Artificial ligament

Abstract

The invention belongs to the technical field of medical materials, and relates to an artificial ligament which is of a round bar structure, the round bar structure forms a first bone tunnel weaving part, an intra-articular free silk part and a second bone tunnel weaving part which are sequentially connected in the axial direction, the round bar structure comprises warp and weft, the warp extends in the axial direction of the round bar structure, and the weft extends in the axial direction of the round bar structure. The warp yarns extend in the circumferential direction of the round bar structure, the weft yarns extend in the circumferential direction of the round bar structure, the first bone tunnel weaving part and the second bone tunnel weaving part both comprise the warp yarns and the weft yarns, and the intra-joint free silk part only comprises the warp yarns; the first bone tunnel weaving part and the second bone tunnel weaving part are provided with penetrating channels perpendicular to the axial direction, the warp yarns are divided into two types, namely sewing threads and multifilaments, and the channels are communicated through through holes formed by breaking the multifilaments. The artificial ligament has mechanical uniformity, flexibility and biocompatibility, is easy to process, and can resist fatigue and stabilize joints under physiological load.

Description

Technical Field

[0001] This invention belongs to the field of medical materials technology and relates to an artificial ligament. Background Technology

[0002] In the medical field, ligament repair and reconstruction has always been a crucial research area, significant for restoring normal joint function and improving patients' quality of life. Artificial ligaments, as an important means of ligament repair and reconstruction, directly affect the effectiveness of clinical applications due to their performance.

[0003] While commercially available artificial ligaments can meet some clinical needs to a certain extent, many problems still need to be solved. Taking the hybrid artificial ligament and its manufacturing method disclosed in patent CN107970081B as an example, this hybrid artificial ligament includes a cylindrical structure, which is sequentially connected along the axial direction to a first bone tunnel braid, an intra-articular free wire, and a second bone tunnel braid. The cylindrical structure is composed of warp and weft yarns, with multiple weft yarns including a first weft yarn made of a biodegradable material and a second weft yarn made of a non-degradable material. Both the first and second bone tunnel braids contain warp and weft yarns, while the intra-articular free wire contains only weft yarns. This design results in the ligament material being composed of both biodegradable and non-degradable parts. During the degradation process, the surrounding tissue of the biodegradable material attaches to the graft, and the ligament tissue itself grows and ascends into the graft, while the non-degradable material provides permanent mechanical strength support. However, this hybrid artificial ligament still faces the challenge of difficulty in bone ingrowth in practical applications.

[0004] When addressing the challenge of bone ingrowth, perforation of ligaments is often necessary, but this is where problems arise. Traditional ligaments, especially those made of multifilament fibers, have warp fibers entirely composed of multifilaments. During perforation, the cutting action of the blade directly causes the warp fibers to break. As a crucial component of the ligament structure, the breakage of the warp fibers not only disrupts the original structural integrity of the ligament but also severely impacts its structural strength. In medical applications, ligaments need sufficient strength to withstand various stresses generated during bodily movement, thereby maintaining joint stability and normal function. For example, the anterior cruciate ligament (ACL) in the knee joint plays a vital role in limiting excessive anterior tibial displacement. If perforation damages the ligament's strength, the ACL will be unable to effectively maintain normal knee joint movement, leading to symptoms such as joint instability and pain, severely impacting the patient's quality of life and athletic ability. Therefore, it is evident that the performance of traditional multifilament fiber ligaments after perforation cannot meet the stringent medical requirements for ligament strength and stability, necessitating a new design solution to address this challenge.

[0005] To address the issue of reduced strength after fabric is perforated, existing technologies have proposed five types of solutions.

[0006] The first category is material modification methods (e.g., patent application CN119615492A), which mainly include three aspects: fiber material modification, polymer matrix reinforcement, and surface treatment technology. Regarding fiber material modification, related patented technologies improve the performance after perforation by enhancing the strength and toughness of the fiber itself. For example, technologies such as carbon fiber reinforcement or nano-coating are used to improve fiber performance, aiming to enhance the strength of the fabric after perforation.

