Multicomponent Breast Implants

Abstract

The resorbable implants can be used to create volume and shape with regenerative tissue in the patient's breast. The implants are temporary, comprising a reinforcing matrix with a load-bearing absorbent macroporous network with an open cell structure, at least partially filled with one or more degradable hydrogels or water-soluble polymers that degrade progressively from the surface of the implant toward the core of the implant, and direct tissue ingrowth in the same direction. The hydrogels and water-soluble polymers help prevent fluid retention within the implant prior to tissue ingrowth. The macroporous network is absorbed after tissue ingrowth has occurred, and the load-bearing support is no longer necessary. The implants are particularly suitable for use in plastic surgery procedures, for example to regenerate or augment breast tissue after mastectomy or during mastopexy procedures, and may provide an alternative to the use of permanent breast implants in these procedures.

Description

[Technical field]

[0001] FIELD OF THEINVENTION

[0001] The present invention relates generally to a three-dimensional implant comprising a load-bearing, reinforced macroporous network at least partially filled with one or more hydrogels, one or more water-soluble polymers, or a combination thereof, suitable for replacing breast tissue. More specifically, the implant is preferably absorbent and comprises one or more hydrogels, water-soluble polymers, or a combination thereof, which degrade to allow tissue ingrowth and minimize fluid retention during tissue ingrowth. The implant is designed to replace or augment soft tissue volume upon implantation into the breast. [Background technology]

[0002] 2. Background of the Invention

[0002] Breast reconstruction after mastectomy has become an integral part of the surgical treatment of breast cancer, providing both aesthetic and psychosocial benefits to patients. Currently, nearly 65% ​​of breast reconstruction procedures in the United States use tissue expanders to create a pocket for a permanent breast implant in the first step of the procedure. In some patients, a pocket for a breast implant can be created without the use of tissue expanders. Once the pocket is created, the tissue expanders are removed and replaced with a permanent breast implant in the second step.

[0003]

[0003] Breast implants can also be used in breast augmentation and mastopexy procedures to increase breast size. In the latter procedure, a breast lift is combined with breast augmentation surgery. Most commonly, breast implants are placed in a pocket beneath the breast tissue, but occasionally they are implanted beneath the chest wall.

[0004]

[0004] Breast implants vary in size, shape, and surface texture. A wide variety of different sizes are available, allowing surgeons and patients to choose from a range of prominence, height, width, and overall volume. In terms of shape, there are rounded implants and anatomically shaped implants, and the surface of the implant may be smooth, micro-textured, or macro-textured. Generally, rounded implants have a smooth surface, while anatomically shaped implants have a dimpled micro- or macro-textured surface.

[0005]

[0005] An increasing number of patients are considering breast reconstruction and augmentation, but are hesitant to have permanent breast implants placed in their breasts. This is especially true for women who have had a mastectomy and are now considering breast reconstruction. Some of these patients do not want a foreign body permanently placed in their breasts and do not want to risk the complications that can occur with permanent breast implants. Complications include capsular contraction requiring revision surgery, implant rupture or contraction, development of anaplastic large cell lymphoma (ALCL), infection, and risk of implant movement causing breast asymmetry.

[0006]

[0006] WO 2016 / 038083 by Hutmacher discloses an implant for tissue reconstruction comprising a scaffold structure including a void system for the development of prevascularized connective tissue with void spaces for cell and / or tissue transplantation. See Abstract of Hutmacher.

[0007]

[0007] U.S. Patent Application Publication No. 2018 / 0206978 by Rehnke discloses an internal brassiere device made from a pleated scaffold that may be used for breast augmentation patients.

[0008]

[0008] WO 2018 / 078489 by Danze discloses a device to be implanted in the body of a subject to form an implant for replacing and / or increasing the volume of soft tissue, the device being of a type that includes a three-dimensional frame and defines an internal space within said frame. The frame is generally bioabsorbable and includes two side apertures that form a transverse passage for inserting a vascular pedicle; the device further includes at least two bioabsorbable textile sheets that can be stacked on top of each other within the internal space of the frame. See the abstract of Danze.

[0009]

[0009] U.S. Patent Application Publication No. 2020 / 0375726 by Limem discloses an implant formed from unit cells suitable for use in breast reconstruction.

[0010]

[0010] International Publication No. 2019 / 217335 by Toro Estrella discloses a biological scaffold structure comprising a plurality of connected unit cells, wherein each unit cell includes at least one opening connected to an interior volume.

[0011]

[0011] International Publication No. WO 2004 / 052768 by Morrison discloses a method for generating vascularized tissue using a vascular pedicle surrounded by a chamber and implanted into a donor, a vascularized tissue graft suitable for implantation, and a method for repairing a tissue defect using the vascularized tissue graft.

[0012]

[0012] International Publication No. 2019 / 043950 by Chhaya discloses an implant for soft tissue reconstruction comprising a plurality of unit cells arranged to form a reversibly compressible porous three-dimensional lattice structure having a bulk porosity of at least 50%.

[0013]

[0013] Zhou et al. “Tuning the mechanics of 3D-printed scaffolds by crystal lattice-like structural design for breast tissue engineering”, Biofabrication, 12 (2020) 015023 discloses an additively manufactured breast scaffold made using polyurethane. Summary of the Invention [Problem to be solved by the invention]

[0014]

[0014] Notwithstanding the above, there remains a need for improved breast implants that, upon implantation, can generate new breast tissue with a specific, desirable appearance. [Means for solving the problem]

[0015] Summary of the Invention

[0015] The breast implants described in this specification assist surgeons in reconstructing the breast, particularly after a mastectomy, improving the appearance of the breast, increasing the size of the breast, reconstructing lost or missing breast tissue, strengthening the tissue architecture of the breast, increasing the soft tissue volume of the breast, restoring the natural feel of the soft tissue of the breast, and delivering biological and synthetic materials to assist in the regeneration, repair, and reconstruction of breast tissue.

[0016]

[0016] The breast implant is configured with a surface, a core, a posterior section, and an anterior section opposite the posterior section. The posterior section of the implant is designed to be placed in the patient's breast, at or near the chest wall. The anterior section includes an anterior bottom for placement in the lower pole of the breast, an anterior top for placement in the upper pole of the breast, and an anterior middle region for placement under the patient's skin. In an embodiment, the breast implant has a longitudinal axis defined by an axis defined between the posterior and anterior sections of the implant.

[0017]

[0017] In an embodiment, the breast implant comprises a reinforcing matrix. In an embodiment, the reinforcing matrix comprises a load-bearing macroporous network with an open cell structure at least partially filled with one or more degradable hydrogels, water-soluble polymers, or combinations thereof. In an embodiment, the load-bearing macroporous network with an open cell structure has a compressive strength of at least 0.1 kgf at 30% strain. In an embodiment, the load-bearing macroporous network with an open cell structure has a compressive modulus of 0.1 kPa to 10 MPa at 5 to 15% strain. In an embodiment, the load-bearing macroporous network with an open cell structure has a loss modulus of 0.3 to 100 kPa. In an embodiment, the load-bearing macroporous network with an open cell structure comprises fibers, filaments, 3D printed wires, or struts. In an embodiment, the load-bearing macroporous network is absorbent. In an embodiment, the load-bearing macroporous network has a predictable degradation rate and a predictable strength retention in vivo. In an embodiment, the reinforcing matrix comprises a degradable load-bearing macroporous network. In embodiments, the one or more degradable hydrogels, water soluble polymers, or combinations thereof of the implant degrade before the resorbable load-bearing macroporous network.

[0018] In an embodiment, the breast implant provides a temporary scaffold for tissue ingrowth. After implantation, the implant is designed to allow connective tissue and blood vessels to gradually infiltrate and become fully incorporated into the breast. The breast implant minimizes fluid retention after implantation, which may occur when implants with large void volumes are implanted into the breast. Upon implantation, one or more degradable hydrogels, water-soluble polymers, or combinations thereof that fill at least a portion of the implant gradually degrade to allow tissue ingrowth without significant fluid retention in the void space of the implant. Fluid retention in the void space is minimized by the presence of one or more hydrogels, water-soluble polymers, or combinations thereof prior to tissue ingrowth. Preferably, the hydrogels, water-soluble polymers, or combinations thereof, the structure of the implant progressively degrade from the surface of the implant toward the core of the implant, and tissue ingrowth proceeds in the same direction from the surface of the implant toward the core. The degradation of the hydrogel, water soluble polymer, or combination thereof, preferably precedes the degradation of the load-bearing macroporous network, allowing the load-bearing macroporous network to provide a scaffold and structural support for tissue ingrowth once the hydrogel, water soluble polymer, or combination thereof has degraded.

[0019]

[0019] In an embodiment, the load-bearing macroporous network of the implant retains strength for a sufficient period of time to allow for the transfer of the shape of the breast from the implant to new tissue at the implantation site. The implant needs to maintain its shape for an extended period of time to manage the remodeling of the patient's tissue. The implant preferably supports the breast until support is transferred from the implant to the new tissue. Preferably, there is no loss of support for the shape of the breast or loss of support occurs minimally during this transition period. The shape of the breast implant is maintained for an extended period of time to direct tissue ingrowth into the implant and produce the desired breast shape.

[0020] In an embodiment, the breast implant comprises two or more degradable polymers, preferably selected from hydrogels and water-soluble polymers with different degradation rates. In an embodiment, the breast implant comprises at least one of a first hydrogel or a first water-soluble polymer, and at least one of a second hydrogel or a second water-soluble polymer, and the second hydrogel or the second water-soluble polymer surrounds the first hydrogel or the first water-soluble polymer. The degradation rate of the second hydrogel or the second water-soluble polymer is preferably faster than the degradation rate of the first hydrogel or the first water-soluble polymer. The degradation of the second hydrogel or the second water-soluble polymer exposes a portion of the load-bearing macroporous network, allowing tissue ingrowth into the volume of the implant previously occupied by the second hydrogel or the second water-soluble polymer. At the same time, the retention of fluid in the volume previously occupied by the first hydrogel or the first water-soluble polymer is prevented by the continued presence of the first hydrogel or the first water-soluble polymer in the implant. In embodiments, the first hydrogel or first water soluble polymer degrades following degradation of the second hydrogel or second water soluble polymer and allows tissue ingrowth into the volume previously occupied by the first hydrogel or first water soluble polymer. Complete degradation of both the hydrogel and / or the water soluble polymer allows tissue ingrowth into the entire load-bearing macroporous network and formation of new breast tissue throughout the implant. In embodiments, the load-bearing macroporous network is temporary and is completely degraded following tissue ingrowth such that structural support is no longer required.

[0021] In an embodiment, the breast implant comprises a load-bearing macroporous network, a first water-soluble polymer, and a second water-soluble polymer, where the second water-soluble polymer surrounds the first water-soluble polymer, and the degradation rate of the second water-soluble polymer is preferably faster than the degradation rate of the first water-soluble polymer.

[0022] In an embodiment, the breast implant comprises a load-bearing macroporous network, a hydrogel, and a water-soluble polymer. In an embodiment, the water-soluble polymer degrades faster than the hydrogel degrades, and the water-soluble polymer surrounds the hydrogel. In an embodiment, the hydrogel degrades faster than the water-soluble polymer degrades, and the hydrogel surrounds the water-soluble polymer.

[0023] In an embodiment, the breast implant comprises a load-bearing macroporous network and three hydrogels. Preferably, the three hydrogels have three different degradation rates. In an embodiment, the breast implant comprises a first, a second and a third hydrogel, the third hydrogel degrades the fastest, followed by the second hydrogel, and the first hydrogel degrades last. The breast implant is formed with a first hydrogel located at the core of the breast implant, surrounded by a second hydrogel that degrades faster than the first hydrogel. The second hydrogel is surrounded by a third hydrogel. The third hydrogel degrades faster than the second hydrogel. At the same time, the hydrogels create a degradation rate gradient, with degradation occurring progressively slower moving in the direction from the surface of the implant to its core. Preferably, the load-bearing macroporous network degrades after the three hydrogels have degraded. In an embodiment, one or more hydrogels in the implant degrade in less than 3 months and the load-bearing macroporous network degrades in 3-24 months. In an embodiment, the load-bearing macroporous network has a strength retention of 50% at 3 months. In an embodiment, the implant comprises three hydrogels, and the third (outermost) hydrogel degrades within 1 month, the second hydrogel degrades within 2 months, and the first (innermost) hydrogel degrades within 3 months. In an embodiment, the implant comprises three hydrogels, and the third (outermost) hydrogel degrades within 1 month, the second hydrogel degrades within 3 months, and the first (innermost) hydrogel degrades within 6 months. In an embodiment, the load-bearing macroporous network has a strength retention of 50% at 6 months.

[0024] In an embodiment, the breast implant comprises a macroporous load-bearing network and three water-soluble polymers. Preferably, the three water-soluble polymers have different degradation rates. In an embodiment, the breast implant comprises a first, a second and a third water-soluble polymer, where the third water-soluble polymer degrades the fastest, followed by the second water-soluble polymer, and the first water-soluble polymer degrades last. The breast implant is formed with a first water-soluble polymer located at the core of the breast implant surrounded by a second water-soluble polymer that degrades faster than the first water-soluble polymer. The second water-soluble polymer is surrounded by the third water-soluble polymer.

[0025] In an embodiment, the breast implant comprises a macroporous load-bearing network, a water-soluble polymer, and two hydrogels, or a macroporous load-bearing network, two water-soluble polymers, and one hydrogel. The slowest degrading water-soluble polymer or hydrogel is located in the core of the breast implant and is surrounded by a faster degrading second water-soluble polymer or hydrogel. The second water-soluble polymer or hydrogel is surrounded by the fastest degrading water-soluble polymer or hydrogel.

[0026] In an embodiment, the breast implant comprises a load-bearing macroporous network at least partially filled with a first hydrogel and a second hydrogel, or a first water-soluble polymer and a second water-soluble polymer, where the second hydrogel or the second water-soluble polymer at least partially surrounds the first hydrogel or the first water-soluble polymer, and where the second hydrogel or the second water-soluble polymer degrades faster than the first hydrogel or the first water-soluble polymer. In an embodiment, the second hydrogel or the second water-soluble polymer surrounds the first hydrogel or the first water-soluble polymer, except in a posterior region of the implant where the implant contacts the chest wall. In an embodiment, the hydrogel and the water-soluble polymer degrade before the macroporous network is completely degraded. In an embodiment, the breast implant further comprises a third hydrogel or a third water-soluble polymer, where the third hydrogel or the third water-soluble polymer at least partially surrounds the second hydrogel or the second water-soluble polymer, and the third hydrogel or the third water-soluble polymer degrades faster than the second hydrogel or the second water-soluble polymer. In an embodiment, the three hydrogels or the three water-soluble polymers degrade before the macroporous network is completely degraded. In an embodiment, the second hydrogel or the second water-soluble polymer surrounds the first hydrogel or the first water-soluble polymer, and the third hydrogel or the third water-soluble polymer surrounds the second hydrogel or the second water-soluble polymer, except in the posterior region of the implant where the implant contacts the chest wall.

[0027] In an embodiment, the breast implant comprises a reinforced macroporous network with a plurality of interconnected voids; and a first set of sacrificial void occupants adapted to temporarily occupy the first set of voids until tissue grows therein. In an embodiment, the breast implant further comprises a second set of voids arranged to surround the first set of voids, and a second set of sacrificial void occupants adapted to temporarily occupy the second set of voids until tissue grows therein, and the second set of void occupants are resorbable prior to the first set of void occupants. In an embodiment, the first set of sacrificial void occupants is a first hydrogel or a first water-soluble polymer. In an embodiment, the first and second sets of sacrificial void occupants and the macroporous network are fabricated and arranged together to form the implant by 3D printing. In an embodiment, the second set of sacrificial void occupants is a second hydrogel or a second water-soluble polymer. In embodiments, the second set of void occupants are absorbed before the first set of void occupants, and the macroporous network degrades after the first set of void occupants are degraded, hi embodiments, the first set of void occupants are absorbed within one year of implantation of the implant in the breast.

