WO2022156648A1 - 一种耳软骨组织工程复合物及其用途 - Google Patents

一种耳软骨组织工程复合物及其用途 Download PDF

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WO2022156648A1
WO2022156648A1 PCT/CN2022/072409 CN2022072409W WO2022156648A1 WO 2022156648 A1 WO2022156648 A1 WO 2022156648A1 CN 2022072409 W CN2022072409 W CN 2022072409W WO 2022156648 A1 WO2022156648 A1 WO 2022156648A1
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ear
cartilage
chondrocytes
gel
ear cartilage
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PCT/CN2022/072409
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English (en)
French (fr)
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刘豫
周广东
慈政
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上海软馨生物科技有限公司
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Priority to US18/262,224 priority Critical patent/US20240091411A1/en
Publication of WO2022156648A1 publication Critical patent/WO2022156648A1/zh

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Definitions

  • the invention relates to the field of biomedical tissue engineering, in particular, to an ear cartilage tissue engineering compound and a preparation method thereof, and its application in repairing joint defects.
  • articular cartilage lesions In recent years, with the rapid development of economy and society, various types of articular cartilage lesions such as various sports injuries, accidental injuries and joint degenerative diseases have become more and more common. There is a huge clinical need for restoration.
  • Palliative treatments mainly include arthroscopic debridement and chondroplasty. These treatments can clean up the uneven cartilage surface of the joint surface and remove cartilage fragments to restore the smoothness of the joint surface. Such methods are less traumatic. It can relieve the symptoms of patients to a certain extent, but its curative effect is limited and cannot effectively relieve the development of arthritis. Restorative treatment includes microfracture treatment, osteochondral transplantation, etc.
  • the purpose of the present invention is to provide an auricular cartilage tissue engineering composite, a preparation method thereof, and use in repairing joint defects.
  • a first aspect of the present invention provides an ear cartilage tissue engineering composite, the composite comprising:
  • the complex comprises a complex formed after the auricular cartilage gel or ear perichondrium sheet particles are seeded on the carrier and cultured for chondrogenesis (in the complex, Auricular chondrocytes are loaded on the carrier and form a tighter unitary structure with the carrier).
  • the complex comprises a complex formed after the auricular cartilage gel or auricular perichondrium sheet particles are seeded on the carrier without chondrogenic culture.
  • the ear chondrocytes are derived from human or non-human mammals.
  • the ear chondrocytes are derived from autologous ear chondrocytes or allogeneic ear chondrocytes, preferably autologous ear chondrocytes.
  • the ear chondrocytes are obtained from the subject's autologous ear chondrocytes.
  • the subject is a human or a non-human mammal.
  • the subject has a joint defect.
  • the joint defect is an articular cartilage defect.
  • the joint defect is a knee joint defect, an elbow joint defect, a hip joint defect, an ankle joint defect, a wrist joint defect, a mandibular joint defect or a combination thereof.
  • the ear cartilage gel includes a cell population composed of chondrocytes and an extracellular matrix secreted by chondrocytes, wherein the extracellular matrix wraps the cell population, and the ear cartilage gels
  • the gel is in a gel state and the density of chondrocytes is at least 1.0 ⁇ 10 8 cells/ml or 1.0 ⁇ 10 8 cells/g.
  • the ear cartilage gel is prepared by gelation and culture of ear cartilage cells.
  • the gelation culture is an in vitro culture with a gelation medium.
  • the gelation medium contains the following components: high glucose DMEM medium containing 4-5wt% glucose, 10% FBS (v/v) and 100U/ml penicillin-streptomycin .
  • the adhesion rate of the ear cartilage gel is ⁇ 90%, preferably ⁇ 95%.
  • the concentration of chondrocytes is 1.0 ⁇ 10 8 cells/ml-10 ⁇ 10 8 cells/ml, preferably 1.5-5 ⁇ 10 8 cells/ml.
  • the ear cartilage gel is obtained by gelation culture for 2.5-5.5 days, preferably 3-5 days.
  • the ear chondrocytes are derived from human or non-human mammals.
  • the ear chondrocytes are derived from autologous ear chondrocytes or allogeneic ear chondrocytes, preferably autologous ear chondrocytes.
  • the ear chondrocytes are obtained from the subject's autologous ear chondrocytes.
  • the subject is a human or a non-human mammal.
  • the subject has a joint defect.
  • the joint defect is an articular cartilage defect.
  • the joint defect is a knee joint defect, an elbow joint defect, a hip joint defect, an ankle joint defect, a wrist joint defect, a mandibular joint defect or a combination thereof.
  • the ear perichondral sheet particles include a cell group composed of chondrocytes and an extracellular matrix secreted by chondrocytes, wherein the extracellular matrix wraps the cell group, and the ear cartilage
  • the granules are prepared by shredding flaky ear perichondrium sheets, wherein the density of ear chondrocytes is at least 1.0 ⁇ 10 8 cells/ml or 1.0 ⁇ 10 8 cells/g.
  • the concentration of chondrocytes is 1.0 ⁇ 10 8 cells/ml-10 ⁇ 10 8 cells/ml, preferably 1.5-5 ⁇ 10 8 cells/ml.
  • the ear perichondrium sheet is obtained by gelation culture for 6-30 days, preferably 7-20 days, and most preferably 10-15 days.
  • the gelation culture is an in vitro culture with a gelation medium.
  • the gelation medium contains the following components: high glucose DMEM medium containing 4-5wt% glucose, 10% FBS (v/v) and 100U/ml penicillin-streptomycin .
  • the thickness of the ear perichondrium sheet is 0.2-0.25 mm.
  • the average volume of the ear perichondrium sheet particles is 0.2 ⁇ l.
  • the surface area of the auricular perichondrial sheet particles is 0.05-10 mm 2 , preferably 1-5 mm 2 , and more preferably, the average area is 1 mm 2 .
  • the porous frame structure is made of a biodegradable material selected from the group consisting of PCL, PGA, allogeneic bone repair material, xenogeneic bone repair material, or demineralized bone matrix.
  • the framework structure can also be loaded with gelatin, collagen, silk fibroin, hydrogel or a combination thereof.
  • the frame structure is a PCL frame.
  • the frame structure is demineralized bone matrix.
  • the frame structure is an allogeneic bone repair material.
  • the allogeneic bone repair material is demineralized bone matrix.
  • the frame structure is a heterogeneous bone repair material.
  • the xenogeneic bone repair material is demineralized bone matrix.
  • the shape of the frame structure includes a cylinder, a rectangular parallelepiped or other specific shapes.
  • the auricular cartilage gel/auricular perichondrium sheet particle-frame structure complex can be converted into articular cartilage in a joint microenvironment.
  • the second aspect of the present invention provides a method for preparing the ear cartilage tissue engineering composite described in the first aspect of the present invention, which comprises the following steps: adding the ear cartilage gel or ear cartilage described in the first aspect of the present invention
  • the membrane particles are seeded on the porous frame structure and cultured in vitro to form chondrocytes, thereby obtaining the ear cartilage tissue engineering composite.
  • the ear cartilage gel is seeded on the porous frame structure by a direct filling method.
  • the ear perichondrium sheet particles are seeded on the porous frame structure by centrifugation.
  • no liquid is added to the centrifugation system of the centrifugation method, and repeated centrifugation is used to make the ear perichondrium sheet particles enter the frame structure.
  • the chondrogenic culture is in vitro culture using a chondrogenic medium.
  • the chondrogenic medium has the following components: high glucose DMEM medium, serum replacement, proline, vitamin C, transforming growth factor- ⁇ 1 (TGF- ⁇ 1), insulin-like growth Factor 1 (IGF-I) and dexamethasone.
  • the serum substitute is ITS premix, which contains insulin, transferrin, selenite, linoleic acid, bovine serum albumin, pyruvate, and ascorbic acid phosphate.
  • the chondrogenic culture time is 3-15 days, preferably 5-11 days.
  • the third aspect of the present invention provides a use of the ear cartilage tissue engineering composite described in the first aspect of the present invention for preparing a medical product for repairing joint defects.
  • the joint defect is an articular cartilage defect.
  • the joint defect is a knee joint defect, an elbow joint defect, a hip joint defect, an ankle joint defect, a wrist joint defect, a mandibular joint defect or a combination thereof.
  • the fourth aspect of the present invention provides a method for repairing joint defects, using the ear cartilage tissue engineering composite described in the first aspect of the present invention to be transplanted into the defective joint of a patient to be repaired.
  • the joint defect is an articular cartilage defect.
  • the joint defect is a knee joint defect, an elbow joint defect, a hip joint defect, an ankle joint defect, a wrist joint defect, a mandibular joint defect or a combination thereof.
  • Figure 1 shows the structural features of natural elastic cartilage and hyaline cartilage. The results of HE staining, Saf-O staining, COL-II staining and Elastin staining of the two cartilages were respectively shown.
  • Fig. 2 shows the results obtained after 6 months of implantation of the ear chondrocyte gel complex and the articular chondrocyte gel complex into the articular cartilage.
  • a and D are the whole articular cartilage, in which the regenerated cartilage tissue after implantation is outlined with a dashed circle, and is shown enlarged in B and E;
  • C and F are the section views of the regenerated cartilage tissue after implantation.
  • Figure 3 shows the effect of the articular cartilage microenvironment on the type of ectopic chondrogenesis of ear chondrocytes and articular chondrocytes.
  • the HE staining, Saf-O staining, COL-II staining and Elastin staining results of the two regenerated cartilages are shown respectively.
  • the bar in the graph is 150 ⁇ M.
  • Figure 4 shows a general schematic of the demineralized bone matrix framework.