[0007] The second category is structural design optimization methods (such as patent US10611131B2), which reduce strength loss by improving the design of the perforation pattern, hole structure, and distribution. These methods cover aspects such as hole design, arrangement optimization, and multi-layer structure design. For example, by carefully designing the hole shape and arrangement, the stress distribution can be made more uniform, thereby reducing the impact of perforation on the overall structural strength.

[0008] The third category is process technology improvement methods (e.g., patent application CN118492612A), which cover improvements to the drilling process itself and optimization of post-processing. These methods reduce strength loss during processing through technological innovation, including buffer protection technology, laser-ultrasonic coupling technology, and thermal fusion reinforcement technology. For example, buffer protection technology can reduce impact on the material during drilling, or thermal fusion reinforcement technology can be used to reinforce the drilling edges.

[0009] The fourth category is reinforcement techniques, which restore or enhance strength by adding reinforcing materials to or around the perforated area. These mainly include coating reinforcement, fiber reinforcement, fabric reinforcement, and structural reinforcement. Among these, fabric reinforcement enhances strength by attaching reinforcing materials to the perforated area. For example, to reinforce the perforated area of ​​the facing fabric, non-woven fabric is bonded to the surface of the facing fabric, and a reinforcing component is placed externally. A locking component is installed at the bottom of the reinforcing component via a connecting component, thus securing the reinforcing component to the wrapping between the facing fabric and the non-woven fabric, thereby reinforcing the perforated area of ​​both the non-woven fabric and the facing fabric.

[0010] The fifth category is composite material application methods (e.g., patent application CN11915834A), which solve strength problems through multi-layer composite structures, including laminated structures, sandwich structures, and gradient materials. Specific examples include fiber composites, metal-composite materials, multi-layer composite structures, and ceramic-coated composites. By combining different materials, the advantages of each material are leveraged to improve the overall strength and performance of the structure.

[0011] However, these existing methods all have significant shortcomings in addressing the problems associated with perforation of artificial ligaments. While some methods are theoretically feasible, they cannot be effectively implemented in practice due to the unique medical application environment and performance requirements of artificial ligaments. For example, some material modification methods may use materials that do not meet medical biocompatibility standards or cannot exist stably in the human body; some process improvement methods are difficult to operate precisely on the small size and complex structure of artificial ligaments. Even if some methods can be implemented, factors such as material properties, process complexity, and cost may prevent them from simultaneously meeting the stringent requirements of artificial ligaments regarding biocompatibility, mechanical properties, and post-perforation strength maintenance. For example, some reinforcement techniques may affect the flexibility and biocompatibility of the ligament, or the application of composite materials may result in excessively high costs, hindering widespread clinical application.

[0012] Therefore, it is necessary to develop a new artificial ligament perforation solution to overcome the shortcomings of existing technologies and meet the actual needs of clinical medicine. Summary of the Invention

[0013] The purpose of this invention is to solve the problems existing in the prior art and to provide an artificial ligament.

[0014] To achieve the above objectives, the technical solution adopted by the present invention is as follows:

[0015] An artificial ligament has a cylindrical rod structure. The cylindrical rod structure forms a first bone tunnel braid, an intra-articular free yarn, and a second bone tunnel braid connected sequentially along the axial direction. The cylindrical rod structure includes warp yarns and weft yarns. The warp yarns extend along the axial direction of the cylindrical rod structure, and the weft yarns extend along the circumferential direction of the cylindrical rod structure. Both the first and second bone tunnel braids contain the warp yarns and the weft yarns, while the intra-articular free yarn contains only the warp yarns.