[0028]

[0028] In embodiments, the implant has a shape and size suitable for use in breast surgical procedures, such as breast augmentation, breast reconstruction, and mastopexy. In embodiments, the breast implant has a dome-like shape, a rounded shape, a teardrop shape, or an anatomical shape. In embodiments, the implant has a shape designed to provide a desired anatomical shape to the breast.

[0029] In an embodiment, the anterior bottom of the breast implant has a convex outer surface that is sized and shaped to contour and preferably approximate the anatomical features of the lower pole of the breast.

[0030] In an embodiment, the breast implant includes an opening for inserting tissue into the implant. In an embodiment, the opening is located in a posterior section of the implant. In an embodiment, the opening is located in a posterior section of the implant and has a longitudinal axis between the posterior and anterior sections of the implant. In an embodiment, the implant may have an opening that is a hollow core that defines a longitudinal axis between the posterior and anterior sections of the implant.

[0031] In embodiments, the implant may include two or more openings, allowing for multiple vascular pedicles, or other tissue masses, to be inserted into the implant.

[0032]

[0032] In an embodiment, the implant includes an outer shell surrounding the reinforcing matrix.

[0033] In embodiments, the implant includes one or more anchors, fasteners or tabs to fixate the implant to the breast.

[0034] In an embodiment, the implant is absorbable.

[0035] In an embodiment, the load-bearing macroporous network comprises one or more absorbent polymers. In an embodiment, the one or more absorbent polymers comprise or are made from one or more monomers selected from the group consisting of: glycolide, lactide, glycolic acid, lactic acid, 1,4-dioxanone, trimethylene carbonate, 3-hydroxybutyric acid, 3-hydroxybutyrate, 3-hydroxyhexanoate, 3-hydroxyoctanoate, 4-hydroxybutyric acid, 4-hydroxybutyrate, ε-caprolactone, 1,4-butanediol, 1,3-propanediol, ethylene glycol, glutaric acid, malic acid, malonic acid, oxalic acid, succinic acid, and adipic acid, or the polymer composition comprises poly-4-hydroxybutyrate or a copolymer thereof, or poly(butylene succinate) or a copolymer thereof.

[0036] In an embodiment, the weight average molecular weight of the absorbable polymer used to prepare the implant is from 50 to 1,000 kDa, more preferably from 90 to 600 kDa, and even more preferably from 200 to 450 kDa, relative to polystyrene as determined by GPC.

[0037]

[0037] In an embodiment, the load-bearing macroporous network with an open cell structure includes fibers, filaments, 3D printed wires, or struts having one or more of the following properties: tensile strength greater than 25 MPa, tensile modulus less than 300 MPa, elongation at break greater than 100%, melting temperature greater than 60°C, glass transition temperature less than 0°C, average diameter or width 10 μm to 5 mm, breaking load 0.1 to 200 N, and modulus of elasticity 0.05 to 1,000 MPa.

[0038] In an embodiment, the implant comprises a hydrogel that is degradable, and preferably two or more hydrogels with different degradation rates. In an embodiment, the hydrogel is a homopolymer, copolymer, or multipolymer interpenetrating polymer hydrogel. The hydrogel may be amorphous, semi-crystalline, or crystalline. The hydrogel may comprise chemical or physical crosslinks. The hydrogel may be photocrosslinked. The hydrogel may be nonionic, ionic, amphoteric, containing both acidic and basic groups, or zwitterionic, containing both anionic and cationic groups. The hydrogel may comprise natural polymers, such as proteins and polysaccharides. Examples include collagen, gelatin, fibrin, elastin, starch, cellulose, methylcellulose, carboxymethylcellulose, hydroxypropylmethylcellulose, hyaluronan, hyaluronic acid, alginate, chitosan, carrageenan, pectin, dextran, beta-glucan, gellan, welan, xanthan, and agarose. Hydrogels may comprise synthetic polymers. Examples include polyvinyl alcohol, poly(vinyl methyl ether), polyethylene glycol, polypropylene glycol, polyurethanes, polyphosphazenes, polypeptides, poly(N-isopropylacrylamide), poly(vinylpyrrolidone), polymethacrylic acid, and polyacrylates and copolymers.

[0039]

[0039] In an embodiment, the implant comprises a water-soluble polymer that is biodegradable. In an embodiment, the water-soluble polymer degrades in vivo to allow tissue ingrowth into the load-bearing macroporous network. In an embodiment, the water-soluble polymer is not a hydrogel. The water-soluble polymer may be a natural polymer, a biosynthetic polymer, or a synthetic polymer. Examples of water-soluble polymers include polyethylene glycol, polyvinylpyrrolidone, polyvinyl alcohol, polyacrylic acid, polyacrylamide, polyphosphate, polyoxazoline, divinyl ether-maleic anhydride, N-(2-hydroxypropyl) methacrylamide, and polyphosphazene.

[0040] In embodiments, the breast implant may include one or more of the following: autologous fat, lipoaspirate, injectable fat, cells, adipocytes, fibroblasts, stem cells, gels, hydrogels, hyaluronic acid, collagen, water soluble polymers, antimicrobial agents, antibiotics, bioactive agents, and diagnostic devices. After implantation, the implant is designed to be infested with connective tissue and blood vessels and successfully integrated into the breast. In embodiments, the implant may be an adipose tissue engineering scaffold.

[0041] In an embodiment, the compressive modulus of the breast implant is 0.1 kPa to 10 MPa, more preferably 0.3 kPa to 1 MPa, and even more preferably 3 kPa to 200 kPa at a strain of 5 to 15%. The compressive modulus allows the implant to be compressed and to recover from compression. The breast implant is engineered so that after implantation of the implant, the breast does not feel hard, but is soft to the touch and feels like a natural breast. In an embodiment, the breast implant allows the surgeon to restore or augment breast mass while maintaining or restoring breast feel.

[0042] In an embodiment, the loss modulus of the breast implant is between 0.1 kPa and 5 MPa, preferably between 0.3 kPa and 1 MPa, and even more preferably between 0.3 kPa and 100 kPa.

[0043] In an embodiment, the compression resilience of the breast implant is between 1 and 80%.

[0044] In an embodiment, the breast implant is adapted to recover at least 50%, more preferably 75%, and most preferably 90% or more after deformation / compression.

[0045]

[0045] In embodiments, the implant may be delivered to the breast in a minimally invasive manner.

[0046] In embodiments, the implant is compressible and can be delivered into the breast through a funnel, such as a Keller funnel. In embodiments, the implant can be delivered into the breast through a funnel with a neck diameter (narrowest part of the funnel) of 1-3 inches, and more preferably 1.5-2.5 inches. In embodiments, the implant can be delivered through a funnel with a neck diameter of 1-3 inches, and regain at least 70% of the implant's volume after delivery through the neck of the funnel into the breast. In embodiments, the compressive modulus of the implant allows for delivery of the implant through a funnel with a neck diameter of 1-3 inches, and the implant can regain at least 70% of the implant's volume after passing through the neck of the funnel.

[0047] In an embodiment, the endotoxin content of the implant is less than 20 endotoxin units per implant.

[0048]

[0048] In embodiments, the implant is a sterile implant. The implant may be sterilized by a range of techniques, including but not limited to ethylene oxide, electron beam, or gamma irradiation.

[0049] In an embodiment, a method is provided for producing an implant comprising a reinforcement matrix, wherein the reinforcement matrix comprises a load-bearing macroporous network with an open cell structure at least partially filled with one or more degradable hydrogels, one or more water-soluble polymers, or a combination of degradable hydrogels and water-soluble polymers, the implant comprising a posterior section for placement on the chest wall of a patient, an anterior section opposite the posterior section, the anterior section comprising an anterior bottom section for placement in the lower pole of the breast, an anterior top section for placement in the upper pole of the breast, and an anterior middle section for placement under the skin of a patient. The method provides for the production of a degradable load-bearing macroporous network with an open cell structure having a compressive strength of at least 0.1 kgf at 30% strain, a compressive modulus of 0.1 kPa to 10 MPa at 5 to 15% strain, or a loss modulus of 0.3 to 100 kPa. In an embodiment, the load-bearing macroporous network with an open cell structure is produced by 3D printing a polymer composition to form a network of filaments. In embodiments, the load-bearing macroporous network is formed by extrusion-based additive manufacturing, selective laser melting, fused deposition modeling, fused filament fabrication, melt extrusion deposition, printing of a polymer slurry or solution using a coagulation bath, and printing using a binding solution and polymer powder granules. In embodiments, the infill density of the 3D printed filament in the load-bearing macroporous network is between 1% and 60%, and more preferably between 5% and 25%.

[0050]

[0050] In an embodiment, a load-bearing macroporous network with an open cell structure is fabricated by 3D printing a polymer composition, wherein the polymer composition comprises a polymer selected from polymers or copolymers comprising or made from one or more of the following monomers: glycolide, lactide, glycolic acid, lactic acid, 1,4-dioxanone, trimethylene carbonate, 3-hydroxybutyric acid, 3-hydroxybutyrate, 4-hydroxybutyric acid, 4-hydroxybutyrate, ε-caprolactone, 1,4-butanediol, 1,3-propanediol, ethylene glycol, glutaric acid, malic acid, malonic acid, oxalic acid, succinic acid, and adipic acid, or the polymer composition comprises poly-4-hydroxybutyrate or a copolymer thereof, or poly(butylene succinate) or a copolymer thereof.

[0051] In an embodiment, a method for producing a load-bearing macroporous network of an implant includes forming, preferably by 3D printing, filaments of the network from a polymer having one or more of the following properties: (i) elongation at break >100%, (ii) elongation at break >200%, (iii) melting temperature >60°C, (iv) melting temperature >100°C, (v) glass transition temperature <0°C, (vi) glass transition temperature -55°C to 0°C, (vii) tensile modulus <300MPa, and (viii) tensile strength >25MPa. In a preferred embodiment, the load-bearing macroporous network of the implant is fabricated from P4HB, PBS, P4HB copolymer or PBS copolymer by 3D printing.

[0052]

[0052] In an embodiment, a 3D printer is used to manufacture an implant, where one print head of the 3D printer is used to print a load-bearing macroporous network with an open cell structure, and one or more print heads are used to print one or more hydrogels or one or more water-soluble polymers, so that an implant is formed that includes a macroporous network with an open cell structure that is at least partially filled with one or more hydrogels and / or one or more water-soluble polymers. In this way, an implant can be manufactured, where the degradation rate of each hydrogel, or each water-soluble polymer, incorporated in the implant, decreases as you move from the surface of the implant to the core of the implant.

[0053] In an embodiment, the load-bearing macroporous network with an open cell structure at least partially filled with one or more degradable hydrogels, one or more degradable water-soluble polymers, or a combination thereof is manufactured using a 3D printer with two or more print heads. In an embodiment, the implant is formed using a 3D printer with two print heads, where one print head is used to form the load-bearing macroporous network with an open cell structure, for example, using extrusion-based additive manufacturing, for example, fused deposition modeling or fused pellet deposition, and a second print head is used to print the hydrogel or water-soluble polymer, for example, using solution-based 3D printing, so that the hydrogel or water-soluble polymer at least partially fills the load-bearing macroporous network. In an embodiment, the implant is formed using a 3D printer with at least three print heads, where one print head is used to form a load-bearing macroporous network with an open cell structure, for example, using fused deposition modeling or fused pellet deposition, a second print head is used to print a first hydrogel or a first water-soluble polymer, for example, using solution-based 3D printing, so that it fills the core of the load-bearing macroporous network, and a third print head is used to print a second hydrogel or a second water-soluble polymer, for example, using solution-based 3D printing, so that it surrounds the first hydrogel or the first water-soluble polymer. The second hydrogel has a faster degradation rate than the first hydrogel. The second water-soluble polymer has a faster degradation rate than the first water-soluble polymer.

[0054] In an embodiment, a method for manufacturing an implant includes 3D printing an implant or 3D printing a load-bearing macroporous network and adding one or more of the following components: autologous fat, lipoaspirate, injectable fat, adipocytes, fibroblasts, stem cells, gels, hydrogels, hyaluronic acid, collagen, antimicrobials, antibiotics, bioactive agents, and diagnostic devices. In an embodiment, these components are added to the implant by coating, spraying, immersion, or injection.

[0055] In embodiments, the methods of manufacturing the load-bearing macroporous network of the implant include particle leaching, phase separation, foaming, lamination and perforation. In embodiments, the methods of manufacturing the load-bearing macroporous network of the implant include textile processes such as weaving, knitting, braiding, and nonwoven formation by, for example, meltblowing, electrospinning, staple fiber processing, solution spinning, centrifugal spinning, spunbonding, and dry spinning.

[0056] In an embodiment, the load-bearing macroporous network may be a 3D textile, a 3D braided fabric, or a 3D composite.

[0057]

[0057] In an embodiment, the implant has a predefined three-dimensional shape that can be implanted subcutaneously between the skin and the breast fullness or chest wall of the breast. The breast implant can be implanted in a subglandular, subpectoral, or subfascial location. The implant design allows the surgeon to easily control the volume ratio of the upper and lower poles of the breast, the degree of prominence of the breast from the chest wall, and the curvature of the upper and lower poles of the breast.

[0058] In embodiments, the implant serves to provide the surgeon with a means to deliver cells, stem cells, differentiated cells, adipocytes, muscle cells, platelets, tissues, stalks, vascular stalks, tissue mass, lipoaspirate, extracellular adipose matrix proteins, gels, hydrogels, hyaluronic acid, collagen, bioactive agents, drugs, antibiotics, and other substances to the implantation site. Preferably, the cells and tissues delivered by the implant or coated or injected into the implant are autologous. The implant may be used for autologous fat grafting. The implant may contain bioactive agents that stimulate cell ingrowth, such as growth factors, cell adhesion factors, cell differentiation factors, cell recruitment factors, cell receptors, cell binding factors, cell signaling molecules, such as cytokines, and molecules that promote cell migration, cell division, cell proliferation, and extracellular matrix deposition.

[0059] In embodiments, the implant may be implanted to replace and / or augment soft tissue volume or tissue mass, hi embodiments, the implant may further include a growth chamber for cells and tissue.

[0060]

[0060] In an embodiment, a method is provided for implanting an implant into a patient's breast. In an embodiment, the method of implanting the implant includes: (i) making at least one incision to access the patient's breast tissue; (ii) separating the skin and subcutaneous fascia from the breast mound of the breast; (iii) positioning the implant subglandularly, subpectorally, or subfascially; (iv) securing the implant to nearby tissue; and (v) closing the incision in the breast. In an embodiment, the method of implanting the implant into the breast further includes coating or adding one or more of the following components onto or to the implant, either before implanting the implant into the breast or after implanting the implant into the breast, at one or more occasions. The components are autologous fat, lipoaspirate, injectable fat, adipocytes, fibroblasts, stem cells, gels, hydrogels, hyaluronic acid or derivatives thereof, collagen, antimicrobial agents, antibiotics, and bioactive agents. In embodiments, the components are added to the implant by injecting, spraying, dipping or coating on or into the macroporous network of the implant, preferably by injecting the components. In embodiments, the implant is coated with autologous tissue from the patient before, during or after implantation, or any combination thereof. In embodiments, the implantation method includes implanting an implant with an opening sized to insert tissue into the implant, and inserting a tissue or pedicle, preferably a vascular pedicle, more preferably a vascular pedicle perforator, and even more preferably a pedicle from the pectoralis minor muscle, preferably comprising a perforator, into the opening of the implant during implantation of the implant. In embodiments, the implantation method includes detaching a pedicle, preferably comprising a perforator, from the pectoralis minor muscle of the patient, and inserting the pedicle into the opening of the implant sized to receive the pedicle. In embodiments, the surgeon may insert the pedicle or other tissue mass into the implant before or after implantation of the implant into the patient.Breast implants may be used in patients who: (i) have had a mastectomy, (ii) have had a breast lift and need augmentation, (iii) have had a breast reduction and need support and lift for the reduced breast, (iv) have had previous breast surgery with silicone or saline breast implants and desire to remove the silicone or saline implants and then reconstruct the breast to produce a youthful looking but fuller breast and larger size. Implants may also be used in patients who wish to restore the feel of natural breast tissue to the breast after removal of breast tissue. Implants may be used in combination with fat grafts to increase the breast's rise from the chest and to add volume to the breast.