  • the ruler in the figure is 1 cm.
  • Figure 5 shows an electron micrograph of a demineralized bone matrix framework with a bar of 1 mm.
  • Fig. 6 shows the schematic diagrams of ear cartilage gel and ear perichondrium sheets obtained by culturing ear chondrocytes for 3 days and 15 days.
  • A-C are ear cartilage gels cultured for 3 days
  • D-E are ear perichondrium sheets cultured for 15 days (D and E) and shredded ear perichondrium sheet particles (F).
  • Figure 7 shows a physical image of the ear cartilage gel-framework composite.
  • the ruler in the figure is 1 cm.
  • Figure 8 shows a physical image of the ear perichondrial sheet particle-framework complex.
  • the ruler in the figure is 1 cm.
  • Figure 9 shows a graph comparing the adhesion rates of seeded samples (cell suspension or cartilage gel) after culturing on demineralized bone matrix for 24 hours.
  • Figure 10 shows the comparison of the gel cartilage-demineralized bone complex (A) and the pure demineralized bone (B) transplanted on the defect site of goat knee.
  • an ear cartilage tissue engineering composite for the first time, which is an integrated ear cartilage gel/ear perichondrium sheet particle-frame structure Complex.
  • an ear cartilage tissue engineering composite for the first time, which is an integrated ear cartilage gel/ear perichondrium sheet particle-frame structure Complex.
  • a specific number of ear chondrocytes are seeded and/or spread on a flat or substantially flat culture surface, so that the seeded chondrocytes form a specific layered structure and are
  • the layered chondrocytes are cultured under suitable gelation culture conditions, and depending on the culture time, a novel gel-like ear cartilage or membrane-like ear cartilage can be formed.
  • the prepared ear cartilage tissue engineering composite can be transformed into articular cartilage at the defected joint after being transplanted into the defected joint, so as to realize the realization of articular cartilage. repair and reconstruction. On this basis, the present invention has been completed.
  • ear cartilage tissue engineering complex includes auricular cartilage gel-framework complexes and auris perichondrial sheet particle-framework complexes with or without in vitro chondrogenic culture as described herein , in the present invention, can be collectively referred to as ear cartilage tissue engineering composite.
  • seeding means seeding ear chondrocytes in a cell culture dish, it can also mean seeding auricular cartilage gel/auricular perichondrium sheet particles in a designated frame structure and making it evenly distributed, the art The meaning of “inoculation” as used will be understood by the skilled artisan according to the context.
  • the term “about” means that the value may vary by no more than 1% from the recited value.
  • the expression “about 100” includes all values between 99 and 101 and (eg, 99.1, 99.2, 99.3, 99.4, etc.).
  • the terms "containing” or “including (including)” can be open, semi-closed and closed. In other words, the term also includes “consisting essentially of,” or “consisting of.”
  • gel ear cartilage As used herein, “gel ear cartilage”, “ear cartilage gel”, “gel-like ear cartilage”, “gel-like ear cartilage”, “ear cartilage gel of the present invention” or “gel of the present invention” “Auricular cartilage” is used interchangeably and refers to the auricular cartilage (stem) cells of the present invention in a gel state, especially when a specific concentration of auris cartilage cells is seeded and/or spread on a flat or substantially flat culture surface such that The seeded ear chondrocytes form a layered structure, and the ear chondrocytes with the layered structure are cultured under suitable gelation culture conditions, thereby forming a gelatinous ear cartilage culture.
  • the gel ear cartilage of the present invention is a novel ear cartilage different from free ear chondrocytes, centrifuged ear chondrocytes and ear cartilage pellets.
  • the gel ear cartilage of the present invention can be regarded as a specific form of ear cartilage between free ear chondrocytes and dense ear cartilage mass.
  • the ear cartilage cells during the gelation culture process, not only contact and/or interact with the adjacent cells on the plane (X-Y plane), but also contact and/or interact with the cells above and/or below and/or on the side.
  • the gel ear cartilage of the present invention not only has close contact, but also has a certain viscosity and fluidity, so that the gel ear cartilage of the present invention is more suitable for seeding and loading on various carriers materials, especially porous carrier materials, to form complexes for the repair of ear cartilage.
  • the gelled ear cartilage of the present invention has a gel state on the one hand, and an unusually high cell density (usually at least 1.0 ⁇ 10 8 cells/ml or higher, such as 1.0 ⁇ 10 8 cells-10 ⁇ 10 cells) on the other hand. 8 /ml), therefore, it is especially suitable for preparing grafts for repairing various types of ear cartilage, or for ear cartilage transplantation or ear cartilage repair surgery.
  • the composite for repairing ear cartilage includes a composite formed by loading the gel ear cartilage of the present invention on a carrier material (especially a porous bioframe structure) without culturing the ear cartilage, and also includes the present invention
  • the gel auricular cartilage is loaded on a carrier material (especially a porous bioframe structure) and formed by culturing the auricular cartilage.
  • the composite suitable for transplantation into human or animal body is the ear cartilage tissue engineering composite of the present invention, that is, the gel ear cartilage of the present invention is loaded on a carrier material (especially a porous bioframe structure) and formed into a A complex formed by culture of ear cartilage.
  • a carrier material especially a porous bioframe structure
  • the gelled ear cartilage is formed by culturing in vitro for a period of time t1 under the gelation culture condition.
  • the t1 is 2.5-5.5 days, preferably 3-5 days.
  • a feature is layered seeding, that is, after a specific density of ear chondrocytes is seeded in a culture vessel, the seeded ear chondrocytes will form a multi-layered ear chondrocyte population (that is, with a layered structure) by, for example, deposition. ear chondrocytes).
  • auricular perichondrium sheet As used herein, "auricular perichondrium sheet", “patch-like ear cartilage”, or “auricular perichondrium sheet of the present invention” are used interchangeably, and all refer to auricular cartilage (stem) cells in a patch state of the present invention
  • a specific concentration of ear chondrocytes is seeded and/or spread on a flat or substantially flat culture surface, so that the seeded ear chondrocytes form a stacked structure, and the auris cartilage with a stacked structure is cultured under suitable culture conditions cells, thereby forming patch-like ear cartilage cultures.
  • the "ear perichondrium sheet" of the present invention is prepared by prolonging the gelation culture time on the basis of the preparation of the "ear cartilage gel” of the present invention. That is, in the present invention, ear chondrocytes seeded and/or plated on a flat or substantially flat culture surface are cultured in vitro for a period of time t2 under gelation culture conditions, thereby forming an ear perichondrium sheet.
  • the t2 is 6-30 days, preferably 7-20 days, and most preferably 10-15 days.
  • the ear perichondrial sheet of the present invention has, on the one hand, an unusually high cell density (usually at least 1.0 ⁇ 10 8 cells/ml or higher, such as 1.0 ⁇ 10 8 to 10 ⁇ 10 8 cells/ml), and on the other hand it has It has a thin thickness (only 0.2-0.25mm) and good toughness. It can be chopped into "ear perichondrial membrane particles" with an average volume of 0.2 ⁇ l, which can be filled in the porous frame structure by simple centrifugation. Therefore, it is especially suitable for preparation Grafts to repair various types of cartilage, or for cartilage transplantation or cartilage repair surgery.
  • the composite for repairing cartilage includes a composite formed by loading the ear perichondrial sheet particles of the present invention on a carrier material (especially a porous frame structure) without chondrogenic culture, and also includes the ear perichondrium of the present invention.
  • the perichondrial sheet particles are loaded on a carrier material (especially a porous framework) and the complexes formed by chondrogenic culture.
  • the composite suitable for transplantation into human or animal body is the ear cartilage tissue engineering composite of the present invention, that is, the ear perichondrial membrane sheet particles of the present invention are loaded on a carrier material (especially a porous frame structure) and passed through The complex formed by chondrogenic culture.
  • a carrier material especially a porous frame structure
  • specific concentration or “specific density” refers to seeding 1.0 x 10 7 -2.0 x 10 7 cells in a 3.5 cm dish (eg, one well in a six-well plate), preferably , for 1.5 x 10 7 cells.
  • the gelation culture conditions are as follows: inoculation of chondrocytes of a specific density and culture in a gelation medium containing 10% fetal bovine serum and 100U/ml Penicillin-streptomycin in high glucose (4-5 wt% glucose) DMEM medium.
  • chondrogenic culture refers to the use of chondrogenic medium to culture a porous framework inoculated with auricular cartilage gel or auricular perichondrial sheet particles, and ultimately form an integrated ear cartilage gel-framework composite
  • Auricular perichondrium sheet particle-frame structure composite namely the ear cartilage tissue engineering composite of the present invention, is used for transplantation in the cartilage defect of human or animal body.
  • Cartilage is cartilage tissue, which is composed of chondrocytes and intercellular substance.
  • the matrix in the cartilage is in a gel state and has great toughness.
  • Cartilage is a supportive connective tissue.
  • Cartilage does not contain blood vessels and lymphatic vessels, and nutrients penetrate into the intercellular substance from the blood vessels in the perichondrium, and then nourish bone cells.
  • Cartilage can be divided into three types, namely hyaline cartilage, elastic cartilage and fibrocartilage.
  • the matrix of hyaline cartilage is composed of collagen fibers, fibrils and surrounding amorphous matrix. There is a temporary scaffolding effect during the embryonic period, which is later replaced by bone.
  • hyaline cartilage is found mainly in the walls of the trachea and bronchi, the sternal ends of the ribs, and the surface of the bones (articular cartilage).
  • collagen fibers there are elastic fibers in the matrix of elastic cartilage.
  • This cartilage is more elastic and is mainly distributed in the auricle, the wall of the external auditory canal, the Eustachian tube, the epiglottis, and the larynx.