[0016] Both the first bone tunnel braid and the second bone tunnel braid are provided with through channels, and the extension direction of the channels is perpendicular to the axial direction of the round bar structure;

[0017] The channel is formed by multiple through holes;

[0018] There are two types of warp yarns: non-absorbable thread and multifilament yarn. The breaking strength of a single thread is 140-720N. The through-hole is formed by the breakage of a portion of the multifilament yarn.

[0019] The weft yarn is multifilament.

[0020] Ligaments, as crucial structures for joint stability, need to maintain stable shape and size during long-term joint activities (such as knee flexion, extension, and rotation). If the weft yarn is sewn thread instead of multifilament, the following problems will arise:

[0021] (1) The suture itself has a loose structure and is prone to "unraveling".

[0022] Sutures are made up of multiple fine fibers interwoven together. Their structure relies on the friction between fibers to maintain its integrity, rather than being an integrated structure (such as the bundle structure of monofilaments and multifilaments). When the weft yarn interweaves with the warp yarn, if it is subjected to repeated pulling or friction during joint movement, the suture fibers are prone to slippage and separation, leading to a "straw unraveling" phenomenon. Ultimately, the interlacing point of the warp and weft yarns loses its fixation, the warp yarn is prone to lateral displacement, the overall shape of the ligament becomes distorted, and it cannot conform to the joint anatomy, thus affecting the joint movement trajectory and increasing the risk.

[0023] (2) The mechanical properties are substandard, unable to withstand physiological stress, and prone to failure.

[0024] Poor weaving uniformity and localized structural weakness make it difficult to precisely control the thickness and weaving density of the threads compared to multifilament yarns. When used as weft yarns, this can easily lead to "too loose" or "too tight" areas in ligaments. Too loose areas result in increased warp spacing, reducing the ligament's resistance to lateral deformation and making it prone to localized indentation under stress. Too tight areas can cause uneven thickness due to fiber accumulation, potentially compressing surrounding tissues (such as the synovium of joints) and triggering inflammation. When the ligament is subjected to longitudinal tensile force, the weft yarn's "lateral constraint" on the warp yarn is insufficient, leading to localized overstretching of the warp yarn. This stress concentration near weak points in the weft yarn can cause premature ligament rupture.

[0025] (3) Poor processing adaptability hinders key operations (such as drilling) and affects clinical application.

[0026] If the weft yarn is sewing thread, it will further increase the difficulty of the punching process, and the punched edges are prone to loosening. The thermal effect of laser punching will melt the fiber interlacing points of the sewing thread, causing the sewing thread to "unravel". A large number of free fibers will appear at the punched edge. The shearing force of punching will directly tear the sewing thread, causing the weft yarn in the punched area to lose its restraint on the warp yarn. The warp yarn is prone to shift and gather towards the punched area, resulting in hole deformation (such as enlarged hole diameter and irregular hole walls).

[0027] The part of an artificial ligament most prone to rupture is the intra-articular free filament section, which contains only the warp yarns. There are two types of warp yarns: the suture thread and the multifilament thread. The suture thread has high strength. When punching holes, only some of the multifilament threads in the warp yarns are controlled to break, avoiding the breakage of the suture thread in the warp yarns, which is the core mechanical structure. Therefore, the intra-articular free filament section has excellent mechanical properties.

[0028] As a preferred technical solution:

[0029] The artificial ligament described above has a single suture with a breaking strength of 183-600 N.

[0030] As described above, the artificial ligament has a channel with a pore size of 300-600 μm. Studies have shown that in additively manufactured bone implants, a pore size of 300-600 μm can promote osteoblast proliferation (increasing bone ingrowth by 35%).

[0031] As described above, the pore size of the channel in an artificial ligament is 300-500 μm.

[0032] As described above, in an artificial ligament, the channel intersects the central axis of the cylindrical structure.

[0033] In the artificial ligament described above, the channels in the first bone tunnel braid are referred to as the first group of channels, and the channels in the second bone tunnel braid are referred to as the second group of channels; in the first group of channels or the second group of channels, the channels are distributed on at least two layers perpendicular to the axial direction of the cylindrical structure.