[0061]

[0061] These advantages, as well as other objects and advantages of the present invention, will become apparent from the following detailed description taken in conjunction with the accompanying drawings. [Brief description of the drawings]

[0062] [Figure 1A]

[0062] Figure 1C is a cross-sectional view taken along line AA of a multi-component breast implant 1 shown in Figure 1C according to one embodiment of the present invention. The breast implant 1 is shown with a surface 2, a core 3, a posterior section 4 for placement on or near the patient's chest wall, an anterior section 5 opposite the posterior section, an anterior bottom section 6 for placement in the lower pole of the breast, an anterior top section 7 for placement in the upper pole of the breast, an anterior middle region 8 for placement under the patient's skin, and a load-bearing macroporous network 9 with an open cell structure. Also shown are the locations of a first hydrogel 10, a second hydrogel 11, and a third hydrogel 12 within the breast implant. [Figure 1B]

[0063] FIG. 1B is an isometric view of a multi-component breast implant 1 shown in FIG. 1A with a posterior section 4 for placement on or near the patient's chest wall, an anterior section 5 opposite the posterior section, an anterior bottom section 6 for placement in the lower pole of the breast, an anterior top section 7 for placement in the upper pole of the breast, an anterior middle region 8 for placement under the patient's skin, as well as locations of a first hydrogel 10, a second hydrogel 11, and a third hydrogel 12 within the implant. [Figure 1C]

[0064] FIG. 1 is a top view of a cross section along the midplane of a breast implant 1 according to one embodiment of the present invention. The breast implant is shown with a first hydrogel 10, a second hydrogel 11, and a third hydrogel 12. [Figure 1D]

[0065] 1B is a second isometric view of the multi-component breast implant 1 shown in FIG. 1A, comprising a posterior section 4 and an anterior section 5. FIG. [Figure 1E]

[0066] FIG. 1D is another cross-sectional view of the multi-component breast implant 1 shown in FIG. 1C, taken along line AA, with the first, second and third hydrogels (10, 11, 12) removed. [Figure 1F]

[0067] FIG. 1F is an enlarged view of a portion of the load-bearing macroporous network shown in FIG. 1E, according to an embodiment of the present invention. [Diagram 2]

[0068] FIG. 1 is a side view of a cross section of a 3D printer 20 printing a breast implant 21 supported on a 3D printing stage 22. The 3D printer is shown with a first print head 23, a second print head 24, and a third print head 25. A cross section of the implant 21 is shown with a load-bearing macroporous network 26 with an open cell structure filled with a first hydrogel 27 printed at the core of the implant and a second hydrogel 28 printed surrounding the first hydrogel. The first print head is shown with a reservoir 29 containing pellets 32 of a polymer composition for forming the load-bearing macroporous network, the second print head is shown with a reservoir 30 containing a pre-gel solution or slurry 33, and the third print head is shown with a reservoir 31 containing a gelling agent 34. [Diagram 3]

[0069] FIG. 1 is a side view of a cross section of a 3D printer 40 printing a breast implant 44 supported on a 3D printing stage 45. The 3D printer is shown with a first print head 46, a second print head 47, a third print head 48 and a fourth print head 49. The cross section of the implant is shown with a load-bearing network 41 comprising an open cell structure filled with a first hydrogel 42 printed at the core of the implant and a second hydrogel 43 printed surrounding the first hydrogel. A first print head 46 is shown with a reservoir 50 containing pellets 54 of a polymer composition for forming a load-bearing macroporous network, a second print head 47 is shown with a reservoir 51 filled with a first pre-gel solution or slurry 55, a third print head 48 is shown with a reservoir 52 filled with a second pre-gel solution or slurry 56, and a fourth print head 49 is shown with a reservoir 53 filled with a gelling agent 57. [Figure 4A]

[0070] FIG. 1 is a cross-sectional side view of a beaker 60 containing a load-bearing macroporous network 61 of a breast implant 62. [Figure 4B]

[0071] FIG. 1 is a cross-sectional side view of a breaker 60 on a shaker 63. The beaker contains a load-bearing macroporous network 61 of a breast implant 62 in a solution or slurry of pre-gel 64. Arrows 65 indicate the pre-gel 64 diffusing into the load-bearing macroporous network. [Figure 4C]

[0072] FIG. 1 is a cross-sectional side view of a beaker 60 containing a load-bearing macroporous network 61 of a breast implant 62. The breast implant is shown with a pre-gel 66 within the macroporous network illuminated with light 67 to cross-link the pre-gel and form a hydrogel within the macroporous network. [Figure 5A]

[0073] FIG. 13 is a front view of an implant according to another embodiment of the present invention. [Figure 5B]

[0074] FIG. 5B is a cross-sectional view of the implant shown in FIG. 5A taken along line AA. [Figure 5C]

[0075] FIG. 5B is an isometric view of the implant shown in FIG. 5A. [Figure 6A]

[0076] FIG. 13 is a front view of an implant according to another embodiment of the present invention. [Figure 6B]

[0077] 6B is a cross-sectional view of the implant shown in FIG. 6A taken along line BB. [Figure 6C]

[0078] FIG. 6B is an isometric view of the implant shown in FIG. 6A. [Figure 7A]

[0079] FIG. 13 is a front view of an implant having a cavity according to another embodiment of the present invention. [Figure 7B]

[0080] FIG. 7B is a cross-sectional view of the implant shown in FIG. 7A taken along line AA. [Figure 7C]

[0081] FIG. 7B is an isometric view of the implant shown in FIG. 7A. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0063] Detailed Description of the Invention

[0082] Before describing the present invention in detail, it should be understood that the present invention is not limited to the specific variations described herein, since various changes or modifications may be made to the described invention without departing from the spirit and scope of the present invention, and equivalents may be substituted. As will be apparent to those skilled in the art upon reading this disclosure, each of the individual embodiments described and illustrated herein has separate components and features that may be easily separated or combined with the features of any of the other several embodiments without departing from the scope or spirit of the present invention. Furthermore, many modifications may be made to adapt a particular situation, material, composition of matter, process, act(s) or step(s) of a process to one or more objectives, spirit or scope of the present invention. All such modifications are intended to be within the scope of what is claimed herein.

[0064]

[0083] The methods described herein may be carried out in any order of the described events, as well as in the order of the described events, that is logically possible. Moreover, when a range of values ​​is provided, it is understood that every intermediate value between the upper and lower limit of that range, and any other stated or intermediate value within that stated range, is also encompassed by the invention. It is also contemplated that any optional features of the described variations of the invention may be set forth and claimed independently, or in combination with any one or more of the features described herein.

[0065]

[0084] All existing subject matter discussed herein (e.g., publications, patents, patent applications, and hardware) is incorporated by reference in its entirety into this specification, unless the subject matter may conflict with the subject matter of the present invention, in which case what is presented herein takes precedence.

[0066]

[0085] Reference to a singular item includes the possibility of a plurality of the same items. More specifically, as used in this specification and the appended claims, the singular forms "a," "an," "said," and "the" include plural referents unless the context clearly dictates otherwise. It is further noted that the claims may be drafted to exclude any optional element. As such, this statement shall serve as an antecedent to the use of exclusive terminology such as "solely," "only," and the like, or the use of a "negative" limitation in connection with the recitation of the claimed elements.

[0067]

[0086] To aid in further understanding, the following definitions are set forth below: However, it should also be recognized that unless otherwise defined herein, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs.

[0068]

[0087] I. Definition

[0088] "Bioactive Agent" as generally used herein refers to a therapeutic, prophylactic or diagnostic agent, preferably an agent that promotes healing and regeneration of host tissue, and also an agent that prevents, inhibits or eliminates infection. "Agent" includes a single such agent and is intended to include a plurality of such.

[0069]

[0089] "Biocompatibility" as generally used herein means a biological response to a material or device that is appropriate for the device's intended use in the body. Any metabolic products of these materials should also be biocompatible.

[0070]

[0090] A "blend," as generally used herein, means a physical combination of different polymers, as opposed to a copolymer formed from two or more different monomers.

[0071]

[0091] As used herein, "compressive modulus" refers to the elastic modulus at a crosshead speed of 20 mm min -1 The modulus is measured in a universal testing machine at 100 psi. Samples are preloaded to apply a load and compressed to 5-15% strain. Ten clinically relevant cyclic loadings are repeated and the compressive modulus is calculated based on a quadratic cyclic loading to account for artifacts due to take-up and specimen alignment or placement. Compressive modulus may also be measured using ASTM standards ASTM D1621-16 or ASTM D695-15.

[0072]

[0092] "Compression resilience" as used herein is calculated as the work done during compression recovery divided by the work done during compression multiplied by 100.

[0073]

[0093] "Poly-4-hydroxybutyrate copolymer" as generally used herein means any polymer containing 4-hydroxybutyrate with one or more different hydroxy acid units. The copolymer may be isotopically enriched.

[0074]

[0094] "Copolymer of poly(butylene succinate)" as generally used herein means any polymer containing 1,4-butanediol and succinic acid units and one or more different diol or diacid units. The copolymer may include one or more of the following: branching agents, crosslinking agents, chain extenders, and reactive blending agents. The copolymer may be isotopically enriched.

[0075]

[0095] "Degradable," as generally used herein, and any of its variations or derivatives, including but not limited to "degrade," "decompose," and "degradation," refer to materials that are broken down in the body and the degradation products are excreted or eliminated from the body. The terms "absorbable," "resorbable," "degradable," and "erodible," with or without the prefix "bio," and their respective variations or derivatives, may be used interchangeably herein to describe materials that are broken down and gradually absorbed, excreted, or eliminated by the body, regardless of whether the degradation is primarily by hydrolysis or via metabolic processes, and include processes in which the material is dissolved or dispersed prior to absorption, excretion, or elimination by the body.

[0076]

[0096] "Endotoxin content" as generally used herein refers to the amount of endotoxin present in an implant or sample, and is determined using a limulus amebocyte lysate (LAL) assay.

[0077]

[0097] "Infill density" as used herein is the ratio, expressed as a percentage, of the volume occupied by the print within a porous implant divided by the total volume occupied by the print and interstitial spaces.

[0078]

[0098] "Molecular weight," as generally used herein, refers to weight average molecular weight (Mw) rather than number average molecular weight (Mn), unless otherwise specified, and is measured by GPC against polystyrene.

[0079]

[0099] "Poly(butylene succinate)" means a polymer comprising 1,4-butanediol units and succinic acid units. The polymer may comprise one or more of the following: branching agents, crosslinking agents, chain extenders, and reactive blending agents. The polymer may be isotopically enriched.

[0080]

[0100] "Poly(butylene succinate)s and copolymers" include polymers and copolymers made with one or more of the following: chain extenders, coupling agents, crosslinking agents, and branching agents.

[0081]

[0101] "Poly-4-hydroxybutyrate" as generally used herein means a homopolymer containing 4-hydroxybutyrate units. It may also be referred to herein as P4HB or TephaFLEX® biomaterial (manufactured by Tepha, Inc., Lexington, Mass.). The polymer may be isotopically enriched.

[0082]

[0102] "Subfascial" as used herein means below the connective tissue sheath of the pectoral muscle (the fascia externa) but above the pectoral muscle.

[0083]

[0103] "Soft tissue" as used herein means body tissue that is not hardened or calcified. Soft tissue excludes hard tissues such as bone and tooth enamel.

[0084]

[0104] "Strength retention" refers to the amount of time that a material maintains a particular mechanical property after implantation into a human or animal. For example, if the tensile strength of a resorbable fiber or strut decreases by half at 3 months from the time of implantation into an animal, the strength retention of the fiber or strut at 3 months would be 50%.

[0085]

[0105] "Subglandular" as used herein means below the breast tissue but above the pectoral muscle.

[0086]

[0106] "Subpectoral" as used herein means at least partially below the pectoral muscle.

[0087]

[0107] II. Materials for making implants

[0108] In embodiments, the implants can be used to reshape the breast, fill breast voids, lift the breast, and enlarge the breast. The implants are soft tissue implants, i.e., they can be used to regenerate, augment, repair, reinforce, and reconstruct soft tissue. The implants can eliminate the need to use permanent breast implants during mastectomy, mastopexy, and augmentation procedures. The implants are biocompatible, and are preferably replaced in vivo by the patient's tissue as the implant degrades. The implants are particularly suitable for breast augmentation, and in particular for soft tissue augmentation of the breast. The implants preferably have a compressive modulus that allows the implants to temporarily deform under compressive forces, recover their shape from compression when the forces are removed, and have a similar feel to breast tissue. Optionally, the implants can be coated or filled with autologous tissue, autologous fat, lipoaspirate, injectable fat, adipocytes, fibroblasts, and stem cells before, during, or after implantation.

[0088]

[0109] 7A-7C, the implant 300 may further include one or more openings 310 including one or more passageways or cavities 320 to allow for insertion of vascular pedicles or other tissue masses into the implant. In the embodiment shown in FIGS. 7A-7C, the cavities are cylindrical in shape and extend from the openings 310 in the posterior wall 312 toward the NAC of the breast. The macroporous network surrounding the open passageways includes hydrogels, water-soluble polymers, or combinations thereof. As described herein, multiple different types of hydrogels and / or water-soluble polymers may be disposed in localized or zonal layers (330, 340, 350) for timed absorption and to promote tissue ingrowth. It is understood that the cavities may have a wide variety of shapes and orientations, and are only limited as recited in any of the appended claims. Additionally, although only one cavity is shown in FIGS. 7A-7C, the implant may have multiple cavities. Preferably, the width or diameter of the cavity 320 ranges from 5 to 25 mm.

[0089]

[0110] A. Polymers and Hydrogels for Making Implants

[0111] In an embodiment, the implant comprises a matrix comprising a load-bearing macroporous network with an open cell structure and is at least partially filled with one or more hydrogels, one or more water-soluble polymers, or a combination of one or more hydrogels and one or more water-soluble polymers. In an embodiment, the implant comprises a first hydrogel or a first water-soluble polymer and a second hydrogel or a second water-soluble polymer, where the second hydrogel degrades faster than the first hydrogel or the first water-soluble polymer and surrounds the first hydrogel or the first water-soluble polymer within the implant, or the second water-soluble polymer surrounds the first hydrogel or the first water-soluble polymer and the second water-soluble polymer degrades faster than the first hydrogel or the first water-soluble polymer within the implant. In an embodiment, the implant further comprises a third hydrogel having a faster degradation rate than the second hydrogel or the second water-soluble polymer, or a third water-soluble polymer having a faster degradation rate than the second hydrogel or the second water-soluble polymer, and the third hydrogel or the third water-soluble polymer surrounds the second hydrogel or the second water-soluble polymer within the implant. In an embodiment, the implant comprises one or more hydrogels and / or one or more water-soluble polymers, comprising a faster degrading hydrogel or water-soluble polymer surrounding a slower degrading hydrogel or water-soluble polymer. The load-bearing macroporous network may optionally include other features, such as one or more openings or passages, such as one or more transverse passages.

[0090]

[0112] The load-bearing macroporous network of the implant may comprise a permanent material, such as a non-degradable thermoplastic polymer, such as polymers and copolymers of ethylene and propylene, such as ultra-high molecular weight polyethylene, ultra-high molecular weight polypropylene, nylon, polyesters, such as poly(ethylene terephthalate), poly(tetrafluoroethylene), polyurethane, poly(ether-urethane), poly(methyl methacrylate), polyether ether ketone, polyolefins, and poly(ethylene oxide). However, the load-bearing macroporous network of the implant preferably comprises a resorbable material, more preferably a thermoplastic or polymeric resorbable material, and even more preferably, the load-bearing macroporous network of the implant is fabricated entirely from a resorbable material.