  • bundles of collagen fibers are arranged in parallel or crosswise, and are relatively tough. Distributed in the intervertebral disc, glenoid, joint disc and some tendons, ligaments, etc., to enhance the flexibility of movement and protection, support and other functions.
  • autologous ear chondrocytes taken from subjects with joint defects are cultured in vitro to prepare ear cartilage gel or ear perichondral sheet particles, and the ear cartilage
  • the cartilage gel or ear perichondrium sheet particles are seeded on the porous frame structure to prepare the ear cartilage gel-frame complex or the ear perichondrium sheet particle-frame complex, which is used for the repair of articular cartilage (hyaline cartilage) in joint defects.
  • HE staining hematoxylin-eosin staining (hematoxylin-eosin staining), referred to as HE staining, is one of the commonly used staining methods in paraffin section technology.
  • the hematoxylin staining solution is alkaline, which mainly makes the chromatin in the nucleus and the nucleic acid in the cytoplasm violet blue; eosin is an acidic dye, which mainly makes the components in the cytoplasm and the extracellular matrix red.
  • Saf-O staining also known as Safranin O staining, is a commonly used cartilage staining method.
  • the principle of Saf-O staining is that basophilic cartilage is combined with the basic dye Safranin O to give a red color;
  • Safranin O is a cationic dye that combines polyanions, which shows that cartilage tissue is based on cationic dyes and polysaccharide anion groups ( chondroitin sulfate or keratan sulfate) binding.
  • COL-II staining COL-II is type II collagen, which is a kind of macromolecular protein. Filamentous collagen fibers interweave with elastin and polysaccharide protein to form a network structure, which produces a certain mechanical strength. Type II collagen is mainly produced by chondrocytes and is mostly found in bones, joints, tendons and other tissues.
  • Elastin staining Elastin is elastin, the main component of elastic fibers. Two forms of elastin have been found: elastin I is present in the ligamentum niger, aorta and skin, and elastin II is available from cartilage. In the embodiment of the present invention, Elastin staining is used to reflect the expression of elastin in chondrocytes, so as to distinguish different types of chondrocytes, such as ear cartilage and articular cartilage.
  • cartilage transformation refers to the transformation between different types of cartilage, i.e. from one type of cartilage to another type of cartilage, or from one type of chondrocytes to another type of cartilage cell.
  • the ear chondrocyte cells (hyaline chondrocytes) in the ear cartilage tissue engineering graft formed by in vitro culture are transformed into articular chondrocytes (elastic chondrocytes) under the microenvironment of the joint tissue after being transplanted into the defected joint. chondrocytes) and eventually form articular cartilage.
  • MACI is the abbreviation of matrix-induced autologous chondrocyte implantation, which means "matrix-induced autologous chondrocyte transplantation", which is a technology of chondrocyte transplantation using tissue engineering technology.
  • MACI is the latest and best technology for the treatment of articular cartilage defects in the world.
  • ACI is the abbreviation of autologous chondrocyte implantation, which means “autologous chondrocyte transplantation”. It is one of the widely used tissue engineering techniques for the treatment of articular cartilage damage. After the advent of MACI, ACI was correspondingly called “traditional ACI” to distinguish it from MACI.
  • porous frame structure refers to a structure made of a biocompatible material that has a certain number of pores on its surface and inside to facilitate the attachment of auricular cartilage gel or auricular perichondrial sheet seeded thereon. vector.
  • the biocompatible material is preferably a biodegradable material.
  • Biodegradable materials refer to materials that can be decomposed in the body after being implanted into an animal.
  • the porous frame structure of the ear cartilage tissue engineering graft of the present invention is made of a biodegradable material selected from the group consisting of PCL, PGA, allogeneic bone repair material, xenogeneic bone repair material, demineralized bone matrix or a combination thereof , but not limited to the materials described above.
  • the allogeneic bone repair material and the xenogeneic bone repair material include demineralized bone matrix material.
  • the porous framework structure of the ear cartilage tissue engineering composite is demineralized bone matrix.
  • the demineralized bone matrix used in the preferred embodiment of the present invention has a thickness of 0.3-0.8 cm, preferably 0.4-0.6 cm, and most preferably 0.5 cm.
  • the decalcified bone matrix has a decalcification amount of 30% to 50%, the decalcification degree is suitable, the support function is good, and it is easy to be trimmed and cut into a suitable shape and size.
  • the pores of the demineralized bone matrix have a pore diameter of 400-800 ⁇ m, which is easy to fill with chondrocytes.
  • Demineralized bone matrix is a bone graft material made of allogeneic or xenogeneic bone that has been decalcified to reduce immunogenicity. Different degrees of decalcification correspond to different mechanical strengths. It has good biological properties, osteoinductivity, osteoconductivity and biodegradability, promotes new bone formation and bone tissue mineralization, thereby accelerating bone healing, and can be effectively repaired alone or in combination with autologous bone, other biomaterials, and growth factors It is an ideal scaffold material for bone tissue engineering. However, the pore size of general demineralized bone matrix is large, and the cell adhesion rate is extremely low when inoculated with chondrocyte suspension, which is not conducive to the construction of tissue engineering carriers.
  • the demineralized bone matrix in the present invention has a pore size of 400-800 ⁇ m and a porosity of 87.3% ⁇ 3.7%.
  • Polycaprolactone is a kind of fully biodegradable polymer material. It is made of ⁇ -caprolactone in metal organic compounds (such as tetraphenyl tin) as catalyst and dihydroxyl or trihydroxyl as initiator. It is formed by ring-opening polymerization and belongs to polymeric polyester. Its molecular weight and disproportionation degree vary with the type and amount of starting materials. Its appearance is white solid powder, non-toxic, insoluble in water, and easily soluble in various polar organic solvents.
  • PCL has good biocompatibility, good organic polymer compatibility, and good biodegradability, can be used as a cell growth support material, and is compatible with a variety of conventional plastics, 6-12 in natural environment month to be completely degraded.
  • PCL also has good shape memory temperature control properties, and is widely used in the production and processing of drug carriers, plasticizers, degradable plastics, nanofiber spinning, and plastic materials.
  • the ear cartilage gel/auricular perichondrium sheet particles of the present invention can be seeded on the PCL frame structure to form auricular cartilage gel-framework composite or auricular perichondrial sheet particle-framework composite, Used to repair articular cartilage.
  • Allogeneic bone is the most commonly used bone implant material in orthopaedics. It is mainly used to repair and fill bone defects, and play a role of fixation and support. Allogeneic bone is obtained from donated human bone tissue, with "syngeneic” indicating that it came from the human body, and "allogeneic” indicating that it was not from the patient's own body. After the donor is selected, it is usually obtained within 24 hours of death under sterile conditions and processed immediately. Preservation methods include fresh freezing and freeze drying. Fresh frozen bone can be stored for 1 year at -20°C; freeze-dried bone can be stored at room temperature for a long time after vacuum packaging, and has lower antigenicity. Compared with fresh frozen bone, the mechanical properties of freeze-dried bone were reduced by 50%, and sterilization by ethylene oxide or high-dose gamma irradiation further reduced the inductive properties of bone.
  • the ear cartilage gel/auricular perichondrium sheet particles of the present invention can be seeded on a frame structure (such as demineralized bone matrix) prepared from allogeneic bone to form auricular cartilage gel- Frame complex or ear perichondral membrane particle-frame complex for the repair of articular cartilage.
  • a frame structure such as demineralized bone matrix
  • Xenografts are bone repair materials derived from other species such as cattle and pigs. It is widely available and relatively inexpensive. However, xenogeneic bone is highly immunogenic, and it is easy to cause immune rejection after implantation in patients. In addition, the xenogeneic bone has no ability to induce the proliferation of mesenchymal stem cells, and has poor biological activity. It needs to be compounded with other repair materials or related cytokines to achieve the repair effect.
  • the ear cartilage gel/auricular perichondrium sheet particles of the present invention can be seeded on a frame structure (such as demineralized bone matrix) prepared from xenogeneic bone to form an ear cartilage gel-frame composite.
  • a frame structure such as demineralized bone matrix
  • Auricular perichondrial sheet particle-frame complex for the repair of articular cartilage.
  • the culture medium used in the present invention is a culture medium used in the present invention.
  • Chondrogenic medium high glucose DMEM medium, 1% 1 ⁇ ITS premix ((ITS universal culture mixture, containing insulin, transferrin, selenite, linoleic acid, bovine serum albumin, pyruvate, ascorbic acid phosphate) salt), 40 ⁇ g/ml proline, 10 ng/ml TGF- ⁇ 1, 100 ng/ml IGF-1, 40 ng/ml dexamethasone and 50 ⁇ g/ml vitamin C.
  • ITS premix (ITS universal culture mixture, containing insulin, transferrin, selenite, linoleic acid, bovine serum albumin, pyruvate, ascorbic acid phosphate) salt)
  • 40 ⁇ g/ml proline 10 ng/ml TGF- ⁇ 1, 100 ng/ml IGF-1, 40 ng/ml dexamethasone and 50 ⁇ g/ml vitamin C.
  • Gelling medium DMEM medium containing 4-5 wt% glucose, 10% FBS (v/v) and 100 U/ml penicillin.
  • the ear cartilage gel of the present invention when the ear cartilage gel of the present invention is seeded on a carrier material (especially a porous bioframe structure), the ear cartilage gel of the present invention has a certain adhesion rate. rate determination method.
  • the adhesion rate of the ear cartilage gel of the present invention is ⁇ 90%, preferably ⁇ 95%.