[0034] In the artificial ligament described above, in either the first or second group of channels, the spacing between two adjacent layers along the axial direction of the cylindrical structure is 1-3 mm. This spacing setting has significant advantages, as detailed below:

[0035] (1) It helps to avoid the breakage of the "weak zone" between the holes and preserve the overall strength of the ligament: The fabric area between the channels (which are formed by the through holes) (can be called the "inter-hole bridge") is the key to maintaining the integrity of the local structure. A spacing of 1-3mm can ensure that the "inter-hole bridge" has sufficient mechanical redundancy. The warp yarn is the core force-bearing body of the ligament (multifilament is responsible for the perforation, and the suture is responsible for the strength). This spacing can allow a sufficient number of complete multifilaments (or fabric structures that have not been damaged by the laser) to be retained between adjacent channels, which significantly reduces the risk of tearing from the holes when under stress. If a spacing of less than 1mm is selected, the amount of multifilament residue may be insufficient, the mechanical support effect of the inter-hole area may be weakened, and the degree of optimization of the structural stability during tension will be reduced. If a spacing of more than 3mm is selected, although the strength of the inter-hole bridge can basically meet the basic requirements, the density of the channels in the row may be low, and the optimization space of the clinical fixation effect will be reduced accordingly.

[0036] (2) It can promote bone-ligament integration and improve long-term stability after implantation: When the spacing is selected as 1-3mm, the bone tissue between the holes can more easily obtain sufficient blood supply, which is conducive to the ingrowth of fibrocartilage into the channel (forming "bone-ligament integration"). It can also reduce the compression interference that may be caused to the bone tissue due to the holes being too dense, or the problem of reduced tissue ingrowth efficiency due to the holes being too wide, thereby helping to improve the integration stability between the implant and the bone tissue. If the spacing is less than 1mm, the hole distribution is relatively dense, which may have a slight impact on the local blood supply of the bone tissue, and the smoothness of tissue healing may be affected to some extent. If the spacing is greater than 3mm, the area between the holes is relatively open, and the coverage of tissue ingrowth may not be comprehensive enough. The degree of optimization of the bone-ligament integration effect may not be as good as that of the spacing range.

[0037] (3) It can be adapted to laser processing technology and reduce the adverse effects of thermal effects: The through holes of ligaments are processed by laser (high precision and no mechanical damage), but the laser will generate a heat-affected zone (HAZ, i.e. the area around the hole that is slightly melted by high temperature). A spacing of 1-3mm can effectively reduce the probability of overlapping heat-affected zones. The width of the heat-affected zone of laser drilling is about 0.3-0.5mm. This spacing can make it easier for the heat-affected zones of adjacent channels to avoid each other, reducing the situation of excessive melting and adhesion of multifilaments (avoiding the adverse effects of rough hole walls on suture passage and tissue ingrowth). At the same time, it can reduce the potential interference of heat diffusion on surrounding sutures, which helps to ensure the structural integrity and mechanical properties of the ligament after processing. If the spacing is less than 1mm, the risk of overlapping heat-affected zones of two holes will increase slightly, the probability of multifilament melting and adhesion and rough hole walls may increase, and the effect of heat diffusion on surrounding sutures may also be apparent, but it does not necessarily lead to processing failure. If the spacing is greater than 3mm, although the risk of overlapping heat-affected zones can be completely avoided, the density efficiency of channel processing may decrease, making it difficult to give full play to the precision advantages of laser processing.

[0038] As described above, an artificial ligament is provided, wherein the cylindrical structure is fabricated from a fabric with the through holes, and the fabrication process includes sequential winding around a rotation axis and sewing it in place with a hook needle or sewing needle; the rotation axis is parallel to the warp direction of the fabric; the two ends of the fabric along its width direction are respectively referred to as end a and end b;

[0039] The winding refers to winding the fabric from end a to end b around the rotation axis;

[0040] Alternatively, the winding refers to winding the fabric from end a towards the middle around the rotation axis, while simultaneously winding the fabric from end b towards the middle; the processing steps also include a die-casting operation between the winding operation around the rotation axis and the sewing and fixing operation.