[0091]

[0113] In a preferred embodiment, the load-bearing macroporous network of the implant is fabricated from one or more absorbable polymers or copolymers, preferably absorbable thermoplastic polymers and copolymers, and even more preferably absorbable thermoplastic polyesters. The load-bearing macroporous network of the implant may be, for example, a polymer, including, but not limited to, glycolic acid, glycolide, lactic acid, lactide, 1,4-dioxanone, trimethylene carbonate, 3-hydroxybutyric acid, 4-hydroxybutyrate, 3-hydroxyhexanoate, 3-hydroxyoctanoate, ε-caprolactone, such as polyglycolic acid, polylactic acid, polydioxanone, polycaprolactone, copolymers of glycolic acid and lactic acid, such as VICRYL® polymers, MAXON® and MONOCRYL® polymers, and polymers such as poly(lactide-co-caprolactone); poly(orthoesters); polyanhydrides; poly(phosphazenes); polyhydroxyalkanoates; synthetic or biologically produced polyesters; polycarbonates; tyrosine polycarbonates; polyamides (including synthetic and natural polyamides, polypeptides, and poly(amino acids)); polyesteramides; poly( alkylene alkylates; polyethers (e.g., polyethylene glycol, PEG, and polyethylene oxide, PEO); polyvinylpyrrolidone (PVP); polyurethanes; polyetheresters; polyacetals; polycyanoacrylates; poly(oxyethylene) / poly(oxypropylene) copolymers; polyacetals, polyketals; polyphosphates; (phosphorus-containing) polymers; polyphosphoesters; polyalkylene oxalates; polyalkylene succinates; poly(maleic acid); silk (including recombinant silk and silk derivatives and analogs); chitin; chitosan; modified chitosan; biocompatible polysaccharides; hydrophilic or water-soluble polymers, such as polyethylene glycol or polyvinylpyrrolidone (PVP), with blocks of other biocompatible or biodegradable polymers, for example, poly(lactide), poly(lactide-co-glycolide), or polycaprolactone and copolymers thereof, such as random and block copolymers thereof.

[0092]

[0114] Preferably, the load-bearing macroporous network of the implant is made from an absorbable polymer or copolymer that is substantially resorbed within a time frame of 1 to 24 months, more preferably 3 to 18 months, after implantation, and retains some residual strength for at least 2 weeks to 6 months, hi embodiments, the load-bearing macroporous network has at least 50% strength retention at 3 months.

[0093]

[0115] Blends of polymers and copolymers, preferably absorbable polymers, can be used to create the load-bearing macroporous network of the implant. Particularly preferred blends of absorbable polymers are made from polymers containing absorbable polymers, such as, but not limited to, glycolic acid, glycolide, lactic acid, lactide, 1,4-dioxanone, trimethylene carbonate, 3-hydroxybutyric acid, 4-hydroxybutyrate, ε-caprolactone, 1,4-butanediol, 1,3-propanediol, ethylene glycol, glutaric acid, malonic acid, oxalic acid, succinic acid, adipic acid, or copolymers thereof.

[0094]

[0116] In a particularly preferred embodiment, poly-4-hydroxybutyrate (Tepha's P4HB™ polymer, Lexington, MA) or its copolymers are used to fabricate the load-bearing macroporous network of the implant. The copolymers include P4HB with another hydroxy acid, such as 3-hydroxybutyrate, and P4HB with glycolic or lactic acid monomers. Poly-4-hydroxybutyrate is a strong, flexible thermoplastic polyester that is biocompatible and resorbable (Williams, et al. Poly-4-hydroxybutyrate (P4HB): a new generation of resorbable medical devices for tissue repair and regeneration, Biomed. Tech. 58(5):439-452(2013)). Upon implantation, P4HB hydrolyzes to its monomers, and the monomers are metabolized by the Krebs cycle to carbon dioxide and water. In a preferred embodiment, the weight average molecular weight Mw of the P4HB homopolymer and its copolymers is in the range of 50 kDa to 1,200 kDa (by GPC against polystyrene), more preferably 100 kDa to 600 kDa, and even more preferably 200 kDa to 450 kDa. Weight average molecular weights of polymers of 50 kDa or greater are preferred for processing and mechanical properties.

[0095]

[0117] In another preferred embodiment, the load-bearing macroporous network of the implant is made from a polymer that includes at least a diol and a diacid. In a particularly preferred embodiment, the polymer used to make the load-bearing macroporous network is poly(butylene succinate) (PBS), where the diol is 1,4-butanediol and the diacid is succinic acid. The poly(butylene succinate) polymer can be a copolymer with other diols, other diacids, or combinations thereof. For example, the polymer can be a poly(butylene succinate) copolymer that further includes one or more of the following: 1,3-propanediol, ethylene glycol, 1,5-pentanediol, glutaric acid, adipic acid, terephthalic acid, malonic acid, methylsuccinic acid, dimethylsuccinic acid, and oxalic acid. Examples of preferred copolymers are: poly(butylene succinate-co-adipate), poly(butylene succinate-co-terephthalate), poly(butylene succinate-co-butylene methyl succinate), poly(butylene succinate-co-butylene dimethyl succinate), poly(butylene succinate-co-ethylene succinate), and poly(butylene succinate-co-propylene succinate). The poly(butylene succinate) polymer or copolymer may further comprise one or more of the following: chain extenders, coupling agents, crosslinking agents, and branching agents. For example, poly(butylene succinate) or its copolymers may be branched or crosslinked by adding one or more of the following agents or agents: malic acid, trimethylolpropane, glycerol, trimesic acid, citric acid, glycerol propoxylate, and tartaric acid. A particularly preferred agent or agent for branching or crosslinking poly(butylene succinate) polymers or its copolymers is a hydroxycarboxylic acid unit. Preferably, the hydroxycarboxylic acid unit has two carboxyl groups and one hydroxyl group, two hydroxyl groups and one carboxyl group, three carboxyl groups and one hydroxyl group, or two hydroxyl groups and two carboxyl groups.In a preferred embodiment, the load-bearing macroporous network of the implant is made of poly(butylene succinate) with malic acid as a branching or crosslinking agent. This polymer may be called poly(butylene succinate) crosslinked with malic acid, succinic acid-1,4-butanediol-malic acid copolyester, or poly(1,4-butylene glycol-co-succinic acid) crosslinked with malic acid. It should be understood that references to malic acid and other crosslinking agents, coupling agents, branching agents, and chain extenders include polymers made with these agents or agents, where the agents or agents have undergone further reactions during processing. For example, the agents or agents may be dehydrated during polymerization. Thus, poly(butylene succinate)-malic acid copolymer refers to a copolymer made from succinic acid, 1,4-butanediol, and malic acid. In another preferred embodiment, malic acid may be used as a branching or crosslinking agent to make copolymers of poly(butylene succinate) and adipate, which may be referred to as poly[(butylene succinate)-co-adipate] crosslinked with malic acid. As used herein, "poly(butylene succinate) and copolymers" includes polymers and copolymers made with one or more of the following: chain extenders, coupling agents, crosslinkers, and branching agents. In certain particularly preferred embodiments, poly(butylene succinate) and copolymers thereof comprise at least 70% by weight, more preferably 80% by weight, and even more preferably 90% by weight succinic acid and 1,4-butanediol units. Polymers comprising a diacid and a diol, such as poly(butylene succinate) and its copolymers and others described herein, preferably have a weight average molecular weight (Mw) based on gel permeation chromatography (GPC) versus polystyrene standards of 10,000 to 400,000, more preferably 50,000 to 300,000, and even more preferably 100,000 to 200,000. In certain particularly preferred embodiments, the weight average molecular weight of the polymers and copolymers is 50,000 to 300,000, and more preferably 75,000 to 300,000.In a preferred embodiment, the poly(butylene succinate) or copolymers thereof used to fabricate the load-bearing macroporous network have the following properties: density 1.23-1.26 g / cm. 3 It has one or more or all of a glass transition temperature of -31°C to -35°C, a melting point of 113°C to 117°C, a melt flow rate (MFR) of 2 to 10g / 10 minutes at 190°C / 2.16kgf, and a tensile strength of 30 to 60MPa.

[0096]

[0118] In another embodiment, the polymers and copolymers described herein used to create the load-bearing macroporous network of the implant, including P4HB and its copolymers, and PBS and its copolymers, include polymers and copolymers enriched with known isotopes of hydrogen, carbon and / or oxygen. 1 H (protium), 2 H (Deuterium) and 3 It has three naturally occurring isotopes, including H (tritium), the most common of which is: 1 The isotope content of a polymer or copolymer can be, for example, enriched so that the polymer or copolymer contains a higher ratio of a particular isotope or isotopes than naturally occurs. The carbon and oxygen content of a polymer or copolymer can also be enriched in isotopes of carbon and oxygen, including, but not limited to, 13 C. 14 C. 17 O or 18 The hydrogen isotope may be enriched to have a higher ratio of hydrogen, hydrogen, and oxygen than naturally occurring. Other isotopes of carbon, hydrogen, and oxygen are known to those skilled in the art. A preferred hydrogen isotope enriched in P4HB or its copolymers or PBS or its copolymers is deuterium, i.e., deuterated P4HB or its copolymers or deuterated PBS or its copolymers. The percentage deuteration may be at least 1% and up to 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, 80%, or 85% or more.

[0097]

[0119] In a preferred embodiment, the polymers and copolymers used to make the load-bearing macroporous networks, including P4HB and its copolymers, and PBS and its copolymers, have a low water content. This is preferred to ensure that implants with high tensile strength, long term strength retention, and good life span can be produced. In a preferred embodiment, the water content of the polymers and copolymers used to make the implants is less than 1,000 ppm (0.1 wt%), less than 500 ppm (0.05 wt%), less than 300 ppm (0.03 wt%), more preferably less than 100 ppm (0.01 wt%), and even more preferably less than 50 ppm (0.005 wt%).

[0098]

[0120] The composition used to make the implant desirably has a low endotoxin content. In a preferred embodiment, the endotoxin content is sufficiently low that the endotoxin content of the implant produced from the polymer composition is less than 20 endotoxin activity units per device as determined by Limulus amebocyte lysate (LAL) assay. In one embodiment, the endotoxin content of the polymer composition used to make the load-bearing macroporous network of the implant is <2.5EU / g of polymer or copolymer. For example, the endotoxin content of P4HB polymer or copolymer, or PBS polymer of the copolymer is <2.5EU / g of polymer or copolymer.

[0099]

[0121] In an embodiment, the reinforcing matrix of the implant, which comprises a macroporous network, is filled with one or more hydrogels. Preferably, the hydrogels are degradable. Preferably, the hydrogels have different degradation rates when two or more hydrogels are present in the implant. In an embodiment, the implant comprises a first hydrogel and a second hydrogel, the second hydrogel degrading faster than the first hydrogel. In an embodiment, the implant further comprises a third hydrogel, and the third hydrogel degrading faster than the second hydrogel.

[0100]

[0122] In embodiments, the hydrogel is a homopolymer, copolymer, or multipolymer interpenetrating polymer hydrogel. The hydrogel may be amorphous, semi-crystalline, or crystalline. The hydrogel may include chemical or physical crosslinks. The hydrogel may be photocrosslinked. The hydrogel may be nonionic, ionic, amphoteric, containing both acidic and basic groups, or zwitterionic, containing both anionic and cationic groups.

[0101]

[0123] Examples of hydrogels that can be formed by physical crosslinking, e.g., by heating a polymer solution, cooling a polymer solution, hydrogen bonding, or by ionic interactions, include PEG-PLA, PEO-PPO, agarose, carrageenan, gelatin, Na+alginate-+Ca2+, +2Cl-, Na+alginate-polylysine, chitosan-polylysine, chitosan-TPP, and CMC. Examples of hydrogels that can be formed by chemical crosslinking include collagen-glutaraldehyde. Examples of hydrogels that can be formed by radiation crosslinking include PEG and PVME.

[0102]

[0124] In embodiments, the implant may include a first hydrogel and a second hydrogel with different degradation rates, and the first and second hydrogels may have different amounts of crosslinking. The first hydrogel may be more crosslinked than the second hydrogel, such that the first hydrogel degrades slower than the second hydrogel. In embodiments, the implant may include a third hydrogel with a third different degradable rate and a third different degree of crosslinking. The third hydrogel may be crosslinked such that the second hydrogel degrades slower than the third hydrogel. In embodiments, the hydrogels may only differ in the amount of crosslinking.

[0103]

[0125] In embodiments, hydrogels may be formed from a pregel and a gelling agent. For example, the gelling agent may be a crosslinking agent. The crosslinking agent may be added to the pregel in different amounts or concentrations to produce hydrogels with different degradation rates. The crosslinking agent may crosslink the hydrogel chemically or physically. The crosslinking agent may be an agent, including organic and inorganic crosslinking agents, but may also be a non-agent, including, for example, light to photochemically crosslink the hydrogel. For hydrogels formed by photocrosslinking, hydrogels with different degradation rates may be formed from a photocrosslinkable pregel by using light of different intensity or duration. Photocrosslinked hydrogels may also be formed with different degradation rates from a photocrosslinkable pregel that includes two or more different crosslinking chemistries that may be activated with light of different wavelengths.

[0104]

[0126] In embodiments, the hydrogels and pregels may comprise natural polymers, such as proteins, polypeptides, glycosaminoglycans, and polysaccharides. Examples include hydrogels and pregels including collagen, gelatin, fibrin, elastin, silk, starch, cellulose, methylcellulose, carboxymethylcellulose, hydroxypropylmethylcellulose, hyaluronan, hyaluronic acid (HA), alginate, chitosan, carrageenan, pectin, pullulan, dextran, beta-glucan, gellan, welan, xanthan, agarose, chondroitin sulfate, dermatan sulfate, heparin, keratin sulfate, albumin, casein, elastin, and resilin. The hydrogels and pregels may comprise synthetic polymers. Examples include hydrogels and pregels including polyvinyl alcohol, poly(vinyl methyl ether), polyethylene glycol, poly(ethylene glycol) diacrylate (PEGDA), poly(ethylene glycol) dimethacrylate (PEGDMA), polypropylene glycol, polyurethanes, polyphosphazenes, polypeptides, poly(N-isopropylacrylamide), poly(vinylpyrrolidone), polymethacrylic acid, and polyacrylates and copolymers. In embodiments, the hydrogels and pregels may include both natural and synthetic components, such as methacrylated gelatin (GelMa) hydrogel, GelMa and PEGDA, alginate and polyacrylamide, and PVA and carrageenan. In embodiments, the hydrogels and pregels may include mixtures of natural polymers, such as gelatin and alginate, gelatin and hyaluronic acid or derivatives thereof, gelatin and agar.

[0105]

[0127] In an embodiment, the implant comprises a hyaluronic acid-based hydrogel (HA-based hydrogel). In an embodiment, the HA-based hydrogel is formed by photocrosslinking. In an embodiment, the HA-based hydrogel is formed by thiol-ene photocrosslinking. In an embodiment, the HA-based hydrogel is formed by derivatization with norbornene, or a derivative thereof, such as norbornene carboxylic acid, and photoinitiated crosslinking of norbornene with a dithiol crosslinker. Optionally, the norbornene-derived HA-based hydrogel can be further derivatized with other ligands by photoinitiated reaction with other monothiols or dithiols. In an embodiment, the implant comprises a norbornene-modified alginate.

[0106]

[0128] Additional pregels, gelators, crosslinkers, and hydrogels, as well as methods for printing these 3D hydrogels, are described in Li et al. “3D PRINTING OF HYDROGELS: RATIONAL DESIGN STRATEGIES AND EMERGING BIOMEDICAL APPLICATIONS”, Mater. Sci. Eng, R 140 (2020) 100543, https: / / doi.org / 10.1016 / j.mser.2020.100543.

[0107]

[0129] In an embodiment, the reinforcing matrix of the implant, which comprises a macroporous network, is filled with one or more water-soluble polymers. Preferably, the water-soluble polymers are degradable from the implant over time. Preferably, when two or more water-soluble polymers are present in the implant, the water-soluble polymers have different degradation rates. In an embodiment, the implant comprises a first water-soluble polymer and a second water-soluble polymer, and the second water-soluble polymer degrades faster than the first water-soluble polymer. In an embodiment, the implant further comprises a third water-soluble polymer, and the third water-soluble polymer degrades faster than the second water-soluble polymer.

