé est ensuite formé en une structure (35) mince convenant pour l'implantation. Ce procédé de confection de ligament (10) par génie tissulaire consiste à former un échafaudage de matériaux biocompatibles présentant au moins une couche formant une feuille (15). Puis on ensemence cet échafaudage avec des cellules formant des fibrocytes. Ce procédé consiste aussi à accroître le nombre de cellules (25) sur l'échafaudage ensemencé et à former à partir de cet échafaudage une structure (35) mince convenant pour l'implantation.
PCT/US2000/031033 1999-11-12 2000-11-10 Ligament obtenu par genie tissulaire Ceased WO2001034065A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU15987/01A AU1598701A (en) 1999-11-12 2000-11-10 Tissue-engineered ligament

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US16533199P 1999-11-12 1999-11-12
US60/165,331 1999-11-12

Publications (1)

Publication Number Publication Date
WO2001034065A1 true WO2001034065A1 (fr) 2001-05-17

Family

ID=22598468

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2000/031033 Ceased WO2001034065A1 (fr) 1999-11-12 2000-11-10 Ligament obtenu par genie tissulaire

Country Status (2)

Country Link
AU (1) AU1598701A (fr)
WO (1) WO2001034065A1 (fr)

Cited By (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7824701B2 (en) 2002-10-18 2010-11-02 Ethicon, Inc. Biocompatible scaffold for ligament or tendon repair
US7875296B2 (en) 2003-11-26 2011-01-25 Depuy Mitek, Inc. Conformable tissue repair implant capable of injection delivery
US7901461B2 (en) 2003-12-05 2011-03-08 Ethicon, Inc. Viable tissue repair implants and methods of use
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
US8226715B2 (en) 2003-06-30 2012-07-24 Depuy Mitek, Inc. Scaffold for connective tissue repair
GB2502959A (en) * 2012-06-11 2013-12-18 Xiros Ltd Synthetic ligament assembly
US8691259B2 (en) 2000-12-21 2014-04-08 Depuy Mitek, Llc Reinforced foam implants with enhanced integrity for soft tissue repair and regeneration
US8895045B2 (en) 2003-03-07 2014-11-25 Depuy Mitek, Llc Method of preparation of bioabsorbable porous reinforced tissue implants and implants thereof
US9511171B2 (en) 2002-10-18 2016-12-06 Depuy Mitek, Llc Biocompatible scaffolds with tissue fragments
EP3204059A4 (fr) * 2014-10-10 2018-06-27 Orthocell Ltd Construction de collagène, et procédé de production de construction de collagène
US10583220B2 (en) 2003-08-11 2020-03-10 DePuy Synthes Products, Inc. Method and apparatus for resurfacing an articular surface
US11395865B2 (en) 2004-02-09 2022-07-26 DePuy Synthes Products, Inc. Scaffolds with viable tissue

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5078744A (en) * 1987-09-04 1992-01-07 Bio-Products, Inc. Method of using tendon/ligament substitutes composed of long, parallel, non-antigenic tendon/ligament fibers
US6077989A (en) * 1996-05-28 2000-06-20 Kandel; Rita Resorbable implant biomaterial made of condensed calcium phosphate particles
US6106556A (en) * 1994-12-02 2000-08-22 Omeros Medical Systems, Inc. Tendon and ligament repair system
US6123727A (en) * 1995-05-01 2000-09-26 Massachusetts Institute Of Technology Tissue engineered tendons and ligaments

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5078744A (en) * 1987-09-04 1992-01-07 Bio-Products, Inc. Method of using tendon/ligament substitutes composed of long, parallel, non-antigenic tendon/ligament fibers
US6106556A (en) * 1994-12-02 2000-08-22 Omeros Medical Systems, Inc. Tendon and ligament repair system
US6123727A (en) * 1995-05-01 2000-09-26 Massachusetts Institute Of Technology Tissue engineered tendons and ligaments
US6077989A (en) * 1996-05-28 2000-06-20 Kandel; Rita Resorbable implant biomaterial made of condensed calcium phosphate particles