[0041] As described above, the artificial ligament has a warp density of 90-110 threads / 10cm and a weft density of 65-85 threads / 10cm.

[0042] As described above, in an artificial ligament, the first bone tunnel braid is composed of a first non-channel region and a first channel region arranged sequentially along the axial direction of the cylindrical bar structure, and the second bone tunnel braid is composed of a second non-channel region and a second channel region arranged sequentially along the axial direction of the cylindrical bar structure. The first non-channel region, the first channel region, the intra-articular free wire portion, the second channel region, and the second non-channel region are connected sequentially.

[0043] As described above, in an artificial ligament, the diameter of the round rod structure is 7.5-9.5 mm; the length of the first bone tunnel braid or the second bone tunnel braid is 16-17.5 cm; the length of the first channeled region or the second channeled region does not exceed 6 cm; and the length of the intra-articular free wire is 20-30 mm.

[0044] As described above, in an artificial ligament, the multifilament is composed of 12-36 single yarns joined together, the specification of the multifilament is 1800-2500D (suitable for artificial ligaments), the single yarn is FDY yarn, and the material is high molecular weight polyethylene (UHMWPE), polyethylene terephthalate (PET), polyether ether ketone (PEEK) or carbon fiber.

[0045] As described in any of the preceding claims, the artificial ligament has a tensile strength of 5211-6478 N and an ultimate strain of 4.6%-9.0%. After being subjected to a tensile force of 300-1700 N for 24 hours, the artificial ligament exhibits a deformation rate of <1.2%, which is negligible, indicating that the ligament is not prone to permanent deformation under long-term stress and demonstrates outstanding fatigue stability. Furthermore, the artificial ligament maintains low deformation characteristics under a test tensile force of 300 N-1700 N, while the mechanical load of daily human activities (67 N-630 N, covering typical scenarios such as climbing stairs, descending stairs, and jogging) is entirely within the safe range of this test, further verifying the fatigue stability of the artificial ligament under physiological conditions.

[0046] Beneficial effects:

[0047] (1) The present invention solves the problem of difficult bone ingrowth in traditional artificial ligaments by setting through channels in the first bone tunnel braiding part and the second bone tunnel braiding part. At the same time, by controlling the warp yarn to be composed of sutures and multifilaments, only the multifilaments are broken during punching, and the sutures that serve as the core mechanical structure are retained. This avoids the strength collapse caused by warp yarn breakage after punching the traditional ligament, and ensures the structural integrity and core mechanical properties of the artificial ligament after punching.

[0048] (2) The present invention achieves the characteristics of "rigidity and flexibility" of artificial ligament by using sutures to provide core mechanical support and multifilaments to enhance flexibility and tissue compatibility. This ensures core mechanical performance and improves compatibility and biocompatibility with tissues in the body, thus meeting the medical application requirements of artificial ligament.

[0049] (3) The present invention controls the laser perforation to act only on the multifilament area without damaging the suture, taking into account the processing feasibility and accuracy of the perforation operation, and avoiding the damage to the core stress structure caused by improper perforation position.

[0050] (4) The artificial ligament of the present invention can maintain low deformation characteristics within the mechanical load range corresponding to physiological working conditions, and has outstanding fatigue stability, avoiding permanent deformation under long-term stress, and ensuring the long-term stability and normal function of the joint. Attached Figure Description

[0051] Figure 1 and Figure 2 This is a schematic diagram of the winding scheme 2 of the present invention;

[0052] Figure 3 Three-dimensional model diagrams of the artificial ligament channel openings (corresponding to embodiments 1, 9, 17, and 25);

[0053] Figure 4 The diagram shows the distribution of the artificial ligament channel holes (corresponding to Examples 1, 9, 17, and 25); the lengths of each segment in the diagram are: a=1.87mm, b=3.44mm, c=5.04mm, d=6.57mm, e=8.13mm, f=9.70mm, and g=11.26mm.