[0108]

[0130] Examples of water-soluble polymers that can be used to make the implant include: polyethylene glycol, polyvinylpyrrolidone (PVP), polyvinyl alcohol (PVA), polyacrylic acid, polyacrylamide, polyphosphates, polyoxazolines, divinyl ether-maleic anhydride, N-(2-hydroxypropyl) methacrylamide, and polyphosphazenes.

[0109]

[0131] B. Additives

[0132] Some additives may be incorporated into the implant. The additives may be incorporated into the matrix of the implant. The additives may be incorporated into or on one or more hydrogels or one or more water-soluble polymers of the implant, including on the load-bearing macroporous network of the implant or on the surface of the implant. In one embodiment, one or more additives are incorporated during the compounding process with a polymer or copolymer described herein to produce pellets or fibers that can then be processed to produce the load-bearing macroporous network of the implant. For example, the pellets or fibers can be 3D printed to form the load-bearing macroporous network of the implant. In another embodiment, the pellets can be ground to produce a powder suitable for further processing, for example, by 3D printing. Or, a powder suitable for further processing, for example, by 3D printing, can be directly formed by blending the additives with the polymer or copolymer. If necessary, the powder for use in processing can be sieved to select the optimal particle size range. In another embodiment, the additives can be incorporated into the polymer composition used to create the load-bearing macroporous network structure of the implant using a solution-based process. In embodiments, the one or more additives may be mixed with the one or more hydrogels or the one or more water-soluble polymers and incorporated into the implant during filling of the implant with the one or more hydrogels or the one or more water-soluble polymers. In embodiments, the one or more additives may be coated onto the one or more hydrogels or the one or more water-soluble polymers after the implant is filled with the one or more hydrogels or the one or more water-soluble polymers. The one or more hydrogels or the one or more water-soluble polymers may also be derivatized with the one or more additives before the one or more hydrogels or the one or more water-soluble polymers are incorporated into the implant.

[0110]

[0133] In preferred embodiments, the additive is biocompatible, and even more preferably, the additive is both biocompatible and absorbable.

[0111]

[0134] In one embodiment, the additives may be nucleating agents and / or plasticizers. These additives may be added in sufficient amounts to the polymeric compositions used to create the load-bearing macroporous network of the implant matrix to produce the desired results. Generally, these additives may be added in amounts of 1% to 20% by weight. Nucleating agents may be incorporated to increase the crystallization rate of the polymer, copolymer, or blend. Such nucleating agents may be used, for example, to facilitate the fabrication of the load-bearing macroporous network of the implant and to improve the mechanical properties of the load-bearing macroporous network of the implant. Preferred nucleating agents include, but are not limited to, salts of organic acids such as calcium citrate, polymers or oligomers of PHA polymers and copolymers, high melting point polymers such as PGA, talc, micronized mica, calcium carbonate, ammonium chloride, and aromatic amino acids such as tyrosine and phenylalanine.

[0112]

[0135] Plasticizers that may be incorporated into the polymer composition to create a load-bearing macroporous network for the implant matrix include, but are not limited to, di-n-butyl maleate, methyl laurate, dibutyl fumarate, di(2-ethylhexyl)(dioctyl)maleate, paraffin, dodecanol, olive oil, soybean oil, polytetramethylene glycol, methyl oleate, n-propyl oleate, tetrahydrofurfuryl oleate, epoxidized linseed oil, 2-ethylhexyl epoxythalate, glycerol triacetate, linoleic acid. Examples of suitable plasticizers include methyl, dibutyl fumarate, methyl acetyl ricinoleate, acetyl tri(n-butyl)citrate, acetyl triethyl citrate, tri(n-butyl)citrate, triethyl citrate, bis(2-hydroxyethyl)dimerate, butyl ricinoleate, glyceryl tri-(acetyl ricinoleate), methyl ricinoleate, n-butyl acetyl ricinoleate, propylene glycol ricinoleate, diethyl succinate, diisobutyl adipate, dimethyl azelate, di(n-hexyl)azelate, tri-butyl phosphate, and mixtures thereof. Particularly preferred plasticizers are citrate esters.

[0113]

[0136] C. Bioactive Agents, Cells and Tissues

[0137] The matrix of the implant may be loaded, filled, coated, or otherwise incorporated with a bioactive agent. Bioactive agents may be included in the matrix of the implant for a variety of reasons. For example, bioactive agents may be included to improve tissue ingrowth into the implant, to improve tissue maturation, to effect delivery of active agents, to improve wettability of the implant, to prevent infection, and to improve cell attachment. Bioactive agents may also be incorporated into or on the load-bearing macroporous network structure of the matrix of the implant, or into or on one or more hydrogels of the matrix of the implant.

[0114]

[0138] The matrix of the implant may contain active agents designed to stimulate cellular ingrowth, including growth factors, cell adhesion factors such as cell adhesion polypeptides, cell differentiation factors, cell recruitment factors, cell receptors, cell binding factors, cell signaling molecules such as cytokines, and molecules that promote cell migration, cell division, cell proliferation and extracellular matrix deposition. Such active agents include fibroblast growth factor (FGF), transforming growth factor (TGF), platelet derived growth factor (PDGF), epidermal growth factor (EGF), granulocyte-macrophage colony stimulation factor (GMCSF), vascular endothelial growth factor (VEGF), insulin-like growth factor (IGF), hepatocyte growth factor (HGF), interleukin-1-B (IL-1 B), interleukin-8 (IL-8), and nerve growth factor (NGF), and combinations thereof. As used herein, the term "cell adhesion polypeptide" refers to a compound having at least two amino acids per molecule that is capable of binding cells by cell surface molecules. Cell adhesion polypeptides include any of the proteins of the extracellular matrix known to play a role in cell adhesion, such as fibronectin, vitronectin, laminin, elastin, fibrinogen, collagen types I, II, and V, as well as synthetic peptides with similar cell adhesion properties. Cell adhesion polypeptides also include peptides derived from any of the above proteins, including fragments or sequences that contain the binding domain.

[0115]

[0139] The implant matrix may incorporate wetting agents designed to improve the wettability of the surface of the load-bearing macroporous network, hydrogel or water-soluble polymer structure to allow fluids to be easily absorbed onto the implant surface and to promote cell attachment and / or modify the water contact angle of the implant surface. Examples of wetting agents include polymers of ethylene oxide and propylene oxide, such as polyethylene oxide, polypropylene oxide, or copolymers thereof, such as PLURONICS®. Other suitable wetting agents include surfactants, emulsifiers and proteins, such as gelatin.

[0116]

[0140] Other bioactive agents that may be incorporated into the matrix of the implant include antimicrobial agents, especially antibiotics, bactericides, oncological agents, anti-scarring agents, anti-inflammatory agents, anesthetics, small molecule drugs, anti-adhesives, inhibitors of cell proliferation, anti-angiogenic and pro-angiogenic factors, immunomodulators, and blood coagulants. Bioactive agents may be proteins, such as collagen and antibodies, peptides, polysaccharides, such as chitosan, alginates, hyaluronic acid and their derivatives, nucleic acid molecules, small molecular weight compounds, such as steroids, inorganic materials, such as hydroxyapatite and ceramics, or complex mixtures, such as platelet-rich plasma. Suitable antimicrobial agents include: bacitracin, biguanides, triclosan, gentamicin, minocycline, rifampin, vancomycin, cephalosporins, copper, zinc, silver, and gold. Nucleic acid molecules may include DNA, RNA, siRNA, miRNA, antisense, or aptamers.

[0117]

[0141] The matrix of the implant may also include allograft and xenograft materials, such as acellular dermal matrix material and small intestinal submucosa (SIS).

[0118]

[0142] In embodiments, the implant may include a vascular pedicle, vascular pedicle perforator, or other tissue mass. The vascular pedicle, vascular pedicle perforator, or other tissue mass may be autologous tissue, allograft tissue, or xenograft tissue.

[0119]

[0143] In another embodiment, the implant may incorporate a system for controlled release of the therapeutic or prophylactic agent.

[0120]

[0144] In some embodiments, the implant may be coated with autograft, allograft or xenograft tissue and cells before, during or after implantation, or any combination thereof. In some particularly preferred embodiments, the implant is coated with autologous tissue and cells from the patient before, during or after implantation, or any combination thereof. The autologous tissue and cells are preferably one or more of the following: autologous fat, lipoaspirate, fat tissue, injectable fat, adipose tissue, adipocytes, fibroblasts, and stem cells, such as human adipose tissue-derived stem cells, also known as preadipocytes or adipose tissue-derived progenitor cells, and fibroblast-like stem cells. In a preferred embodiment, the implant may be coated with autologous tissue and cells as described herein, and may further include vascular pedicles, vascular pedicle perforators, or other tissue masses. As will become apparent herein, the load-bearing macroporous network structure of the implant is designed to create a large surface area that can hold not only the shape of the breast implant, but also autologous tissue and cells to promote tissue ingrowth.

[0121]

[0145] III. Methods for Making Multicomponent Breast Implants

[0146] A variety of methods can be used to manufacture the implant.

[0122]

[0147] In embodiments, the implant is engineered to provide one or more of the following: (i) structural support within the breast; (ii) a matrix with a load-bearing macroporous network with an open structure for tissue ingrowth; (iii) an expansion volume for tissue ingrowth that increases over a period of time to allow tissue ingrowth and prevent or minimize fluid retention; (iv) controlled tissue ingrowth from the surface of the implant toward the core of the implant; (v) a tissue ingrowth volume that can absorb water and other biological fluids with high affinity; (vi) a slowly resorbing macroporous network engineered to allow complete tissue ingrowth of the implant before complete degradation; (vii) a matrix with a load-bearing macroporous network with an open structure for tissue ingrowth; (iii) an expansion volume for tissue ingrowth that increases over a period of time to allow tissue ingrowth and prevent or minimize fluid retention; (iv) a controlled tissue ingrowth from the surface of the implant toward the core of the implant; (v) a tissue ingrowth volume that can absorb water and other biological fluids with high affinity; (vii) a slowly resorbing macroporous network engineered to allow complete tissue ingrowth of the implant before complete degradation; (vii) a matrix with a load-bearing macroporous network that can absorb cells, tissue, fat, lipoaspirate, adipocytes, fibroblasts, stem cells, and other biological fluids. (viii) a structure that may allow incorporation of grafts, such as vascular pedicles or other tissue masses, into the implant structure; (ix) a structure in which the inside of the macroporous network may be coated with cells, tissues, bioactive agents, such as fat, lipoaspirate, adipocytes, fibroblasts, and stem cells, by injection using a needle; (x) a load-bearing macroporous network with an open cell structure having a compressive strength of at least 0.1 kgf at 30% strain; (xi) a structure comprising a load-bearing macroporous network with an open cell structure having a compressive modulus of 0.1 kPa to 10 MPa at 5 to 15% strain; (xii) a structure comprising a load-bearing macroporous network with an open cell structure having a loss modulus of 0.3 to 100 kPa.

[0123]

[0148] A. Implant shape

[0149] In some embodiments, the implants are designed to be three-dimensional at the time of manufacture. In embodiments, the implants are designed to be used in place of permanent breast implants, such as silicone and saline breast implants.

[0124]

[0150] The shape of the implant allows the surgeon to increase tissue volume, reconstruct lost or missing tissue or tissue structures, contour tissue, augment tissue, restore tissue function, repair damaged tissue structures, strengthen existing tissue structures, increase soft tissue volume, alter breast mound, increase upper pole fullness, and reshape the breast. In preferred embodiments, the implants are used to reshape or repair the breast, to augment the breast, and to repair the breast after mastectomy. In some embodiments, the implants allow the shape of the soft tissue structures to be changed or reshaped without the use of permanent implants.

[0125]

[0151] In an embodiment, and with reference to Figure 1A, a multi-component breast implant 1 comprising a reinforcing matrix comprises a surface 2, a core 3, a posterior section 4 for placement on or near a patient's chest wall, an anterior section 5 opposite the posterior section, an anterior bottom 6 for placement in the lower pole of the breast, an anterior top 7 for placement in the upper pole of the breast, an anterior middle region 8 for placement under the patient's skin, and a load-bearing macroporous network 9 comprising an open cell structure. The multi-component breast implant 1 further comprises a first hydrogel 10, a second hydrogel 11, and a third hydrogel 12, the third hydrogel being present on the surface 2 of the implant. Figure 1B shows an isometric view of the multi-component breast implant 1 comprising the posterior section 4, the anterior section 5 opposite the posterior section, the anterior bottom 6, the anterior top 7, the anterior middle region 8, and the locations of the first hydrogel 10, the second hydrogel 11, and the third hydrogel 12 within the implant. Figure 1C shows a cross-section along the midplane of the multi-component breast implant 1 and a top view of the locations of the first hydrogel 10, second hydrogel 11, and third hydrogel 12. Figure ID shows an alternative isometric view of the multi-component breast implant 1 with a posterior section 4 and an anterior section 5. In embodiments, one or more water soluble polymers may be substituted for one or more of the hydrogels 10, 11, and 12.

[0126]

[0152] The anterior section of the breast implant is shaped to provide a bulge to the breast. As used herein, the bulge of the implant is the maximum distance between the posterior and anterior sections of the implant.

[0127]

[0153] In an embodiment, the anterior bottom area of ​​the implant includes a convex outer surface. The convex outer surface shape of the implant provides a pleasing anatomical shape to the lower pole of the breast.

[0128]

[0154] It should be understood that there are multiple implant shapes and sizes within the scope described herein, and the present invention is not limited with respect to the three-dimensional shape and size of the implant, except as recited in the appended claims. The implant can be fabricated or printed to have any size and shape suitable for use as an implant. For example, implants having three-dimensional shapes such as spheres, hemispheres, cylinders, teardrops, anatomical, cones, domes, rectangular prisms, tetrahedrons, triangular or regular prisms, dodecahedrons, tori, and ellipsoids can be easily fabricated, and custom shapes can be produced, optionally with the aid of computer-aided design. For example, dome-shaped implants can be produced for breast reconstruction.

[0129]

[0155] The shape of the implant including the reinforcing matrix is ​​created by the load-bearing macroporous network structure. For example, the dome shape of FIG. 1A is created by the load-bearing macroporous network structure 9. The shape of the load-bearing macroporous network may be altered to provide different implant shapes.

[0130]

[0156] The implant may have different shapes in the anterior bottom area and the anterior top area of ​​the implant. The dimensions of the implant may be sized to increase breast tissue volume, replace previous breast tissue volume, change the volume distribution of breast tissue, change the appearance of breast tissue, or replace existing breast tissue volume with a smaller volume. The implant may be sized or shaped to provide a low, moderate, or high contour shape to the breast, where the contour of the implant determines the mound of the breast. High contour implants may be used to increase the sidewall height of the breast and provide the patient with more upper pole fullness or cleavage. Lower sidewall height increase may be obtained using low or moderate contour implants. The implant may be designed for use in the breast with a size large enough to allow for use in mastopexy and breast reconstruction. In an embodiment, the breast implant has a volume of 100-1200 cc (cubic centimeters), and more preferably a volume of 120-850 cc. In an embodiment, the implant is wide enough to span the width of the breast. In an embodiment, the width of the posterior section of the implant is between 6 and 20 cm, and more preferably between 8 and 18 cm. The prominence of the implant as used herein is the maximum distance between the posterior and anterior sections of the implant. In an embodiment, the prominence of the implant is between 2 and 15 cm, more preferably between 3 and 10 cm, and even more preferably between 4 and 7 cm.