  • the adhesion rate in the present invention is defined as follows:
  • DNA quantification A1 of inoculated samples such as ear cartilage gel
  • detection of DNA quantification A2 after inoculation complexes such as ear cartilage gel-framework complexes
  • adhesion ratio A2/A1*100 % adhesion ratio
  • the method for measuring the adhesion rate comprises the following steps:
  • ear cartilage gel is more mature and has a certain fluidity.
  • ear cartilage which does not need to be taken from the joint site, and will not cause secondary damage to the patient's joint area, and ear cartilage cells will be transformed into articular cartilage cells in the joint environment
  • Most of the selected framework structures are natural materials or materials with neutral degradation products.
  • the degradation rate in vivo is moderate, the immune response of the body is low, and the biological safety is good.
  • the pore size of the frame structure material is large and the porosity is good, but the cell adhesion rate is extremely low when inoculated with chondrocyte suspension.
  • the use of a certain fluidity and relatively viscous cartilage gel-like tissue can effectively improve the adhesion rate.
  • the ear cartilage gel/auricular perichondrium sheet particle-frame structure composite can stably regenerate cartilage.
  • the ear cartilage gel/auricular cartilage membrane particle-frame structure composite can stabilize the regenerated cartilage and provide instant mechanical support, and the instant repair effect is good
  • cartilage tissue is divided into three types: elastic cartilage, hyaline cartilage, and fibrocartilage.
  • ear cartilage is elastic cartilage
  • articular cartilage is hyaline cartilage.
  • the biggest difference between the two is that the former expresses abundant elastin ( see picture 1).
  • the following experiments were carried out.
  • the skin, subcutaneous, superficial fascia, and deep fascia were cut in layers with large blood vessels and meningeal scissors, and the joint capsule and synovium were opened along the trailing edge of the primary band, taking care not to damage the primary band.
  • the trochlear site was fully exposed, a 5mm diameter trephine was used to create a circular defect of the full thickness of the cartilage, and different chondrocyte gel mixtures were injected into the defect. In vivo culture for six months.
  • ear cartilage gel-framework complexes were prepared.
  • the specific operation method is as follows:
  • the shape and size of the cartilage to be repaired can be determined according to auxiliary examinations such as MRI and CT in the early stage.
  • auxiliary examinations such as MRI and CT in the early stage.
  • the ear cartilage gel-frame structure complex is cut.
  • an ear perichondrial sheet particle-frame complex was prepared.
  • the specific operation method is as follows:
  • the shape and size of the cartilage to be repaired can be determined according to auxiliary examinations such as MRI and CT in the early stage.
  • a demineralized bone matrix framework is provided (as shown in Figure 4).
  • the gel cartilage preparation (prepared in Example 2, with a volume of about 0.25-0.35 ml) was inoculated into the above demineralized bone matrix framework, and the DNA content of the gel cartilage preparation was determined before inoculation.
  • the primary cultured chondrocytes were passaged 4 times at 37°C, 95% humidity, 5% carbon dioxide, added to cell culture medium to prepare a cell suspension, and the DNA content of the prepared chondrocyte suspension was determined.
  • the cell suspension was seeded in the demineralized bone matrix framework described above.
  • the seeded cartilage gel-demineralized bone matrix complex and chondrocyte suspension-decalcified bone matrix complex were left standing for 24 hours in an incubator at 37° C., 95% humidity, and 5% carbon dioxide.
  • the two complexes were sampled separately and their DNA content was determined.
  • the adhesion rate was calculated by the adhesion rate measurement method described in the specification.