[0054] Figure 5 Image of the artificial ligament fabric after laser perforation;

[0055] Figures 6(a) and 6(b) are schematic diagrams of the structures of two types of artificial ligaments (where 1-first region without channels, 2-first region with channels, 3-intra-articular free wire, 4-second region with channels, 5-second region without channels, 6-first group of channels, 7-second group of channels).

[0056] Figure 7Three-dimensional model diagram of the artificial ligament channel opening (corresponding to embodiments 3, 11, 19, and 27);

[0057] Figure 8 The diagram shows the distribution of the artificial ligament channel holes (corresponding to Examples 3, 11, 19, and 27); the lengths of each segment in the diagram are as follows: a1=1.87mm, b1=3.44mm, c1=5.04mm, d1=6.57mm, a2=1.87mm, b2=3.44mm, c2=5.04mm, d2=6.57mm;

[0058] Figure 9 Three-dimensional model diagrams of the artificial ligament channel openings (corresponding to embodiments 5, 13, 21, and 29);

[0059] Figure 10 The diagram shows the distribution of the artificial ligament channel openings (corresponding to Examples 5, 13, 21, and 29); the lengths of each segment in the diagram are as follows: a=0.45mm, b=0.64mm, c=0.81mm, d=0.99mm, e=1.15mm, f=1.33mm, g=1.50mm, h=1.69mm, i=1.86mm, j=2.04mm, k=2.20mm, l=2.38mm, m=2.55mm, n=2.74mm, o=2.90mm, p=3.08mm, q=3.25mm, r=3.43mm, s=3.60mm, t=3.78mm;

[0060] Figures 11(a) and 11(b) are schematic diagrams of the structures of two other types of artificial ligaments;

[0061] Figure 12 Three-dimensional model diagrams of the artificial ligament channel openings (corresponding to embodiments 7, 15, 23, and 31);

[0062] Figure 13 The diagram shows the distribution of the artificial ligament channel holes (corresponding to embodiments 7, 15, 23, and 31). The lengths of each segment in the diagram are as follows: a1=0.45mm, b1=0.64mm, c1=0.81mm, d1=0.99mm, e1=1.15mm, f1=1.33mm, g1=1.5mm, h1=1.69mm, i1=1.86mm, j1=2.04mm, k1=2.20mm, l1=2.38mm, a2=0.45mm, b2=0.64mm, c2=0.81mm, d2=0.99mm, e2=1.15mm, f2=1.33mm, g2=1.5mm, h2=1.69mm, i2=1.86mm, j2=2.04mm, k2=2.20mm, l2=2.38mm. Detailed Implementation

[0063] The present invention will be further described below with reference to specific embodiments. It should be understood that these embodiments are for illustrative purposes only and are not intended to limit the scope of the invention. Furthermore, it should be understood that after reading the teachings of this invention, those skilled in the art can make various alterations or modifications to the invention, and these equivalent forms also fall within the scope defined by the appended claims.

[0064] The following are the test methods or calculation formulas for the relevant performance indicators in each embodiment and comparative example:

[0065] Fracture strength: According to YY / T 0965-2014 and YY / T 0966-2014 standards, at least 3 specimens were taken and equilibrated for 1 hour in an environment of 20-25℃ and 50%-65% relative humidity. Using a tensile testing equipment with a linear clamping device (clamp spacing 100±1mm), the tensile speed was adjusted to 100±10mm / min. The specimens were placed under a preload of 2±1N and stretched until fracture, and the force value was recorded. Three specimens were tested in parallel, and the mathematical average of the force values ​​of the three specimens was taken as the result.