[0131]

[0157] In a preferred embodiment, the implant is provided in a shape that can be used to alter the soft tissue volume of the breast without the use of permanent breast implants, e.g., silicone breast implants. In an embodiment, the implant can be made in a shape and size that can be used to increase the size of the breast or replace the volume and shape of the breast tissue after a mastectomy procedure, to remove breast defects, and to create a particular appearance in the breast. For example, the implant can be made such that, upon implantation into the breast, it creates a breast with a particular ratio of upper pole volume (UPV) to lower pole volume (LPV). In an embodiment, the implant is a breast implant having volumetric dimensions such that implantation of the implant results in a breast with a UPV of 25-35% of the total breast volume and a LPV of 65-75% of the total breast volume. In addition to shaping the breast with a particular volume ratio of upper and lower pole tissue, the size and shape of the implant can also be selected to create a highly desirable shape of the lower pole, upper pole, and degree of breast prominence from the chest wall. In an embodiment, the implant is designed such that (a) the lower pole of the breast has a highly attractive lower pole curvature, specifically an attractive convex shape, (b) the upper pole of the breast has a straight or slightly concave curvature, and (c) the distance the breast rises from the breast wall is defined. It will therefore be apparent that the implant of the present invention can be used to create highly attractive reconstructed breasts by having a specific shape that (i) defines the ratio of UPV to LPV; (ii) defines the curvature of the upper and lower poles; (iii) defines the degree of rise of the breast from the chest wall; and (iv) defines the angular shape of the nipple at the breast.

[0132]

[0158] The shape of the implant may vary. Non-limiting examples of shapes include: rounded, teardrop, anatomical breast shape, or anatomical breast contour.

[0133]

[0159] Additional implant shapes are described in U.S. Patent Application No. 16 / 262,018, filed January 30, 2019 ("FULL CONTOUR BREAST IMPLANT"), which is incorporated herein by reference in its entirety.

[0134]

[0160] In an embodiment, the implant includes one or more openings for inserting one or more tissue masses. In a preferred embodiment, the implant includes one or more openings in a posterior region of the implant (e.g., posterior region 4 of FIG. 1A). The one or more openings in the posterior region of the implant allow the surgeon to insert one or more pedicles into the implant when the posterior region of the implant is implanted into the chest wall. The one or more openings in the implant may create a chamber in the implant or create a passageway through the implant. For example, the openings may extend from the posterior region 4 of the implant to the anterior region 5 of the implant. In an embodiment, the implant may include an opening extending in a medial to lateral direction for insertion of a tissue mass. In an embodiment, the implant may include one or more openings in the anterior region 5, anterior bottom 6, anterior top 7, or anterior middle region 8 of the implant. The dimensions of the one or more openings are sized to receive the tissue mass.

[0135]

[0161] B. Implant Construction

[0162] The implant comprises a reinforcing matrix comprising an open cell structure and a load-bearing macroporous network comprising one or more hydrogels, one or more water-soluble polymers, or a combination of hydrogels and water-soluble polymers.

[0136]

[0163] In embodiments, the load-bearing macroporous network may be produced using a textile process and may include filaments. For example, the macroporous network may be produced by knitting, weaving, or braiding filaments. The filaments may be monofilaments, multifilaments, and / or yarns. In embodiments, the load-bearing macroporous network is a 3D textile.

[0137]

[0164] In embodiments, the macroporous network may be an orthogonal woven structure, a multi-layer structure, or an oblique three-dimensional woven structure. In embodiments, a 3D textile is formed by filaments or yarns that run along two axes (x-axis and y-axis) plus filaments or yarns that run at an additional angle to create thickness. In embodiments, the macroporous network is a 3D knitted structure.

[0138]

[0165] In embodiments, the load-bearing macroporous network can be made using nonwoven textiles. In embodiments, the macroporous network comprises multiple layers of nonwovens. In embodiments, the macroporous network can comprise nonwoven 3D fabrics. The nonwoven can comprise short filaments, such as short filaments. In embodiments, the nonwoven can be meltblown, electrospun, derived from staple fibers, dry spun, made by centrifugal spinning, solution spun, spunlaid, or spunbonded.

[0139]

[0166] In an embodiment, the macroporous network may comprise a 3D braided fabric, which may be formed by inter-plating three orthogonal sets of filaments or yarns together.

[0140]

[0167] In an embodiment, the macroporous network may include a 3D composite. For example, the macroporous network may include a 3D woven composite, a 3D braided composite, a 3D stitched composite. In an embodiment, the 3D composite is formed by applying a resin to a 3D preform, such as a 3D woven composite, a 3D braided composite, or a 3D stitched composite.

[0141]

[0168] In embodiments, the load-bearing macroporous network is formed by particle leaching or phase separation. For example, a polymer solution containing particles or porogens can be transferred to a suitable mold formed in the shape of the macroporous network, after which the solvent is removed, for example by evaporation or freeze-drying, leaving the particles in the polymer structure. The mold can then be transferred to a bath to dissolve the particles or porogens and form the macroporous network.

[0142]

[0169] In an embodiment, the load-bearing macro-porous network is formed by foaming, hi an embodiment, the macro-porous network is an open-cell porous foam.

[0143]

[0170] In an embodiment, the load-bearing macroporous network is formed by lamination, hi an embodiment, the laminate is perforated to form the macroporous network.

[0144]

[0171] In an embodiment, the load-bearing macroporous network is formed from 3D printed filaments or printed lines. In one embodiment, the implant is fabricated using 3D printing to build the load-bearing macroporous network of the implant. 3D printing of the macroporous network is highly desirable because it allows precise control of the shape of the macroporous network of the implant. Suitable methods for 3D printing include extrusion-based additive manufacturing, fused deposition modeling, fused filament fabrication, melt extrusion deposition, selective laser melting, printing of slurries and solutions using a coagulation bath, and printing using binding solutions and powder granules. Preferably, the macroporous network of the implant is fabricated by extrusion-based additive manufacturing, such as fused deposition modeling or fused filament fabrication.

[0145]

[0172] In an embodiment, the average diameter or width of the filaments or printed lines of the load-bearing macroporous network is 50-800 μm, more preferably 100-600 μm, and even more preferably 150-550 μm. In an embodiment, the distance between the filaments of the implant is 50 μm-5 mm, more preferably 100 μm-1 mm, and even more preferably 200 μm-1 mm.

[0146]

[0173] The average diameter of the filaments and the distance between the filaments can be selected according to the desired properties of the load-bearing macroporous network, such as the compression modulus and porosity. For example, the porosity of the macroporous network can be reduced by reducing the infill density (defined as the ratio, expressed as a percentage, of the volume occupied by the filament material in the macroporous divided by the total volume of the macroporous network) when the filament size, interfilament spacing, and printing or textile pattern are kept constant. When the infill density is reduced, the compression modulus is also reduced when the filament size, interfilament spacing, and printing pattern are kept constant. In an embodiment, the infill density of the macroporous network of the implant is 1-60%, and more preferably 5-25%.

[0147]

[0174] In an embodiment, the pore width or diameter of the macroporous network is less than 15 mm, and preferably 1 mm to 8 mm, and more preferably 2 mm to 5 mm. In an embodiment, the pore sizes of the macroporous network of the implant are the same. In an embodiment, the macroporous network of the implant has a mixture of pore sizes. Preferably, the load-bearing macroporous network of the implant has an architecture that provides a larger surface area and a large void volume suitable for allowing the macroporous network to be colonized by cells and infiltrated by tissue, blood vessels, or a combination thereof as the hydrogel or water-soluble polymer in the macroporous network degrades.

[0148]

[0175] In embodiments, the external porosity of the macroporous network may be less than or greater than the vertical porosity of the macroporous network.

[0149]

[0176] In an embodiment, the filaments or printed lines within the macroporous network are bonded to at least one other filament or printed line.

[0150]

[0177] In an embodiment, the filaments or printed lines within the macroporous network have a surface roughness.

[0151]

[0178] In embodiments, the properties of the macroporous network, such as the compressive modulus, can also be altered by varying the 3D Computer Aided Design Model (CAM) for printing the load-bearing macroporous network.

[0152]

[0179] In an embodiment, the macroporous network comprises a unit cell. In an embodiment, the network may be made from unit cells having one or more of the following shapes: tetrahedron, cuboid, pentahedron, hexahedron, heptahedron, octahedron, icosahedron, decahedron, dodecahedron, tetradecahedron, as well as prism, antiprism, and truncated polyhedron. Examples of unit cells in the shape of prism, antiprism, and truncated polyhedron are hexagonal prism, octagonal antiprism, and truncated dodecahedron. In an embodiment, the unit cell is formed from an elongated polyhedron. In a preferred embodiment, the unit cell has 4, 6, 8, 12, or 20 faces. In a particularly preferred embodiment, the unit cell is a dodecahedron, and even more preferably a rhombic dodecahedron. In an embodiment, the network may be fabricated from two or more different unit cells, for example, a combination of dodecahedron and octagonal shapes. In an embodiment, the size and shape of the unit cell may be selected to provide different types of porous networks with different volumetric densities. The properties of a network formed from repeating unit cells are highly predictable and can be predicted based on the dimensions of the unit cells and the materials used to make the unit cells. Unit cells with different physical properties can be created by selecting the dimensions of the unit cells, the geometric shape of the unit cells, and the materials used to make the unit cells. Selecting specific unit cell dimensions and materials allows for the production of networks from unit cells with properties that are compressible and soft. In embodiments, the mechanical properties of the network can be altered by not changing the shape of the unit cells, but instead by changing the diameter or width of the filaments of the unit cells. For example, if the desired mechanical properties, such as the modulus of elasticity or compressive strength, are known, the required filament thickness or diameter for a given unit cell fabricated from a given polymer can be calculated. In preferred embodiments, the dimensions and materials of the unit cells are selected such that the implant network made from the unit cells has properties similar to those of breast tissue. In preferred embodiments, the unit cells of the macroporous network can be compressed and, optionally, recover to their original shape when the compressive force is released.

[0153]

[0180] In embodiments, the pore size of the implant's macroporous network is large enough to allow a needle to be inserted into the pores of the network to deliver bioactive agents, cells, fat, and other compositions by injection. In embodiments, the architecture of the macroporous network is designed to allow a needle of gauge 12-21 to be inserted into the network. This property allows cells, tissue, collagen, bioactive agents, and additives, such as fat, to be loaded into the macroporous network using a syringe without damaging the network. In embodiments, the network allows a needle of outer diameter 0.5-3 mm to be inserted into the network.

[0154]

[0181] In an embodiment, the implant comprises an outer shell surrounding a reinforcing matrix or surrounding a load-bearing macroporous network.

[0155]

[0182] In an embodiment, the load-bearing macroporous network may be 3D printed to further include one or more openings for inserting a tissue mass. The tissue mass is preferably a vascular pedicle. The openings are preferably formed in the posterior section 4 of the implant for inserting the tissue mass. The openings may extend partially into the implant or may extend from the posterior section 4 to the anterior section 5 of the implant. The implant may include openings in the anterior bottom 6, anterior top 7, or anterior middle region 8 of the implant. These openings may extend partially into the implant or may extend entirely through the implant.

[0156]

[0183] In a typical procedure, the load-bearing macroporous network of the implant is fabricated by extrusion-based additive manufacturing, such as melt extrusion deposition, hot melt pellet deposition, and hot melt filament fabrication, of a composition comprising an absorbable polymer or blends thereof.

[0157]

[0184] The absorbent polymer or blend is preferably dried before printing to avoid significant loss of intrinsic viscosity. Preferably, the polymer or blend is dried so that the moisture content of the printed composition is 0.5 wt% or less, and more preferably 0.05 wt% or less, as measured gravimetrically. The polymer or blend can be dried in a vacuum. In a particularly preferred method, the polymer or blend is dried in a vacuum chamber under a vacuum of at least 10 mbar, more preferably at least 0.8 mbar, to a moisture content of less than 0.03 wt%. Elevated temperatures below the melting point of the polymer may also be used in the drying process. Alternatively, the polymer may be dried by extraction into a solvent and reprecipitation of the polymer or by using a desiccant. The moisture content of the polymer or blend can be determined using a VaporPro Moisture Analyzer from Arizona Instrument, or a similar instrument.

[0158]

[0185] In one embodiment, the load-bearing macroporous network of the implant is formed by extrusion-based additive manufacturing of poly-4-hydroxybutyrate (P4HB), such as fused pellet deposition, fused filament fabrication, and melt extrusion deposition. The P4HB polymer (Mw 100-600 kDa) is preferably dried as described above for 3D printing. The polymer can be pelletized and optionally ground for fused pellet deposition and melt extrusion deposition, or extruded into filaments suitable for 3D printing via fused filament fabrication.

[0159]

[0186] P4HB pellets or filaments can be 3D printed by melt extrusion-based additive manufacturing to form the macroporous network of a breast implant, for example, using the printing parameters shown in Table 1, an Arburg Freeformed 200-3X 3D printer, and a 3D CAD (Computer Aided Design) Model for the load-bearing macroporous network of the implant. The average diameter of the 3D filaments printed from the P4HB polymer is selected based on the desired load-bearing macroporous network properties, such as the compressive modulus of the network, and the porosity or infill density. Preferably, the average filament diameter or width is 50-800 μm, more preferably 100-600 μm, and even more preferably 150-550 μm.

[0160] [Table 1]

[0161]

[0188] In another embodiment, the parameters shown in Table 2 may be used for melt extrusion-based additive manufacturing of load-bearing macroporous networks using a composition comprising poly(butylene succinate) or a copolymer thereof and an Arburg Freeformed 200-3X 3D printer.

[0162] [Table 2]

[0163]

[0190] In embodiments, the implant comprises a reinforcing matrix comprising a load-bearing macroporous network at least partially filled with one or more hydrogels, one or more water-soluble polymers, or a combination thereof.

[0164]

[0191] In an embodiment, the load-bearing macroporous network can be filled with hydrogel and / or water-soluble polymer by 3D printing. In one embodiment, the load-bearing macroporous network is at least partially filled with hydrogel by 3D printing a pregel solution or slurry from one print head and adding a gellant to the pregel solution from a second print head. Adding the gellant to the pregel solution leads to the formation of a hydrogel within the load-bearing macroporous network. In an embodiment, the hydrogel can be formed from the pregel solution or slurry by irradiating the pregel to form the hydrogel, rather than printing the pregel solution and adding the gellant. This method can be used, for example, when the pregel solution or slurry can be crosslinked by irradiation with light (i.e., the method can be used in the creation of photocrosslinkable hydrogels).

[0165]

[0192] The concentration of the pregel solution or slurry used for 3D printing of the implant depends on the molecular weight of the pregel. In embodiments, the pregel solution or slurry is printed from a solution or slurry of pregel at a concentration of 1-20 wt%, more preferably 1-10 wt%, and even more preferably 2-5 wt%. For example, an alginate pregel may be printed at a concentration of 2-5 wt%, and a solution of calcium chloride is used as the gelling agent. In embodiments, the pregel solution may include a mixture of pregels. For example, the pregel solution may include 3% alginate and 9% methylcellulose, and may be gelled using a solution of calcium chloride.

[0166]

[0193] In embodiments, two hydrogels with different degradation rates can be 3D printed to at least partially fill an implant from the same pregel solution or slurry by increasing or decreasing the crosslinking of the pregel solution or slurry. For example, a first hydrogel can be printed into an implant from a pregel solution or slurry and crosslinked with a gelling solution, and a second hydrogel can be printed from the same pregel solution but crosslinked to a lesser extent with the same gelling solution by using a lower concentration of gelling solution or by shortening the exposure time of the pregel to the gelling solution (e.g., reducing the dripping of gelling solution applied by the printer). Alternatively, for example, a first hydrogel can be printed into an implant from a pregel solution or slurry and crosslinked by irradiation with light, and a second hydrogel can be printed into an implant from the same pregel solution but crosslinked to a lesser extent by shortening the exposure time of the pregel to light or by reducing the intensity of the light.

[0167]

[0194] In embodiments, two hydrogels may be printed into the implant by printing two different pregel solutions or slurries. A first hydrogel may be printed into the macroporous network of the implant by printing the first pregel solution or slurry and the first gelator into the macroporous network. A second hydrogel may be printed into the macroporous network of the implant by printing the second pregel solution or slurry and the gelator into the macroporous network. Depending on the selection of the second hydrogel, the gelator may be the same as or different from the first gelator. In embodiments, the first pregel and the first gelator are printed to fill the core of the macroporous network with the first hydrogel, and the second pregel and gelator are printed to form a second hydrogel surrounding the first hydrogel.