  • the gel cartilage adhesion rate of the present invention is 92% ⁇ 2%, which is about 3 times that of the cell suspension.
  • a cartilage defect with a diameter of 7.5 mm was produced on the articular surface of the knee joint of experimental animals, and the ear cartilage gel-frame complex (gel cartilage-decalcified bone complex) prepared in Example 1 and a simple decalcified bone matrix were respectively used. Implanted in A defect and B defect.
  • the defect at A is smooth and solid, surrounded by a soft tissue membrane, which has a certain elasticity and has an excellent immediate repair effect.
  • the wound surface of the defect at B is rough and only has the function of physical support, which cannot be repaired.

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Abstract

一种耳软骨组织工程复合物及其制备方法。所述复合物包括含有耳软骨细胞的耳软骨凝胶或耳软骨膜片颗粒，和一多孔框架结构，将所述耳软骨凝胶或耳软骨膜片颗粒接种或负载于所述多孔框架结构，形成耳软骨凝胶/耳软骨膜片颗粒-框架结构复合物。所述耳软骨组织工程复合物用于关节软骨的修复与重建。

Description

一种耳软骨组织工程复合物及其用途 技术领域
本发明涉及生物医学组织工程领域，具体地，涉及一种耳软骨组织工程复合物和其制备方法，及其在修复关节缺损中的应用。
背景技术
近些年来，随着经济社会的快速发展，各类运动损伤、意外伤以及关节退行性病变等各种类型的关节软骨病变日趋多见，而软骨病变依靠患者自体能力是难以修复的，所以关节修复临床需求巨大。目前临床上对于关节软骨病变的治疗方法主要为姑息性治疗及修复性治疗。姑息性治疗主要包括关节镜下清理术和软骨成形术等，这类治疗方法可清理关节表面不平整的软骨面及移除软骨碎片等，以恢复关节面的光滑平整，此类方法创伤较小且可以一定程度缓解患者的症状，但其疗效有限，不能有效缓解关节炎的发展。修复性治疗包括微骨折治疗、骨软骨移植等，此类治疗虽使得局灶性关节软骨缺损得到一定的修复，但创伤较大易导致供区并发症。传统治疗方法总体而言疗效欠佳，自体移植缺乏供体，人工关节远期并发症难以避免。
随着组织工程学的进步，人们逐渐开始研究使用组织工程所构建的支架或组织来尝试修复软骨缺损。现有组织工程修复技术所构建的原位软骨细胞-材料复合物(自体软骨细胞移植ACI或基质诱导的自体软骨细胞移植MACI)虽已在临床治疗中逐渐开展，但仍有诸多劣势难以避免：1、细胞来源为关节软骨，在本已受损的关节部位获取细胞，难以避免的会增加原有关节的损伤。2、关节软骨细胞增殖能力有限，前期细胞-材料复合物构建周期长，患者需要等待较长时间。3、细胞-材料复合物强度低，远不及天然软骨的力学强度水平。
据此，关节修复亟需新方法。
发明内容
本发明的目的在于提供一种耳软骨组织工程复合物及其制备方法，以及在修复关节缺损中的用途。
本发明的第一方面，提供了一种耳软骨组织工程复合物，所述复合物包括：
(a)载体，所述载体包括多孔框架结构；和
(b)接种于或负载于所述载体的含有耳软骨细胞的耳软骨凝胶或耳软骨膜片颗粒。
在另一优选例中，所述的复合物包括将所述耳软骨凝胶或耳软骨膜片颗粒接种于所述载体并经成软骨培养后所形成的复合物(在所述复合物中，耳软骨细胞负 载于载体并与载体形成更为紧密的一体结构)。
在另一优选例中，所述的复合物包括将所述耳软骨凝胶或耳软骨膜片颗粒接种于所述载体但未经成软骨培养后所形成的复合物。
在另一优选例中，所述耳软骨细胞来自人类或非人类哺乳动物。
在另一优选例中，所述耳软骨细胞来源于自体耳软骨细胞或异体耳软骨细胞，优选地为自体耳软骨细胞。
在另一优选例中，所述耳软骨细胞取自受试者自体耳软骨细胞。
在另一优选例中，所述受试者为人类或非人类的哺乳动物。
在另一优选例中，所述受试者具有关节缺损。
在另一优选例中，所述关节缺损为关节软骨缺损。
在另一优选例中，所述关节缺损为膝关节缺损、肘关节缺损、髋关节缺损、踝关节缺损、腕关节缺损、下颌关节缺损或其组合。
在另一优选例中，所述的耳软骨凝胶包括软骨细胞构成的细胞群以及软骨细胞所分泌的细胞外基质，其中所述细胞外基质包裹所述的细胞群，并且所述耳软骨凝胶呈凝胶态，并且软骨细胞的密度为至少1.0×10 8个/ml或1.0×10 8个/g。
在另一优选例中，所述的耳软骨凝胶是用耳软骨细胞经凝胶化培养而制备的。
在另一优选例中，所述的凝胶化培养是用凝胶化培养基进行的体外培养。
在另一优选例中，所述的凝胶化培养基含有以下组分：含4-5wt％葡萄糖的高糖DMEM培养基、10％FBS(v/v)和100U/ml青-链霉素。
在另一优选例中，所述耳软骨凝胶的粘附率≥90％，较佳地≥95％。
在另一优选例中，所述耳软骨凝胶中，软骨细胞的浓度为1.0×10 8个/ml-10×10 8个/ml，较佳地1.5-5×10 8个/ml。
在另一优选例中，所述耳软骨凝胶是凝胶化培养2.5-5.5天，较佳地3-5天得到的。
在另一优选例中，所述耳软骨细胞来自人类或非人类哺乳动物。
在另一优选例中，所述耳软骨细胞来源于自体耳软骨细胞或异体耳软骨细胞，优选地为自体耳软骨细胞。
在另一优选例中，所述耳软骨细胞取自受试者自体耳软骨细胞。
在另一优选例中，所述受试者为人类或非人类的哺乳动物。
在另一优选例中，所述受试者具有关节缺损。
在另一优选例中，所述关节缺损为关节软骨缺损。
在另一优选例中，所述关节缺损为膝关节缺损、肘关节缺损、髋关节缺损、踝关节缺损、腕关节缺损、下颌关节缺损或其组合。
在另一优选例中，所述的耳软骨膜片颗粒包括软骨细胞构成的细胞群以及软 骨细胞所分泌的细胞外基质，其中所述细胞外基质包裹所述的细胞群，并且所述耳软骨颗粒是由薄片状的耳软骨膜片剪碎制得，其中耳软骨细胞的密度为至少1.0×10 8个/ml或1.0×10 8个/g。
在另一优选例中，所述耳软骨膜片中，软骨细胞的浓度为1.0×10 8个/ml-10×10 8个/ml，较佳地1.5-5×10 8个/ml。
在另一优选例中，所述耳软骨膜片是凝胶化培养6-30天，较佳地7-20天，最佳地10-15天得到的。
在另一优选例中，所述的凝胶化培养是用凝胶化培养基进行的体外培养。
在另一优选例中，所述的凝胶化培养基含有以下组分：含4-5wt％葡萄糖的高糖DMEM培养基、10％FBS(v/v)和100U/ml青-链霉素。
在另一优选例中，所述耳软骨膜片的厚度为0.2-0.25mm。
在另一优选例中，所述耳软骨膜片颗粒的平均体积为0.2μl。
在另一优选例中，所述耳软骨膜片颗粒的表面积为0.05-10mm 2，优选地，为1-5mm 2，更优选地，平均面积为1mm 2。
在另一优选例中，所述的多孔框架结构是由选自下组的生物可降解材料制成：PCL、PGA、同种异体骨修复材料、异种骨修复材料、或脱钙骨基质。
在另一优选例中，所述框架结构还可以负载有明胶、胶原、丝素、水凝胶或其组合。
在另一优选例中，所述框架结构为PCL框架。
在另一优选例中，所述框架结构为脱钙骨基质。
在另一优选例中，所述框架结构为同种异体骨修复材料。
在另一优选例中，所述同种异体骨修复材料为脱钙骨基质。
在另一优选例中，所述框架结构为异种骨修复材料。
在另一优选例中，所述异种骨修复材料为脱钙骨基质。
在另一优选例中，所述框架结构的形状包括圆柱体、长方体或其他特定形状。
在另一优选例中，所述耳软骨凝胶/耳软骨膜片颗粒-框架结构复合物在关节微环境下可转化为关节软骨。
本发明的第二方面，提供了一种制备本发明第一方面所述的耳软骨组织工程复合物的方法，其包括以下步骤：将本发明第一方面所述的耳软骨凝胶或耳软骨膜片颗粒接种于多孔框架结构，经体外成软骨培养，从而获得所述的耳软骨组织工程复合物。
在另一优选例中，将所述耳软骨凝胶采用直接填充的方法接种于多孔框架结构。
在另一优选例中，将所述耳软骨膜片颗粒采用离心的方法接种于多孔框架结 构。
在另一优选例中，所述离心的方法的离心体系中不加入液体，采用反复离心法使耳软骨膜片颗粒进入框架结构。
在另一优选例中，所述的成软骨培养是使用成软骨培养基进行的体外培养。
在另一优选例中，所述的成软骨培养基具有以下组分：高糖DMEM培养基、血清替代物、脯氨酸、维生素C、转化生长因子-β1(TGF-β1)、胰岛素样生长因子1(IGF-I)和地塞米松。
在另一优选例中，所述的血清替代物为ITS premix，其中包含胰岛素、转铁蛋白、亚硒酸、亚油酸、牛血清清蛋白、丙酮酸、抗坏血酸磷酸盐。
在另一优选例中，所述的成软骨培养时间为3-15天，优选地为5-11天。
本发明的第三方面，提供了一种本发明第一方面所述的耳软骨组织工程复合物的用途，用于制备用于修复关节缺损的医用产品。
在另一优选例中，所述关节缺损为关节软骨缺损。
在另一优选例中，所述关节缺损为膝关节缺损、肘关节缺损、髋关节缺损、踝关节缺损、腕关节缺损、下颌关节缺损或其组合。
本发明的第四方面，提供了一种修复关节缺损的方法，使用本发明第一方面所述的耳软骨组织工程复合物，移植入待修复患者的缺损关节内。