[0066] Ultimate strain: According to YY / T 0965-2014 and YY / T 0966-2014 standards, take at least 3 specimens and equilibrate them for 1 hour in an environment of 20-25℃ and 50%-65% relative humidity. Using a tensile testing device with a linear clamping device, record the initial clamping distance L0 (100mm). Tensile the specimens at a speed of 100±10mm / min until fracture, and record the clamping distance L at fracture. b (mm), through the formula "limit strain = (L) b The result of the calculation is -L0)×100% / L0”, and the final average value of multiple samples is taken.

[0067] Deformation rate: The sample is loaded into an electronic universal testing machine and loaded with 300-1700 N at a speed of 5 mm / min and held at the tension for 24 h. Then, the tension is unloaded at the same speed and allowed to recover for 30 min. The initial effective length L1 (mm) and the effective length L2 (mm) after recovery are measured respectively. The deformation rate is calculated according to the formula "deformation rate = The result is calculated as "×100%".

[0068] In the following embodiments, the winding scheme 1 refers to: the two ends of the fabric along the width direction are respectively labeled as end a and end b. The fabric is first wound around the rotation axis from end a to end b, and then sewn and fixed to obtain an artificial ligament.

[0069] like Figures 1 to 2As shown, the winding scheme 2 refers to: the two ends of the fabric along the width direction are respectively labeled as end a and end b. First, the fabric is wound around the rotation axis from end a to the middle, and at the same time, it is wound from end b to the middle to obtain a blank. Then, the blank is die-cast into a cylinder and then sewn and fixed to obtain an artificial ligament.

[0070] In winding scheme 1 or winding scheme 2, the rotation axis is parallel to the warp direction of the fabric.

[0071] In the following embodiments, Method 1 refers to: threading warp yarns a and b into the heald frame, with 1 warp yarn a and 1 warp yarn b as a group, arranged in 32 groups from left to right. In groups 4, 8, 12, 22 and 28, warp yarn b is located to the left of warp yarn a, and in the remaining groups, warp yarn b is located to the right of warp yarn a.

[0072] Method 2 refers to: mapping the calculated hole positions to the heald frame through three-dimensional mapping, and threading warp yarns a and b into the heald frame; when threading the heald, starting from the inner side of the winding (i.e. the end with the densest perforation), warp yarns a are set in each inter-hole bridge in sequence. If the length of the next inter-hole bridge is not less than 1mm longer than that of the previous inter-hole bridge, then there are 2 more warp yarns a in the next inter-hole bridge than in the previous inter-hole bridge. Otherwise, the number of warp yarns a in the next inter-hole bridge is the same as that in the previous inter-hole bridge. Among them, there is 1 warp yarn a in the first inter-hole bridge.

[0073] Method 3 refers to: threading warp yarns a and b into the heald frame, placing several warp yarns b from left to right until placing one warp yarn a at 5.7mm, filling in several warp yarns b between 5.7 and 6.53mm, and then arranging 31 groups of warp yarns a and b from left to right, where each group contains one warp yarn a and several warp yarns b, with the sum of the diameters of the several warp yarns b being 1.23mm. In groups 7, 8, 11, 16, 18, 20, 22, and 24, warp yarns b are located to the left of warp yarns a; in groups 1-6, 9-10, 12-15, 17, 19, 21, and 23, warp yarns b are located to the right of warp yarns a; and in groups 25-31, warp yarns a are interspersed among several warp yarns b.

[0074] Method four refers to: mapping the calculated hole positions to the heald frame through three-dimensional mapping, and threading warp yarns a and b into the heald frame; when threading the heald, one warp yarn a is set in the inter-hole bridge with a length of less than 1.6 mm, two warp yarns a are set in the inter-hole bridge with a length between 1.6 and 2.1 mm, and three warp yarns a are set in the inter-hole bridge with a length greater than 2.1 mm.