[0168]

[0195] In an embodiment, the load-bearing macroporous network is at least partially filled with a water-soluble polymer by 3D printing filaments of the water-soluble polymer or resin. For example, polyvinyl alcohol filaments may be used to at least partially fill the macroporous network. In an embodiment, the polyvinyl alcohol filaments may be 3D printed at an extrusion temperature of 205-220°C.

[0169]

[0196] Preferably, the implant is fabricated using a 3D printer setup equipped with multiple print heads, where the printer can print the macroporous network of the implant as well as the one or more hydrogels and / or one or more water-soluble polymers of the implant in a single manufacturing step.

[0170]

[0197] A suitable setup 20 for 3D printing an implant comprising a load-bearing macroporous network and a reinforcing matrix comprising two hydrogels is shown in FIG. 2. In this embodiment, the 3D printer comprises three print heads 23, 24, and 25 and a 3D printing stage 22. The reservoir 29 of the first print head 23 is filled with pellets 32 of a polymer composition for printing the load-bearing macroporous network. The reservoir 30 of the second print head 24 is filled with a pre-gel solution or slurry 33, and the reservoir 31 of the third print head 25 is filled with a gelling agent 34. FIG. 2 shows the implant 21 being printed by simultaneously printing a load-bearing macroporous network 26 with an open cell structure on the printing stage 22 and filling it with a first hydrogel 27 and a second hydrogel 28 surrounding the first hydrogel 27. The printing of the macroporous network and filling the network with the first and second hydrogels are performed according to a 3D CAD Model for the implant. The first hydrogel 27 can be formed in the macroporous network by printing a solution or slurry of the pre-gel 33 from the second print head 24 and adding a first concentration or amount of gelling agent 34 from the third print head 25. The second hydrogel 28 can be formed in the macroporous network by surrounding the first hydrogel 27 by printing a solution or slurry of the pre-gel 33 from the second print head 24 and adding a second concentration or amount of gelling agent 34 from the third print head. The first and second concentrations or amounts of gelling agent 34 can be selected to form the first and second hydrogels, where the second hydrogel degrades faster than the first hydrogel. For example, a higher concentration or amount of gelling agent 34 is added to the pre-gel 33 to form the first hydrogel 27 than is added to form the second hydrogel 28. In an embodiment, print head 23 may be designed to print filaments instead of pellets.

[0171]

[0198] In another embodiment, a similar equipment setup as shown in FIG. 2 can be used to 3D print an implant comprising a macroporous network and a reinforcing matrix comprising two hydrogels, where the first and second hydrogels are formed by photocrosslinking instead of using a gelling agent. In this embodiment, the third print head 25 can be replaced with a suitable light source to photocrosslink the pregel 33. In this embodiment, hydrogels with different degradation rates can be formed by irradiating the pregel for different periods of time or with different intensities or wavelengths of light. Irradiating the pregel for a longer period of time can be used, for example, to form hydrogels that are more highly crosslinked and degrade more slowly than those formed when the pregel is irradiated for a shorter period of time.

[0172]

[0199] In an embodiment, a suitable setup 40 for 3D printing both a load-bearing macroporous network 41 and two hydrogels 42 and 43 of an implant using two different pre-gels is shown in FIG. 3. In this embodiment, the 3D printer includes four print heads 46, 47, 48, and 49 and a 3D printing stage 45. A reservoir 50 of the first print head 46 is filled with pellets 54 of a polymer composition for printing the load-bearing macroporous network. A reservoir 51 of the second print head 47 is filled with a first pre-gel solution or slurry 55. A reservoir 52 of the third print head 48 is filled with a second pre-gel solution or slurry 56. And a reservoir 53 of the fourth print head 49 is filled with a gelling agent 57. FIG. 3 shows an implant 44 being printed at a printing stage 45 by simultaneously printing a load-bearing macroporous network 41 with an open cell structure and filling it with a first hydrogel 42 and a second hydrogel 43 surrounding the first hydrogel 42. The printing of the macroporous network and filling the network with the first and second hydrogels are performed according to a 3D CAD model for the implant. The first hydrogel 42 can be formed in the macroporous network by printing a solution or slurry of a first pre-gel 55 from a second print head 47 and adding a gellant 57 from a fourth print head 49. The second hydrogel 43 can be formed in the macroporous network surrounding the first hydrogel 42 by printing a solution or slurry of a second pre-gel 56 from a third print head 48 and adding a gellant 57 from a fourth print head. The first and second hydrogels may be selected and formed such that the second hydrogel degrades faster than the first hydrogel. In an embodiment, the print head 46 may be configured to print filaments instead of pellets 54.

[0173]

[0200] In an embodiment, and with reference to FIGS. 5A-5C, the implant may be printed such that all three hydrogels are in contact with the chest wall. In this embodiment, when the implant is implanted, each hydrogel will be in contact with the chest wall. In an embodiment, the implant may be printed such that the second hydrogel 120 surrounds the first hydrogel 110, except in the posterior section 140 of the implant 100, where the hydrogels are in contact with the chest wall. In an embodiment, one or two water-soluble polymers may be substituted for one or both of the hydrogels. For example, the implant may be made by 3D printing a water-soluble polymer, such as polyvinyl alcohol, in place of the second hydrogel 120 to surround the first hydrogel 110. The polyvinyl alcohol may be 3D printed, for example, from polyvinyl alcohol filaments at an extrusion temperature of 205-220° C. In an embodiment, an implant may be printed where the implant includes a third hydrogel 130 surrounding the second hydrogel 120 and a second hydrogel surrounding the first hydrogel 110, except on the back surface 140 of the implant 100. In an embodiment, one, two or three water soluble polymers may be replaced with one or more of the hydrogels 110, 120 and 130.

[0174]

[0201] In an embodiment, and referring to Figures 6A-6C, all of the hydrogels (210, 220, 230) of the implant 200 are present in the posterior section 240 of the implant. In an embodiment, one or more water soluble polymers may be substituted for one or more of the hydrogels.

[0175]

[0202] In embodiments, all of the hydrogels (210, 220, 230) of the implant, or one or more of the water soluble polymers of the implant, may come into contact with the chest wall when the implant is implanted in a patient's body.

[0176]

[0203] In embodiments, the implant may be at least partially filled with a hydrogel and / or water soluble polymer without the use of 3D printing.

[0177]

[0204] In embodiments, the implant is made by immersing a load-bearing macroporous network with an open cell structure in a solution or slurry of a pregel, allowing the pregel to infiltrate the macroporous network, removing the solution or slurry of the pregel, and crosslinking the pregel. In embodiments, the pregel is photocrosslinked by exposure to light to form a hydrogel within the macroporous network.

[0178]

[0205] 4A-C show how, in one embodiment, an implant can be made by first allowing the pregel to penetrate the macroporous network and then crosslinking the pregel to provide a macroporous network at least partially filled with hydrogel. FIG. 4A shows a cross-sectional side view of a beaker 60 containing a load-bearing macroporous network 61 of an implant 62. The load-bearing macroporous network can be made, for example, by 3D printing as described herein. As shown in FIG. 4B, the beaker can be filled with a solution or slurry of pregel 64, which submerges or covers the macroporous network 61. The beaker is placed on a shaker 63 and shaken to encourage diffusion of the pregel into the macroporous network, as shown by the direction of arrow 65 in FIG. 4B. Once the pregel has diffused into the macroporous network, the remaining solution or slurry of pregel is removed from the beaker. FIG. 4C shows the macroporous network 61 filled with pregel 66 after the network has been immersed in a solution or slurry of the pregel and the solution or slurry has been removed. The pregel 66 held within the macroporous network 61 can then be crosslinked to form a hydrogel in the macroporous network. In the example shown in FIG. 4C, the pregel is crosslinked by exposing the pregel 66 to light 67. In an alternative embodiment, the pregel 66 can be crosslinked by adding a gelling agent to the pregel. The method shown in FIGS. 4A-C is most suitable for making implants comprising a macroporous network filled with one type of hydrogel, preferably implants comprising photocrosslinkable hydrogels. In an embodiment, the photocrosslinkable pregel comprises a norbornene-derivatized hyaluronic acid-based pregel. These pregels can be crosslinked by exposure to UV light, for example, at wavelengths of 320-390 nm, in the presence of a dithiol crosslinker.

[0179]

[0206] C. Implant Characteristics

[0207] In certain embodiments, the mechanical properties of the implant are designed such that they approach those of breast tissue, hi embodiments, the mechanical properties of the implant are designed such that the mechanical properties of the reinforcing matrix, including the load-bearing macroporous network of the implant, approach those of breast tissue.

[0180]

[0208] In an embodiment, the compressive modulus of the implant or macroporous network of the implant is from 0.1 kPa to 10 MPa, more preferably from 0.3 kPa to 1 MPa, and even more preferably from 3 kPa to 200 kPa at a strain of 5 to 15%. In an embodiment, the compressive modulus of the implant or macroporous network allows the implant to compress when a compressive force is applied, but to recover from compression when the compressive force is removed.

[0181]

[0209] In another embodiment, the compressive modulus of the implant or the macroporous network of the implant is ±50% of the compressive modulus of breast tissue at 5-15% strain, hi other embodiments, the compressive modulus of the implant or the macroporous network is ±50%, more preferably ±25%, of the compressive modulus of glandular tissue, adipose tissue, skin, pectoral fascia, or breast tissue at 5-15% strain.

[0182]

[0210] In embodiments, the filaments present in the macroporous network of the breast implant are formed from a polymeric composition that preferably has one or more of the following properties: (i) elongation at break greater than 100%, (ii) elongation at break greater than 200%, (iii) melting temperature greater than 60° C., (iv) melting temperature greater than 100° C., (v) glass transition temperature less than 0° C., (vi) glass transition temperature between −55° C. and 0° C., (vii) tensile modulus less than 300 MPa, and (viii) tensile strength greater than 25 MPa.

[0183]

[0211] In embodiments, the filaments present in the macroporous network of the breast implant have one or more of the following properties: (i) a breaking load of 0.1-200 N, 1-100 N, or 2-50 N; (ii) an elongation at break of 10%-1,000%, more preferably 25%-500%, and even more preferably 100% or greater than 200%, and (iii) an elastic modulus of 0.05-1,000 MPa, and more preferably 0.1-200 MPa.

[0184]

[0212] In embodiments, the macroporous network of the implant may have anisotropic properties. That is, the macroporous network may have different properties in different directions. For example, the macroporous network may have a first compressive modulus in one direction and a second, different compressive modulus in a second direction. In embodiments, the macroporous network of the breast implant may have different properties in a direction from the anterior top to the anterior bottom of the implant versus the properties of the implant measured in a lateral to medial direction upon implantation in the breast.

[0185]

[0213] To allow tissue ingrowth into the macroporous network of the implant, the macroporous network should have a strength retention long enough to allow cells and blood vessels to infiltrate and proliferate into the macroporous network of the implant. In an embodiment, the strength retention of the macroporous network of the implant is at least 25% at 2 weeks, more preferably at least 50% at 2 weeks, and even more preferably at least 50% at 4 weeks. In another embodiment, the macroporous network of the implant is designed to support mechanical forces acting on the implant and to allow a steady transfer of mechanical forces from the macroporous network to the regenerated host tissue. In particular, the macroporous network of the implant is designed to support mechanical forces acting on the implant and to allow a steady transfer of mechanical forces from the macroporous network to the new host tissue.

[0186]

[0214] D. Other Features of Implants

[0215] The implant, reinforcing matrix, or macroporous network of the implant may be trimmed or cut using scissors, a blade, other sharp cutting instrument, or a thermal knife to provide the desired implant or macroporous network shape. The implant or macroporous network may also be cut into the desired shape using laser cutting techniques. This may be particularly advantageous for shaping filament-based implants, as this technique is versatile and, importantly, may provide shaped implants and macroporous networks without sharp edges.

[0187]

[0216] The implant may include suture tabs so that the implant can be fastened in the body using, for example, sutures and / or staples. The number of tabs may vary. In one embodiment, the number of tabs depends on the load placed on the implant. When the implant is heavier or has a larger volume, a larger number of tabs may be desirable. In an embodiment, the implant includes 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20 or more tabs. In an embodiment, the implant preferably includes 4 or more tabs, preferably 4-12 tabs, to fasten the breast implant to the chest wall. The dimensions of the tabs are preferably 0.5 cm x 0.5 cm to 5 cm x 4 cm, and more preferably 2 cm x 2.5 cm. The tabs attached to the implant should have sufficient strength retention in vivo to resist mechanical loads and to allow sufficient ingrowth of tissue into the implant, preventing movement of the implant after implantation. In a preferred embodiment, the suture pull-out strength of the tabs attached to the implant is greater than 10N, and more preferably greater than 20N.

[0188]

[0217] E. Implant Coatings and Fillings

[0218] The implant comprises a macroporous network, where there are continuous pathways through the implant, which encourage and allow tissue ingrowth into the network structure as the one or more hydrogels and / or one or more water-soluble polymers degrade. The continuous pathways also allow for coating of the entire macroporous network structure with one or more of the following: cells, stem cells, fat cells, adipose cells, tissue, collagen, additives, and bioactive agents.

[0189]

[0219] For example, a macroporous network with a low infill density, less than 60%, or between 5 and 25%, is preferred as it provides more void space for tissue ingrowth.

[0190]

[0220] In embodiments, the implant is fabricated with a coating and / or some or all of the reinforcing matrix or macroporous network is used as a carrier. For example, the macroporous network can be fabricated by placing one or more of the following into some or all of the void spaces of the macroporous network: cells and tissues, such as autograft, allograft or xenograft tissues and cells, and vascular pedicles. Examples of cells that can be inserted into the void spaces of the macroporous network of the implant and coated on the surface of the network include adipocytes, fibroblasts, and stem cells. In embodiments, vascular pedicles can be inserted into the void spaces of the macroporous network of the implant. In embodiments, the implant can be partially or entirely coated with one or more bioactive agents. Particularly preferred bioactive agents that can be coated on the macroporous network of the implant include collagen and hyaluronic acid or derivatives thereof. In other embodiments, the implant or the macroporous network of the implant can be coated with one or more antibiotics.

[0191]

[0221] IV. Methods for Implanting Implants

[0222] In an embodiment, the implant is implanted into the body. Preferably, the implant is implanted into a site of reconstruction, remodeling, repair, and / or regeneration. In a preferred embodiment, the implant is implanted into the breast of a patient. In a preferred embodiment, the connective tissue and / or vasculature infiltrates into the macroporous network of the implant after implantation as the hydrogel(s) and / or water-soluble polymer(s) degrade. In a particularly preferred embodiment, the implant comprises a resorbable material, and the connective tissue and / or vasculature also infiltrates into the space where the hydrogel and / or water-soluble polymer(s) degrade (and eventually the macroporous network is resorbed). The pores of the macroporous network can be colonized by cells before implantation or, more preferably, after implantation, and the pores of the macroporous network of the implant are infiltrated by tissue, blood vessels, or a combination thereof.

[0192]

[0223] The macroporous network of the implant may be coated or filled with transplant cells, stem cells, fibroblasts, adipocytes, and / or tissues before or after implantation. In an embodiment, the macroporous network of the implant is coated with differentiated cells before or after implantation. Differentiated cells have a specific morphology and function. An example is adipocytes. In an embodiment, the macroporous network of the implant is loaded with cells by injection before or after implantation, and preferably by using a needle that does not damage the macroporous network of the implant. The macroporous network of the implant may also be coated or filled with platelets, extracellular adipose matrix proteins, gels, hydrogels, water-soluble polymers, and bioactive agents before implantation. In an embodiment, the macroporous network of the implant may be coated with antibiotics before implantation, for example, by dipping the implant in a solution of antibiotics.

[0193]

[0224] The implants can be used to deliver autologous cells and tissue to the patient's breast. The autologous tissue is preferably one or more of the following: autologous fat, lipoaspirate, injectable fat, adipocytes, fibroblasts, and stem cells.