在另一优选例中，所述关节缺损为关节软骨缺损。
在另一优选例中，所述关节缺损为膝关节缺损、肘关节缺损、髋关节缺损、踝关节缺损、腕关节缺损、下颌关节缺损或其组合。
应理解，在本发明范围内中，本发明的上述各技术特征和在下文(如实施例)中具体描述的各技术特征之间都可以互相组合，从而构成新的或优选的技术方案。限于篇幅，在此不再一一累述。
附图说明
图1显示了天然弹性软骨和透明软骨的结构特点。分别显示了两种软骨的HE染色、Saf-O染色、COL-II染色和Elastin染色结果。
图2显示了耳软骨细胞凝胶复合物和关节软骨细胞凝胶复合物植入关节软骨处6个月后取材的结果。A和D为整体关节软骨，其中植入后的再生软骨组织用虚线圈出，并在B和E中进行放大展示；C和F为植入后再生软骨组织的切面图。
图3显示了关节软骨微环境对耳软骨细胞和关节软骨细胞异位成软骨类型的影响。分别显示了两种再生软骨的HE染色、Saf-O染色、COL-II染色和Elastin染色结果。图中的标尺(bar)为150μM。
图4显示了脱钙骨基质框架的大体示意图。图中标尺为1cm。
图5显示了脱钙骨基质框架的电镜图，图中的标尺(bar)为1mm。
图6显示了耳软骨细胞培养3天和15天所得到的耳软骨凝胶和耳软骨膜片示意图。其中A-C为3天培养的耳软骨凝胶，D-E为15天培养的耳软骨膜片(D和E)及剪碎形成的耳软骨膜片颗粒(F)。
图7显示了耳软骨凝胶-框架结构复合物实物图。图中标尺为1cm。
图8显示了耳软骨膜片颗粒-框架结构复合物实物图。图中标尺为1cm。
图9显示了接种样品(细胞悬液或软骨凝胶)于脱钙骨基质上培养24小时后的粘附率比较图。
图10显示了凝胶软骨-脱钙骨复合物(A)与单纯脱钙骨(B)移植到山羊膝关节缺损部位上的对比图。
具体实施方式
本发明人经过广泛而深入的研究，首次意外地发现并开发了一种耳软骨组织工程复合物，该耳软骨组织工程复合物是一体化的耳软骨凝胶/耳软骨膜片颗粒-框架结构复合物。实验证明，通过获取原代耳软骨进行扩增培养，将特定数量的耳软骨细胞接种于和/或铺于平坦或基本平坦的培养表面，使得被接种的软骨细胞形成特定的层叠结构，并在合适的凝胶化培养条件下培养所述层叠的软骨细胞，因培养时间不同，可形成一种新颖的凝胶状耳软骨或膜片状耳软骨。将制得的凝胶状软骨或膜片状软骨与多孔框架结构结合，制备得到的耳软骨组织工程复合物在移植进入缺损关节后，可以在缺损的关节处转化再生为关节软骨，实现关节软骨的修复重建。在此基础上，完成了本发明。
术语
除非另外定义，否则本文中所用的全部技术与科学术语均具有如本发明所属领域的普通技术人员通常理解的相同含义。
如本文所用，术语“耳软骨组织工程复合物”包括如本文所述的经体外成软骨培养或未经体外成软骨培养的耳软骨凝胶-框架复合物和耳软骨膜片颗粒-框架复合物，在本发明中，可统一称为耳软骨组织工程复合物。
如本文所用，术语“接种”意指将耳软骨细胞接种于细胞培养皿中，也可意指将耳软骨凝胶/耳软骨膜片颗粒接种于指定框架结构中并使其均匀分布，本领域技术人员根据上下文可以理解所用“接种”的含义。
如本文所用，在提到具体列举的数值中使用时，术语“约”意指该值可以从列举的值变动不多于1％。例如，如本文所用，表述“约100”包括99和101和之间的全部值(例如，99.1、99.2、99.3、99.4等)。
如本文所用，术语“含有”或“包括(包含)”可以是开放式、半封闭式和封 闭式的。换言之，所述术语也包括“基本上由…构成”、或“由…构成”。
耳软骨凝胶及其制备
如本文所用，“凝胶耳软骨”、“耳软骨凝胶”、“凝胶态耳软骨”、“凝胶状耳软骨”、“本发明的耳软骨凝胶”或“本发明的凝胶耳软骨”可互换使用，皆指本发明的呈凝胶状态的耳软骨(干)细胞，尤其是将特定浓度的耳软骨细胞接种于和/或铺于平坦或基本平坦的培养表面，使得被接种的耳软骨细胞形成层叠结构，并在合适的凝胶化培养条件下培养具有层叠结构的耳软骨细胞，从而形成凝胶状耳软骨培养物。
本发明的凝胶耳软骨是不同于游离的耳软骨细胞、离心沉淀的耳软骨细胞和耳软骨团块(pellet)的新型耳软骨。本发明的凝胶耳软骨可视为介于游离的耳软骨细胞和致密的耳软骨团块之间的一种特定形态的耳软骨。本发明凝胶耳软骨，由于在凝胶化培养过程中，耳软骨细胞不仅与平面(X-Y平面)上相邻细胞存在接触和/或相互作用，而且还与其上方和/或下方和/或侧上方或下方等多方向的相邻耳软骨细胞存在接触和/或相互作用，从而促使耳软骨细胞分泌和形成更多的细胞外基质，从而将将凝胶化培养的耳软骨细胞包裹于具有一定粘性的细胞外基质中，从而使得本发明的凝胶耳软骨既具有紧密联系，而具有一定的粘性和流动性，从而使得本发明的凝胶耳软骨更适合接种和负载于各种不同的载体材料(尤其是多孔的载体材料)上，从而形成用于修复耳软骨的复合物。
此外，本发明的凝胶耳软骨一方面具有凝胶状态，另一方面具有异乎寻常高的细胞密度(通常至少1.0×10 8个/ml或更高，如1.0×10 8个-10×10 8个/ml)，因此，特别适合制备修复各类耳软骨的移植物，或用于耳软骨移植或耳软骨修复手术。
在本发明中，修复耳软骨的复合物包括将本发明的凝胶耳软骨负载于载体材料(尤其是多孔生物框架结构)所形成的未经成耳软骨培养的复合物，也包括将本发明的凝胶耳软骨负载于载体材料(尤其是多孔生物框架结构)并经成耳软骨培养所形成的复合物。
在本发明中，适合用于移植于人体或动物体的复合物就是本发明耳软骨组织工程复合物，即将本发明的凝胶耳软骨负载于载体材料(尤其是多孔生物框架结构)并经成耳软骨培养所形成的复合物。
优选地，在本发明中，在凝胶化培养条件系下，体外培养一段时间t1，从而形成了凝胶耳软骨。优选地，所述的t1为2.5-5.5天，较佳地3-5天。
在本发明中，一个特征是层叠接种，即将特定密度的耳软骨细胞接种于培养容器后，接种的耳软骨细胞会通过例如沉积作用形成互相层叠的多层耳软骨细胞群(即具有层叠结构的耳软骨细胞群)。典型地，以培养皿(或培养容器)的培养面积计算，并设铺设单层细胞的汇合度为100％，则本发明的层叠接种的细胞数量S1是对于100％汇合度的细胞数量S0的n倍(即S1/S0＝n)，其中所述的n为1.5-20， 较佳地2-10，更佳地2.5-5。
耳软骨膜片及其制备
如本文所用，“耳软骨膜片”、“膜片状耳软骨”、或“本发明的耳软骨膜片”可互换使用，皆指本发明的呈膜片状态的耳软骨(干)细胞，尤其是将特定浓度的耳软骨细胞接种于和/或铺于平坦或基本平坦的培养表面，使得被接种的耳软骨细胞形成层叠结构，并在合适的培养条件下培养具有层叠结构的耳软骨细胞，从而形成膜片状耳软骨培养物。
本发明的“耳软骨膜片”是在本发明所述的“耳软骨凝胶”的制备基础上，通过延长凝胶化培养时间所制备得到的。即，在本发明中，在凝胶化培养条件下，将接种于和/或铺于平坦或基本平坦的培养表面的耳软骨细胞体外培养一段时间t2，从而形成了耳软骨膜片。优选地，所述的t2为6-30天，较佳地7-20天，最佳地10-15天。
本发明的耳软骨膜片一方面具有异乎寻常高的细胞密度(通常至少1.0×10 8个/ml或更高，如1.0×10 8个-10×10 8个/ml)，另一方面它的厚度薄(仅有0.2-0.25mm)并且韧性佳，可被剪碎为平均体积0.2μl的“耳软骨膜片颗粒”，通过简单离心的方式填充于多孔框架结构中，因此，特别适合制备修复各类软骨的移植物，或用于软骨移植或软骨修复手术。
在本发明中，修复软骨的复合物包括将本发明的耳软骨膜片颗粒负载于载体材料(尤其是多孔框架结构)所形成的未经成软骨培养的复合物，也包括将本发明的耳软骨膜片颗粒负载于载体材料(尤其是多孔框架结构)并经成软骨培养所形成的复合物。
在本发明中，适合用于移植于人体或动物体的复合物就是本发明的耳软骨组织工程复合物，即将本发明的耳软骨膜片颗粒负载于载体材料(尤其是多孔框架结构)并经成软骨培养所形成的复合物。
如本文所用，“特定浓度”或“特定密度”是指在3.5cm的培养皿(例如，六孔板中的一个孔)中，接种1.0×10 7-2.0×10 7个细胞，较佳地，为1.5×10 7个细胞。经凝胶化培养不同的时间，最终形成所含耳软骨细胞密度为1.0×10 8个-10×10 8个/ml的耳软骨凝胶或所含耳软骨细胞密度为1.0×10 8个-10×10 8个/ml的耳软骨膜片。
在另一优选例中，所述的凝胶化培养条件为：接种特定密度的软骨细胞，使用凝胶化培养基培养，所述凝胶化培养基为含10％胎牛血清及100U/ml青-链霉素的高糖(4-5wt％葡萄糖)DMEM培养基。
如本文所用，术语“成软骨培养”是指使用成软骨培养基培养接种了耳软骨凝胶或耳软骨膜片颗粒的多孔框架结构，最终使其形成一体化的耳软骨凝胶-框架 结构复合物或耳软骨膜片颗粒--框架结构复合物，即本发明的耳软骨组织工程复合物，用于移植于人体或动物体的软骨缺损处。
软骨和软骨细胞
软骨即软骨组织，由软骨细胞和细胞间质组成。软骨内的基质呈凝胶状态，具有较大韧性。软骨是以支持作用为主的结缔组织。软骨内不含血管和淋巴管，营养物由软骨膜内的血管中渗透到细胞间质中，再营养骨细胞。
根据细胞间质的不同可把软骨分为3种，即透明软骨、弹性软骨和纤维软骨。透明软骨的基质是由胶原纤维、原纤维和周围无定形的基质组成。在胚胎时期有临时支架作用，后来这种作用被骨代替。成人的透明软骨主要分布在气管和支气管壁中、肋骨的胸骨端和骨的表面(关节软骨)。弹性软骨的基质中除了胶原纤维还有弹性纤维，这种软骨弹性较大，主要分布在耳廓、外耳道壁、耳咽管和会厌、喉部等处。纤维软骨基质中有成束的胶原纤维平行或交叉排列，较坚韧。分布在椎间盘、关节盂、关节盘以及一些腱、韧带等处，以增强运动的灵活性和保护、支持等作用。
透明软骨和弹性软骨的最大区别在于前者(即透明软骨)表达丰富的弹性蛋白(Elastin)，两者的结构特点如图1所示。