Cited By (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8691259B2 (en) 2000-12-21 2014-04-08 Depuy Mitek, Llc Reinforced foam implants with enhanced integrity for soft tissue repair and regeneration
US7824701B2 (en) 2002-10-18 2010-11-02 Ethicon, Inc. Biocompatible scaffold for ligament or tendon repair
US10603408B2 (en) 2002-10-18 2020-03-31 DePuy Synthes Products, Inc. Biocompatible scaffolds with tissue fragments
US9511171B2 (en) 2002-10-18 2016-12-06 Depuy Mitek, Llc Biocompatible scaffolds with tissue fragments
US8895045B2 (en) 2003-03-07 2014-11-25 Depuy Mitek, Llc Method of preparation of bioabsorbable porous reinforced tissue implants and implants thereof
US8226715B2 (en) 2003-06-30 2012-07-24 Depuy Mitek, Inc. Scaffold for connective tissue repair
US9211362B2 (en) 2003-06-30 2015-12-15 Depuy Mitek, Llc Scaffold for connective tissue repair
US10583220B2 (en) 2003-08-11 2020-03-10 DePuy Synthes Products, Inc. Method and apparatus for resurfacing an articular surface
US7875296B2 (en) 2003-11-26 2011-01-25 Depuy Mitek, Inc. Conformable tissue repair implant capable of injection delivery
US7901461B2 (en) 2003-12-05 2011-03-08 Ethicon, Inc. Viable tissue repair implants and methods of use
US11395865B2 (en) 2004-02-09 2022-07-26 DePuy Synthes Products, Inc. Scaffolds with viable tissue
US8221780B2 (en) 2004-04-20 2012-07-17 Depuy Mitek, Inc. Nonwoven tissue scaffold
US8137686B2 (en) 2004-04-20 2012-03-20 Depuy Mitek, Inc. Nonwoven tissue scaffold
GB2502959A (en) * 2012-06-11 2013-12-18 Xiros Ltd Synthetic ligament assembly
US10524895B2 (en) 2014-10-10 2020-01-07 Orthocell Limited Collagen construct and method for producing the collagen construct
EP3204059A4 (fr) * 2014-10-10 2018-06-27 Orthocell Ltd Construction de collagène, et procédé de production de construction de collagène
US11517419B2 (en) 2014-10-10 2022-12-06 Orthocell Limited Collagen construct and method for producing the collagen construct

Also Published As

Publication number Publication date
AU1598701A (en) 2001-06-06

Similar Documents

Publication Publication Date Title
US6737053B1 (en) Tissue-engineered ligament
US7914579B2 (en) Tissue engineered tendons and ligaments
Lin et al. Ligament tissue engineering using synthetic biodegradable fiber scaffolds
JP4298193B2 (ja) 軟組織を人工プロテーゼに固定する装置
CA2314448C (fr) Dispositif de fixation de greffe, et methode
EP0808142B1 (fr) Matrice multicouches a base de collagene ou implant utilisable dans la reparation de lesions de cartilages
DE60311379T2 (de) Körperverträgliches Stützgerüst zur Wiederherstellung von Bändern oder Sehnen
US8226715B2 (en) Scaffold for connective tissue repair
DE69626560T2 (de) Laminare Knochengrundlage für das Knorpelwachstum
DE602004013257T2 (de) Implantate mit lebender Gewebe zur Reparatur von Gewebeschäden oder Gewebedefekten
DE69432865T2 (de) Implantierbare prothese, kit und vorrichtung zu deren herstellung
US20070185585A1 (en) Implant Scaffold Combined With Autologous Tissue, Allogenic Tissue, Cultured Tissue, or combinations Thereof
US10155068B2 (en) Connective tissue repair technology
WO1996024304A1 (fr) Procede de fixation de materiaux destines a reparer les defauts de cartilage
WO2001034065A1 (fr) Ligament obtenu par genie tissulaire
JP2003512896A (ja) 組織修復
CN113521389B (zh) 复合人工纤维元
WO2009029853A2 (fr) Structure d'échafaudage composite
EP1272127B1 (fr) Procedes de production de constructions de remplacement de ligaments
US20060159665A1 (en) Seed tear resistant scaffold
CA2285161A1 (fr) Tissu de ligament cultive in vitro et methode pour sa production
CN109475403B (zh) 用于旋转袖修复的工程化肌腱移植物
US20250170306A1 (en) Implantable synthetic structures comprising porous polymer
AU693323C (en) Multi-stage collagen-based template or implant for use in the repair of cartilage lesions
AU710212C (en) Fixation method for the attachment of wound repair materials to cartilage defects

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AU CA CN JP SG

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE TR

121 Ep: the epo has been informed by wipo that ep was designated in this application
DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
122 Ep: pct application non-entry in european phase