[0194]

[0225] The implant may be used to deliver adipose tissue into the patient's body. In a particularly preferred embodiment, autologous adipose tissue is prepared before or after implantation of the implant and injected or otherwise inserted into or coated on the macroporous network of the implant before or after implantation of the implant. The autologous adipose tissue is preferably prepared by liposuction at a donor site on the patient's body. After centrifugation, the lipid phase containing the adipocytes is separated from the blood components and combined with the macroporous network of the implant before implantation or injected or otherwise inserted into the macroporous network of the implant after implantation. In an embodiment, the macroporous network of the implant is injected or filled with a volume of lipoaspirate representing 1% to 50% of the total volume of the macroporous network, and more preferably 1% to 20% of the total volume of the macroporous network.

[0195]

[0226] In another embodiment, lipoaspirate adipose tissue taken from a patient can be mixed with a biological or synthetic matrix, such as ultrafine fibers or very small particles, prior to adding the lipoaspirate to the macroporous network of the implant. In this embodiment, the added matrix serves to hold or bind the micro fat globules and to keep them dispersed within the macroporous network of the implant. In some embodiments, the use of an added matrix can help prevent fat pooling that can lead to necrosis and / or help increase vascularization of the implant.

[0196]

[0227] In another embodiment, a vascular pedicle or other tissue mass is harvested from a patient and inserted into the implant. The pedicle or other tissue mass may be inserted into the implant prior to implantation of the implant, and then the implant with the pedicle or other tissue mass may be implanted into the patient, or the pedicle or other tissue mass may be inserted into the implant after the implant has been implanted into the patient.

[0197]

[0228] In some embodiments, the implants are implanted and secured in both breasts. In some embodiments, the implants are implanted in patients during mastopexy and augmentation procedures, such as revision procedures. In some particularly preferred embodiments, the implants are implanted in patients who: (i) have had a mastectomy; (ii) have had a breast lift and need augmentation; (iii) have had a breast reduction and need support, lift or remodeling of the reduced breast; or (iv) have had a previous silicone or saline breast implant procedure and want to remove the silicone or saline implant and provide a fuller or larger breast size with subsequent breast reconstruction. Implants may also be implanted in breast surgery patients to add additional fat graft volume to the implant to increase the breast rise away from the chest and, optionally, to increase the rise after implantation. The additional fat graft volume may be added to the implant immediately after implantation, but may also be added at follow-up visits. For example, the additional fat graft volume may be added to the implant on one or more occasions within days, weeks or months of implantation. The procedures described herein may be performed by removal of breast tissue, excision, and redistribution of breast tissue.

[0198]

[0229] In an embodiment, a method for implanting an implant in a breast includes at least: (i) making at least one incision to access the patient's breast tissue, (ii) separating the skin and subcutaneous fascia from the breast bulge in the chest, (iii) positioning the implant in the breast bulge in the chest, (iv) securing the implant to the tissue surrounding the breast bulge in the chest, and (v) closing the breast incision. The method may further include one or more of the following steps: (a) preparing a sample of lipoaspirate and coating or filling the implant with the sample before implantation of the implant, (b) preparing a sample of lipoaspirate and coating or filling the implant with the sample after implantation of the implant, preferably by injecting the sample into the implant, (c) inserting a vascular pedicle into the implant before or after implantation of the implant, and (d) suturing or stapling the implant in place. In a preferred embodiment, the implant is implanted in a subglandular, subpectoral, or prepectoral position. In an embodiment, the implant is sutured to the tissue surrounding the breast fullness, and even more preferably to the fascia surrounding the pectoral muscle underlying the breast fullness, hi another embodiment, the implant includes tabs, which are sutured to the tissue surrounding the breast fullness.

[0199]

[0230] The reinforcing matrix or macroporous network of the implant may also be coated or filled with cells and tissues other than fat grafts, as well as with cytokines, platelets and extracellular fat matrix proteins, before or after implantation. For example, the reinforcing matrix or macroporous network of the implant may be coated or filled with cartilage or dermal grafts. The macroporous network of the implant may also be coated or filled with other tissue cells, such as stem cells genetically engineered to contain genes to treat a patient's disease.

[0200]

[0231] In certain embodiments, the implant has properties that allow it to be delivered by minimally invasive means, through a small incision. The implant can be designed, for example, to be rolled, folded, or compressed to allow it to be delivered through a small incision. This minimally invasive approach can reduce patient mortality, scarring, and the chance of infection. In embodiments, the implant has a three-dimensional shape and shape memory properties that allow it to assume its original three-dimensional shape unaided after being delivered through an incision into a properly sized dissected tissue plane. For example, the implant can be temporarily deformed by rolling into a small diameter cylindrical shape that is delivered using an inserter, and then allows it to resume its original three-dimensional shape unaided in vivo. In embodiments, the implant is compressible and can be delivered into the breast through a funnel, such as a Keller funnel. In embodiments, the implant can be delivered into the breast through a funnel with a neck diameter (narrowest part of the funnel) of 1 to 3 inches, and more preferably 1.5 to 2.5 inches. In embodiments, the implant can be delivered through a funnel with a neck diameter of 1-3 inches, and at least 70% of the implant's volume can be restored after delivery through the neck of the funnel and into the breast. In embodiments, the implant has a compressive modulus that allows the implant to be delivered through a funnel with a neck diameter of 1-3 inches, and the implant can be restored to at least 70% of the implant's volume after passing through the neck of the funnel.

Claims

1. 1. A breast implant comprising a reinforcing matrix, the implant comprising a surface, a core, a posterior section for placement against a patient's chest wall, an anterior section opposite the posterior section, the anterior section comprising an anterior bottom portion for placement in a lower pole of the breast, an anterior top portion for placement in an upper pole of the breast, and an anterior middle region for placement under the patient's skin, and the reinforcing matrix comprises a load-bearing macroporous network with an open cell structure that is at least partially filled with one or more degradable hydrogels, degradable water soluble polymers, or combinations thereof.

2. 2. The implant of claim 1, wherein the reinforcing matrix comprises a first hydrogel and a second hydrogel, with the second hydrogel surrounding the first hydrogel, or the reinforcing matrix comprises a first water soluble polymer and a second water soluble polymer, with the second water soluble polymer surrounding the first water soluble polymer, or the reinforcing matrix comprises a first hydrogel and a second water soluble polymer, with the first hydrogel surrounding the second water soluble polymer or the second water soluble polymer surrounding the first hydrogel.

3. 3. The implant of claim 2, wherein the reinforcing matrix comprises a first hydrogel and a second hydrogel, and the second hydrogel degrades in vivo faster than the first hydrogel, or the reinforcing matrix comprises a first water-soluble polymer and a second water-soluble polymer, and the second water-soluble polymer degrades in vivo faster than the first water-soluble polymer, or the reinforcing matrix comprises a first hydrogel and a second water-soluble polymer, and one of the first hydrogel and the second water-soluble polymer degrades faster than the other of the first hydrogel and the second water-soluble polymer.

4. 4. The implant of claim 3, wherein the reinforcing matrix comprises a first hydrogel and a second hydrogel, the implant further comprising a third hydrogel, the second hydrogel being surrounded by the third hydrogel, and the third hydrogel degrading in vivo faster than the second hydrogel.

5. 10. The implant of claim 1, wherein the load-bearing macroporous network has one or more of the following properties: a compressive strength of at least 0.1 kgf at 30% strain, a compressive modulus of 0.1 kPa to 10 MPa at 5-15% strain, and a loss modulus of 0.3 to 100 kPa.

6. 10. The implant of claim 1, wherein the implant has a teardrop shape, an anatomical shape, a rounded shape, a dome-like shape, or the anterior bottom of the implant has a convex outer surface.

7. The implant of claim 1 , further comprising an opening for inserting tissue into the implant.

8. The implant of claim 1 , further comprising an outer shell surrounding the reinforcing matrix.

9. The implant of claim 1 , further comprising one or more anchors, fasteners, or tabs for securing the implant within the breast.

10. The implant of claim 1 , wherein the load-bearing macroporous network is degradable or comprises one or more absorbable polymers.

11. 11. The implant of claim 10, wherein the one or more absorbable polymers comprise or are made from one or more monomers selected from the group consisting of glycolide, lactide, glycolic acid, lactic acid, 1,4-dioxanone, trimethylene carbonate, 3-hydroxybutyric acid, 3-hydroxybutyrate, 3-hydroxyhexanoate, 3-hydroxyoctanoate, 4-hydroxybutyric acid, 4-hydroxybutyrate, ε-caprolactone, 1,4-butanediol, 1,3-propanediol, ethylene glycol, glutaric acid, malic acid, malonic acid, oxalic acid, succinic acid, and adipic acid, or the polymer composition comprises poly-4-hydroxybutyrate or a copolymer thereof, or poly(butylene succinate) or a copolymer thereof.

12. The implant of claim 1 , wherein the load-bearing macroporous network comprises filaments, fibers, struts, textiles, nonwovens, foams, laminates, or phase-separated or particle-infused structures.

13. 13. The implant of claim 12, wherein the filaments, fibers or struts have one of the following properties: tensile strength greater than 25 MPa, tensile modulus less than 300 MPa, elongation at break greater than 100%, melting temperature greater than or equal to 60°C, glass transition temperature less than 0°C, average diameter or width between 10 μm and 5 mm, breaking load between 0.1 and 200 N, and modulus of elasticity between 0.05 and 1,000 MPa.

14. The implant of claim 12 , wherein the load-bearing microporous network is resorbable.

15. The implant of claim 1 , wherein one or more of the degradable hydrogels or one or more of the water-soluble polymers degrade faster than the load-bearing macroporous network with an open cell structure.

16. 2. The implant of claim 1, wherein the load-bearing macroporous network with an open cell structure comprises unit cells selected from one or more of the following shapes: (i) tetrahedron, cuboid, pentahedron, hexahedron, heptahedron, octahedron, icosahedron, decahedron, dodecahedron, tetradecahedron, and prisms, antiprisms, and truncated polyhedrons thereof; (ii) elongated polyhedrons; (iii) shapes with 4, 6, 8, 12, or 20 faces; and (iv) rhombic dodecahedron.

17. 10. The implant of claim 1, further comprising autologous fat, lipoaspirate, injectable fat, adipocytes, fibroblasts, stem cells, hyaluronic acid, collagen, antimicrobials, antibiotics, bioactive agents, and diagnostic devices.

18. 13. A method for producing the breast implant of claim 1, wherein the load-bearing macroporous network with an open cell structure is produced by 3D printing a polymer composition to form a macroporous network of filaments.

19. 20. The method of claim 18, wherein the macroporous network comprises unit cells, the unit cells being selected from one or more of the following shapes: (i) tetrahedrons, cuboids, pentahedrons, hexahedrons, heptahedrons, octahedrons, icosahedrons, decahedrons, dodecahedrons, tetradecahedrons, and prisms, antiprisms, and truncated polyhedra; (ii) elongated polyhedrons; (iii) shapes with 4, 6, 8, 12, or 20 faces; and (iv) rhombic dodecahedrons.

20. 20. The method of claim 18, further comprising placing at least one of a first hydrogel or a first water-soluble polymer in the macroporous network.

21. 21. The method of claim 20, further comprising disposing at least one of a second hydrogel or a second water soluble polymer in the macroporous network such that the second hydrogel or the second water soluble polymer surrounds the first hydrogel or the first water soluble polymer, and optionally disposing at least one of a third hydrogel or a third water soluble polymer in the macroporous network such that the third hydrogel or the third water soluble polymer surrounds the second hydrogel or the second water soluble polymer.

22. 20. The method of claim 18, wherein the macroporous network of filaments is formed by extrusion-based additive manufacturing, selective laser melting, fused deposition modeling, fused filament fabrication, melt extrusion deposition, printing of a polymer slurry or solution using a coagulation bath, and printing using a binding solution and polymer powder granules.

23. 20. The method of claim 18, wherein the implant is formed using a 3D printer comprising two or more print heads, wherein the load-bearing macroporous network comprising an open cell structure is formed by using a first print head to print the network from a polymer composition, and a second print head is used to print at least one of a first hydrogel or a first water-soluble polymer to be located within the macroporous network.

24. 24. The method of claim 23, wherein the 3D printer includes a third print head, the third print head being used to print at least one of a second hydrogel or a second water soluble polymer within the macroporous network and surrounding the first hydrogel or the first water soluble polymer.

25. 25. The method of claim 24, wherein the implant is formed using solution-based or slurry-based printing to print the first and second hydrogels or first and second water-soluble polymers.

26. 26. The method of any one of claims 18 to 25, wherein the macroporous network has one or more of the following properties: compressive strength of at least 0.1 kgf at 30% strain, compressive modulus of 0.1 kPa to 10 MPa at 5 to 15% strain, and loss modulus of 0.3 to 100 kPa.

27. 13. A method of implanting the implant of claim 1 into a breast, comprising the steps of: (i) making at least one incision to access breast tissue of a patient; (ii) separating the skin and subcutaneous fascia from the breast volume in the chest; (iii) positioning the implant subglandularly, subpectorally, or subfascially; (iv) securing the implant to nearby tissue; and (v) closing the incision in the breast.

28. 28. The method of claim 27, further comprising coating or injecting one or more of the following into the implant either prior to implantation of the implant into the patient's body or after implantation of the implant into the patient's body: autologous fat, lipoaspirate, injectable fat, adipocytes, fibroblasts, stem cells, gels, hydrogels, hyaluronic acid or derivatives thereof, collagen, antimicrobial agents, antibiotics, and bioactive agents on one or more occasions either prior to implantation of the implant into the patient's body or after implantation of the implant into the patient's body.

29. 28. The method of claim 27, further comprising inserting a vascular pedicle or other tissue mass into the implant.

30. An implant comprising a reinforced macroporous network as described herein.

31. A method of producing an implant comprising a macroporous reinforcing network as described herein.

32. 1. A breast implant comprising: a reinforced macroporous network defining a plurality of interconnected voids; and a first set of sacrificial void occupants adapted to temporarily occupy the first set of voids until tissue grows therein, said first set of sacrificial void occupants being formed of at least one of a hydrogel, a water soluble polymer, or a combination thereof.

33. 33. The breast implant of claim 32, further comprising a second set of voids disposed surrounding the first set of voids and a second set of sacrificial void occupants adapted to temporarily occupy the second set of voids until tissue has grown therein, the second set of void occupants being resorbable prior to the first set of void occupants.

34. 34. The breast implant of claim 33, wherein the first set of sacrificial void occupants is a first hydrogel.

35. 35. The breast implant of claim 34, wherein the first and second sets of sacrificial void occupants and the macroporous network are fabricated and arranged together to form the implant by 3D printing.

36. 35. The breast implant of claim 34, wherein the second set of sacrificial void occupants is a second hydrogel.

37. 37. The breast implant of claim 36, wherein the second set of sacrificial void occupants are absorbed before the first set of void occupants and the macroporous network completely degrades after the first set of void occupants have degraded.

38. 40. The breast implant of claim 37, wherein the first set of void occupants are absorbed within one year of implantation within the breast.

39. 13. A method of implanting the implant of claim 1 into a breast, comprising delivering the implant into the breast through a funnel.

40. 1. A breast implant comprising a reinforcing matrix, the implant including a surface, a core, a posterior section for placement against a patient's chest wall, an anterior section opposite the posterior section, the anterior section including an anterior bottom section for placement in a lower pole of the breast, an anterior top section for placement in an upper pole of the breast, and an anterior middle section for placement under the patient's skin, the reinforcing matrix comprising a load-bearing macroporous network with an open cell structure, the reinforcing matrix including at least a first hydrogel or a first water-soluble polymer, and at least a second hydrogel or a second water-soluble polymer, the second hydrogel or the second water-soluble polymer surrounding the first hydrogel or the water-soluble polymer except for the posterior section of the implant.

41. 41. The breast implant of claim 40, wherein the first hydrogel or first water soluble polymer comprises a first hydrogel and the second hydrogel or water soluble polymer comprises a second water soluble polymer.

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