在本发明的优选例中，将取自具有关节缺损的受试者的自体耳软骨细胞(弹性软骨)，通过体外培养，制备成耳软骨凝胶或耳软骨膜片颗粒，并将所述耳软骨凝胶或耳软骨膜片颗粒接种于多孔框架结构上，制备得到耳软骨凝胶-框架复合物或耳软骨膜片颗粒-框架复合物，并用于关节缺损的关节软骨(透明软骨)修复。
HE染色、Saf-O染色、COL-II染色和Elastin染色
HE染色：苏木精—伊红染色法(hematoxylin-eosin staining)，简称HE染色法，石蜡切片技术里常用的染色法之一。苏木精染液为碱性，主要使细胞核内的染色质与胞质内的核酸着紫蓝色；伊红为酸性染料，主要使细胞质和细胞外基质中的成分着红色。
Saf-O染色：又称番红O染色，是一种常用的软骨染色方法。Saf-O染色的原理在于嗜碱性的软骨与碱性染料番红O结合呈现红色；番红O是一种结合多阴离子的阳离子染料，其显示软骨组织是基于阳离子染料与多糖阴离子基团(硫酸软骨素或硫酸角质素)结合。
COL-II染色：COL-II即II型胶原蛋白，它是一种高分子蛋白质，丝状的胶原蛋白纤维与弹性蛋白及多糖蛋白相互交织形成网状结构，产生一定的机械强度。Ⅱ型胶原蛋白主要由软骨细胞产生，多存在于骨骼、关节、肌腱等组织。
Elastin染色：Elastin即弹性蛋白，是弹性纤维的主要成分。已发现弹性蛋白的两种形式：弹性蛋白I存在项韧带、主动脉和皮肤中，弹性蛋白II可从软骨中 得到。在本发明的实施例中，采用Elastin染色来反映软骨细胞中的弹性蛋白的表达情况，用以区别不同类型的软骨细胞，例如耳软骨和关节软骨。
软骨转化
如本文所用，术语“软骨转化”是指不同类型软骨之间的转化，即由一种类型的软骨转变为另一种类型的软骨，或一种类型的软骨细胞转变为另一种类型的软骨细胞。
在本发明中，经体外培养形成的耳软骨组织工程移植物中的耳软骨细胞细胞(透明软骨细胞)在被移植进入缺损的关节后，在关节组织微环境下，转化为关节软骨细胞(弹性软骨细胞)，并最终形成关节软骨。
MACI和ACI
MACI是matrix-induced autologous chondrocyte implantation的缩写，意为“基质诱导的自体软骨细胞移植”，是利用组织工程科技手段进行软骨细胞移植的技术。MACI是目前全世界最新、最好的治疗关节软骨缺损的技术。
ACI是autologous chondrocyte implantation的缩写，意为“自体软骨细胞移植”，是目前应用较广泛的治疗关节软骨损伤的组织工程技术之一。在MACI问世之后，ACI就被相应称为“传统ACI”，以便与MACI区别。
多孔框架结构
如本文所用，术语“多孔框架结构”是指其表面和内部具有一定数量的孔隙以便于使接种于其上的耳软骨凝胶或耳软骨膜片附着的由生物相容性材料制成的一载体。在本发明中，所述生物相容性材料优选生物可降解材料。
生物可降解材料是指在移植进入动物体内后，可以在体内被分解的材料。本发明的耳软骨组织工程移植物的多孔框架结构是由选自下组的生物可降解材料制成：PCL、PGA、同种异体骨修复材料、异种骨修复材料、脱钙骨基质或其组合，但不限于以上所述材料。其中同种异体骨修复材料和异种骨修复材料包括脱钙骨基质材料。在本发明的优选实施例中，所述耳软骨组织工程复合物的多孔框架结构为脱钙骨基质。
脱钙骨基质
本发明的优选实施例中使用的脱钙骨基质，其厚度为0.3～0.8cm，较佳地0.4～0.6cm，最佳地0.5cm。所述脱钙骨基质的脱钙量为30％～50％，脱钙程度合适，支持作用佳，并易于修整裁剪为合适的形状和大小。所述的脱钙骨基质的孔隙的孔径为400-800μm，易于填充软骨细胞。
脱钙骨基质(DBM)是由同种异体骨或异种骨经脱钙处理，能降低免疫原性的 骨移植材料。脱钙程度不同对应的机械强度也不同。具有良好的生物学特性、骨诱导性和骨传导性和生物降解性，促进新骨形成及骨组织矿化，进而加速骨愈合，可以单独或与自体骨、其它生物材料、生长因子联合有效修复骨损伤，是比较理想的骨组织工程支架材料。然而一般的脱钙骨基质的孔径较大，接种软骨细胞悬液时细胞黏附率极低，不利于组织工程载体的构建。
在另一优选例中，本发明中所述脱钙骨基质具有400-800μm孔径，87.3％±3.7％孔隙率。
PCL
聚己内酯(Polycaprolactone，PCL)是一种全生物降解高分子材料，是由ε-己内酯在金属有机化合物(如四苯基锡)做催化剂，二羟基或三羟基做引发剂条件下开环聚合而成，属于聚合型聚酯，其分子量与歧化度随起始物料的种类和用量不同而异。其外观为白色固体粉末，无毒，不溶于水，易溶于多种极性有机溶剂。PCL具有良好的生物相容性、良好的有机高聚物相容性，以及良好的生物降解性，可用作细胞生长支持材料，可与多种常规塑料互相兼容，自然环境下6-12个月即可完全降解。此外，PCL还具有良好的形状记忆温控性质，被广泛应用于药物载体、增塑剂、可降解塑料、纳米纤维纺丝、塑形材料的生产与加工领域。
在一优选实施例中,本发明所述的耳软骨凝胶/耳软骨膜片颗粒可以接种于PCL框架结构上，形成耳软骨凝胶-框架复合物或耳软骨膜片颗粒-框架复合物，用于修复关节软骨。
同种异体骨修复材料
同种异体骨是目前骨科最常用的骨植入材料，主要用于修复、填充骨缺损，起到固定和支撑作用。同种异体骨取自捐献的人体骨组织，“同种”表明它来自人体，“异体”表明它不是来自患者自体。供体选定后，通常在死亡24小时内，无菌条件下取得，并立即加工处理。保存方法包括新鲜冷冻和冷冻干燥两种。新鲜冷冻骨在-20℃条件下可储存1年；冷冻干燥骨经真空包装后可在室温长时间保存，且抗原性更低。与新鲜冷冻骨相比，冷冻干燥骨的力学性能会降低50％，而且环氧乙烷或大剂量γ射线照射消毒会进一步降低骨的诱导性能。
在一优选实施例中，本发明所述的耳软骨凝胶/耳软骨膜片颗粒可以接种于同种异体骨所制备成的框架结构上(例如脱钙骨基质)，形成耳软骨凝胶-框架复合物或耳软骨膜片颗粒-框架复合物，用于修复关节软骨。
异种骨修复材料
异种骨是来源于其他物种如牛、猪等的骨修复材料。其来源广泛且价格相对低廉。但异种骨的免疫原性强，植入患者体内后容易引起免疫排斥反应。此外， 异种骨无诱导间充质干细胞增殖的能力，生物活性差，需要复合其他修复材料或相关细胞因子才能达到修复效果。
在一优选实施例中，本发明所述的耳软骨凝胶/耳软骨膜片颗粒可以接种于异种骨所制备成的框架结构上(例如脱钙骨基质)，形成耳软骨凝胶-框架复合物或耳软骨膜片颗粒-框架复合物，用于修复关节软骨。
本发明所用的培养基
成软骨培养基：高糖DMEM培养基，1％1×ITS premix((ITS通用型培养混合剂，含胰岛素、转铁蛋白、亚硒酸、亚油酸、牛血清蛋白、丙酮酸、抗坏血酸磷酸盐)，40μg/ml脯氨酸，10ng/ml TGF-β1，100ng/ml IGF-1,40ng/ml地塞米松和50μg/ml维生素C。
凝胶化培养基：含4-5wt％葡萄糖，10％FBS(v/v)和100U/ml青链霉素的DMEM培养基。
黏附率
在本发明中，当将本发明的耳软骨凝胶接种于载体材料(尤其是多孔生物框架结构)时，本发明中的耳软骨凝胶具有一定的粘附率，通过本发明提供的粘附率测定方法确定。本发明的耳软骨凝胶的粘附率≥90％，较佳的，≥95％。
本发明中的粘附率如下定义：
检测所接种样品(例如耳软骨凝胶)的DNA定量A1；检测接种后复合物(例如耳软骨凝胶-框架复合物)培养24小时后的DNA定量A2；粘附率为A2/A1*100％。
所述黏附率的测定方法包括以下步骤：
取接种样品(例如耳软骨凝胶或耳软骨凝胶-框架复合物)，使用蛋白酶K消化，消化后的样品使用使用PicoGreen试剂盒(Invitrogen,Carlsbad,CA,USA)定量检测，使用荧光酶标仪测定520nm的吸光度，依据标准曲线公式计算出DNA含量。
本发明的主要优点包括：
(1)耳软骨凝胶较软骨细胞而言更加成熟，且具有一定的流动性。
(2)细胞来源为耳软骨，无需从关节部位取材，不会对患者关节区域二次损伤，且在关节环境中耳软骨细胞将转化为关节软骨细胞
(3)耳软骨扩增能力显著优于关节软骨，患者等待周期短。
(4)所选取的框架结构多为天然材料或降解产物为中性的材料，体内降解速率适中，机体免疫反应较低，生物安全性好。
(5)框架结构材料孔径较大，孔隙率较好，但接种软骨细胞悬液时细胞黏附率极低，使用具有一定流动性且较为粘稠的软骨凝胶样组织可有效提高黏附率。
(6)相较于其他组织工程修复方法，耳软骨凝胶/耳软骨膜片颗粒-框架结构复合物可稳定再生软骨。
(7)耳软骨凝胶/耳软骨膜片颗粒-框架结构复合物可稳定再生软骨可提供即时力学支撑，即时修复效果好
下面，通过具体的实施例对本发明做进一步说明。下面结合具体实施例，进一步阐述本发明。应理解，这些实施例仅用于说明本发明而不用于限制本发明的范围。下列实施例中未注明具体条件的实验方法，通常按照常规条件如Sambrook等人，分子克隆：实验室手册(New York：Cold Spring Harbor Laboratory Press，1989)中所述的条件，或按照制造厂商所建议的条件。除非另外说明，否则百分比和份数按重量计算。除非特别说明，否则本发明实施例中所用材料和试剂均为市售产品。
实施例1
不同类型软骨在天然关节软骨微环境中转归的研究
根据细胞外基质结构的不同，软骨组织分为弹性软骨、透明软骨、纤维软骨三种类型，其中耳软骨为弹性软骨，关节软骨为透明软骨，两者的最大区别在于前者表达丰富的弹性蛋白(见图1)。为研究不同类型软骨在天然关节软骨微环境中转归，遂进行如下实验。
(1)两种软骨细胞的取材分离与培养:山羊在麻醉完成后,无菌条件下切取一部分耳廓、同时刮取关节非负重区软骨。在无菌条件下分别将其剪成1mm×lmm大小,配置浓度为0.15％胶原酶；将软骨碎片加入配置好的胶原酶中消化8小时；8小时后将胶原酶溶液过滤离心得到耳软骨细胞，进行原代及传代培养，扩增到所需细胞量。
(2)Pluronic温敏凝胶的制备:将pluronic粉剂与H-DMEM按3:10的比例在室温下混合,然后在4℃冰箱里搅拌过夜,最后用高温消毒灭菌待用。
(3)细胞凝胶混合物的制备:分别以0.25％胰蛋白酶消化收集细胞,计数,取100×10 6的细胞与Pluronic温敏凝胶充分混合,静置在培养箱中30min,PBS清洗两遍弃上清。将细胞沉淀在冰盒中预冷，每100×10 6的细胞加入1ml凝胶充分混合后,用1ml注射器装20ml针头抽取细胞凝胶混合物,手握注射器让凝胶迅速呈半固态以保持细胞在凝胶中均匀分布的状态。
(4)将三种软骨细胞凝胶复合物回植入关节软骨微环境中:山羊在麻醉完成后。手术侧裸关节以下用无菌巾包裹好。伸屈膝关节以确定髌骨活动的位置,沿髌韧带后缘做一长约8-10cm纵向弧形切口,上方达髌骨上缘上约2-3cm,下端达腔骨结节下1cm,向内侧掀起皮肤,以大血管巧及脑膜剪分层剪开皮下、浅筋膜、深筋膜,沿酿初带后缘打开关节囊及滑膜,注意不要损伤初带。充分暴露滑车部位,用5mm直 径的环钻造成软骨全层的圆形缺损,分别将不同的软骨细胞凝胶混合物注入缺损中。体内培养六个月。
(5)取材结果：体内六个月取材发现，耳软骨细胞凝胶复合物和关节软骨细胞凝胶复合物在关节软骨微环境中均形成半透明样软骨组织(见图2A-C，D-F)，且均无弹性蛋白表达(见图3)。
实施例2
耳软骨凝胶-框架结构复合物制备
在本实施例中，制备耳软骨凝胶-框架复合物。具体操作方法如下：
(1)取受试者自体部分耳软骨组织，无菌切取2.5×2.5cm 2的耳软骨组织,使用无菌器械将软骨表面的黏膜及纤维组织剥离；
(2)将耳软骨组织剪为1.5×1.5mm 2大小软骨碎片；配置浓度为0.15％胶原酶；将软骨碎片加入配置好的胶原酶中消化8小时；
(3)8小时后将胶原酶溶液过滤离心得到耳软骨细胞，使用含有10％的FBS的高糖DMEM培养基进行原代及传代培养；
(4)扩增后收集细胞重悬，按照8×10 6/10ml至30×10 6/10ml/孔的细胞量接种于六孔板中，以凝胶化培养基(含4-5wt％葡萄糖，10％FBS(v/v)和100U/ml青链霉素的DMEM培养基)培养；
(5)在接种72小时(3天)后将六孔板中培养基吸去，可见六孔板底部的凝胶状耳软骨组织(图6A)，使用镊子将六孔板底部的凝胶状耳软骨聚集(图6B)，一个孔的凝胶软骨产量为0.1-0.2ml，收集至5ml注射器中；该凝胶软骨中，细胞密度为1.0×10 8个/ml-10×10 8个/ml，较佳地1.5-5×10 10个/ml。将其与0.15ml培养基混合，制成含耳软骨凝胶的制剂，如图6C所示；
(6)将耳软骨凝胶制剂(步骤(5)制备，体积约0.25-0.35ml)，接种于框架结构(脱钙骨基质框架(图4和图5)，具有约400-800μm孔径，约87.3％±3.7％孔隙率)中，于37℃、95％湿度、5％二氧化碳静置2小时；
(7)静置后加入成软骨培养基继续体外培养3-11天，形成耳软骨凝胶-框架结构复合物，如图7所示；
当用于关节缺损修复时，可根据前期MRI、CT等辅助检查确定所需修复的软骨形状、大小切割耳软骨凝胶-框架结构复合物。
实施例3
耳软骨膜片颗粒-框架结构复合物制备
在本实施例中，制备耳软骨膜片颗粒-框架复合物。具体操作方法如下：
(1)无菌切取2.5×2.5cm 2的耳软骨组织；使用无菌器械将软骨表面的黏膜及纤维组织剥离；
(2)将耳软骨组织剪为1.5×1.5mm 2大小软骨碎片；配置浓度为0.15％胶原酶；将软骨碎片加入配置好的胶原酶中消化8小时；
(3)8小时后将胶原酶溶液过滤离心得到耳软骨细胞，进行原代及传代培养；
(4)扩增后收集细胞重悬，按照8×10 6/10ml至30×10 6/10ml/孔的细胞量接种于六孔板中，以凝胶化培养基(含4-5wt％葡萄糖，10％FBS(v/v)和100U/ml青链霉素的DMEM培养基)培养；培养24小时或48小时后更换新鲜凝胶化培养基，继续体外培养至15天；
(6)吸去六孔板中的培养基，可见六孔板底部的耳软骨膜片组织(图6D)，其中耳软骨膜片组织中的细胞密度约为1.0×10 8个/ml-10×10 8个/ml；
使用镊子将耳软骨膜片夹起(图6E)，将其切割为1×1mm 2大小的耳软骨膜片颗粒后，收集至50ml离心管，如图6F所示；
(7)将需要接种的框架材料(脱钙骨基质框架(图4和图5))置于装有耳软骨膜片颗粒的离心管中，确保框架材料被完全浸没过；将装有框架材料及耳软骨膜片颗粒的离心管放于离心机中，600转/分钟，离心2分钟；
(8)将接种好的框架材料于37℃、95％湿度、5％二氧化碳静置一定时间；静置后加入成软骨培养基继续体外培养3-11天，形成耳软骨膜片颗粒-框架结构复合物，如图8所示；
当用于关节缺损修复时，可根据前期MRI、CT等辅助检查确定所需修复的软骨形状、大小切割耳耳软骨膜片颗粒-框架结构复合物。
对比例1
软骨细胞悬液与软骨凝胶的黏附率测定
提供一脱钙骨基质框架(如图4所示)。将凝胶软骨制剂(实施例2制备，体积约0.25-0.35ml)接种于上述脱钙骨基质框架中，接种前测定凝胶软骨制剂的DNA含量。
取原代培养的软骨细胞于37℃、95％湿度、5％二氧化碳传代4次，加入细胞培养基制备成细胞悬液，并测定制备的软骨细胞悬液的DNA含量。将细胞悬液接种于上述脱钙骨基质框架中。
将接种好的软骨凝胶-脱钙骨基质复合物与软骨细胞悬液-脱钙骨基质复合物于37℃、95％湿度、5％二氧化碳的培养箱中静置24小时。分别取样两种复合物，测定其DNA含量。
如图9所示，通过说明书中所述的粘附率测定方法计算粘附率。与细胞悬液相比，本发明的凝胶软骨粘附率为92％±2％，约为细胞悬液黏附率的3倍。
对比例2
修复关节软骨的动物移植实验
在实验动物膝关节的关节面制造直径7.5mm的软骨缺损，分别将实施例1中制备的耳软骨凝胶-框架复合物(凝胶软骨-脱钙骨复合体)与单纯脱钙骨基质基质植入A缺损处和B缺损处。
植入后立即观察动物体内软骨缺损的修复情况。
结果如图10所示：
A处缺损部位光滑，质实，周围包绕软组织膜，有一定弹性，具有优异的即时修复效果。
B处缺损部位创面粗糙，仅有物理支撑作用，无法起到即使修复作用。
在本发明提及的所有文献都在本申请中引用作为参考，就如同每一篇文献被单独引用作为参考那样。此外应理解，在阅读了本发明的上述讲授内容之后，本领域技术人员可以对本发明作各种改动或修改，这些等价形式同样落于本申请所附权利要求书所限定的范围。

Claims (15)

  1. 一种耳软骨组织工程复合物，其特征在于，所述复合物包括：
    (a)载体，所述载体包括多孔框架结构；和
    (b)接种于或负载于所述载体的含有耳软骨细胞的耳软骨凝胶或耳软骨膜片颗粒。
  2. 如权利要求1所述的复合物，其特征在于，所述的耳软骨凝胶包括软骨细胞构成的细胞群以及软骨细胞所分泌的细胞外基质，其中所述细胞外基质包裹所述的细胞群，并且所述耳软骨凝胶呈凝胶态，并且软骨细胞的密度为至少1.0×10 8个/ml或1.0×10 8个/g。
  3. 如权利要求2所述的复合物，其特征在于，所述耳软骨凝胶是凝胶化培养2.5-5.5天，较佳地3-5天得到的。
  4. 如权利要求2所述的复合物，其特征在于，所述耳软骨凝胶的粘附率≥90％，较佳地≥95％。
  5. 如权利要求1所述的复合物，其特征在于，所述耳软骨膜片颗粒包括软骨细胞构成的细胞群以及软骨细胞所分泌的细胞外基质，其中所述细胞外基质包裹所述的细胞群，并且所述耳软骨颗粒是由薄片状的耳软骨膜片剪碎制得，其中耳软骨细胞的密度为至少1.0×10 8个/ml或1.0×10 8个/g。
  6. 如权利要求5所述的复合物，其特征在于，所述耳软骨膜片是凝胶化培养6-30天，较佳地7-20天，最佳地10-15天得到的。
  7. 如权利要求3或权利要求6所述的复合物，其特征在于，所述的凝胶化培养是用凝胶化培养基进行的体外培养，所述的凝胶化培养基含有以下组分：含4-5wt％葡萄糖的高糖DMEM培养基、10％FBS(v/v)和100U/ml青-链霉素。
  8. 如权利要求1所述的复合物，其特征在于，所述耳软骨细胞来源于自体耳软骨细胞或异体耳软骨细胞，优选地为自体耳软骨细胞。
  9. 如权利要求1所述的复合物，其特征在于，所述多孔框架结构是由选自下组的生物可降解材料制成：PCL、PGA、同种异体骨修复材料、异种骨修复材料、或脱钙骨基质。
  10. 如权利要求1所述的复合物，其特征在于，所述耳软骨凝胶/耳软骨膜片颗粒-框架结构复合物在关节微环境下可转化为关节软骨。
  11. 一种制备如权利要求1所述的耳软骨组织工程复合物的方法，其包括以下步骤：将权利要求2所述的耳软骨凝胶或权利要求5所述的耳软骨膜片颗粒接种于多孔框架结构，经体外成软骨培养，从而获得所述的耳软骨组织工程复合物。
  12. 如权利要求11所述的方法，其特征在于，所述的成软骨培养是使用成软骨培养基进行的体外培养，所述的成软骨培养基具有以下组分：高糖DMEM培养基、血清替代物、脯氨酸、维生素C、转化生长因子-β1(TGF-β1)、胰岛素样 生长因子1(IGF-I)和地塞米松。
  13. 如权利要求11所述的方法，其特征在于，将所述耳软骨膜片颗粒采用离心的方法接种于多孔框架结构，并且所述离心的方法的离心体系中不加入液体，采用反复离心法使耳软骨膜片颗粒进入框架结构。
  14. 一种如权利要求1所述的耳软骨组织工程复合物的用途，其特征在于，用于制备用于修复关节缺损的医用产品。
  15. 一种修复关节缺损的方法，其特征在于，使用如权利要求1所述的耳软骨组织工程复合物，移植入待修复患者的缺损关节内。
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