[0075] Method 5 refers to: threading warp yarns a and b into the heddle frame; when threading the heddle, one warp yarn a and a warp yarn b sufficient to fill a 3.3mm area are grouped together, and 15 groups are arranged from left to right. In groups 1, 6, 11 and 14, warp yarn b is located to the left of warp yarn a, and in the remaining groups, warp yarn b is located to the right of warp yarn a.

[0076] Method six refers to: mapping the calculated hole positions to the heald frame through three-dimensional mapping, and threading warp yarns a and b into the heald frame; when threading the heald, one warp yarn a is set in the inter-hole bridge with a length of less than 3.5 mm, two warp yarns a are set in the inter-hole bridge with a length between 3.5 and 6.0 mm, three warp yarns a are set in the inter-hole bridge with a length greater than 6.0 mm, and one warp yarn a is set on the outside of the inter-hole bridge.

[0077] Method seven refers to: threading warp yarns a and b into the heald frame; when threading the heald, one warp yarn a and a warp yarn X sufficient to fill a 3.3mm area are grouped into 15 groups of warp yarns from left to right; in the 4th group, warp yarn X is located to the left of warp yarn a, and in the other groups, warp yarn X is located to the right of warp yarn a; in the 6th, 8th and 10th groups, warp yarn X consists of one warp yarn a and several warp yarns b, and in the other groups, warp yarn X consists of warp yarns b.

[0078] Method 8 refers to: mapping the calculated hole positions to the heald frame through three-dimensional mapping, and threading warp yarns a and b into the heald frame; when threading the heald, a warp yarn a is set inside the inter-hole bridge with a length of not less than 1 mm, and a warp yarn a is set outside the inter-hole bridge.

[0079] Method nine refers to: threading warp yarns a and b into the heald frame, with one warp yarn a and enough warp yarn b to fill a 2.3mm area as one group, arranging 18 groups from left to right. In the first group, warp yarn a is arranged 1.7mm from the left edge of the fabric, and the remaining space is filled with warp yarn b. In the second, third, fifth, seventh, tenth and eleventh groups, warp yarn b is located to the left of warp yarn a, and in the remaining groups, warp yarn b is located to the right of warp yarn a.

[0080] Method 10 refers to: mapping the calculated hole positions to the heald frame through three-dimensional mapping, and threading warp yarns a and b into the heald frame; when threading the heald, one warp yarn a is set in the inter-hole bridge with a length of less than 3.5 mm, two warp yarns a are set in the inter-hole bridge with a length between 3.5 and 6.0 mm, and three warp yarns a are set in the inter-hole bridge with a length greater than 6.0 mm.

[0081] Method eleven refers to: threading warp yarns a and b into the heald frame; when threading the healds, each group consists of one warp yarn a and a warp yarn X sufficient to fill a 2.3mm area, arranged from left to right in 14 groups; in groups 2, 3, 10, and 11, warp yarn X is located to the left of warp yarn a, and in the remaining groups, warp yarn X is located to the right of warp yarn a; in groups 5, 7, 13, and 14, warp yarn X consists of one warp yarn a and several warp yarns b, and in the remaining groups, warp yarn X consists of warp yarns b.

[0082] Method 12 refers to: mapping the calculated hole positions to the heald frame through three-dimensional mapping, and threading warp yarns a and b into the heald frame; when threading the heald, a warp yarn a is set in the inter-hole bridge with a length of not less than 0.9mm.

[0083] Method thirteen refers to: threading warp yarns a and b into the heald frame, with one warp yarn a and enough warp yarn b to fill a 5.87mm area as one group, arranging 9 groups from left to right. In groups 1, 3, 4 and 7, warp yarn b is located to the left of warp yarn a. In group 2, warp yarn a is placed 9.5mm from left to right facing the machine direction. In the remaining groups, warp yarn b is located to the right of warp yarn a.

[0084] Method fourteen refers to: mapping the calculated hole positions to the heald frame through three-dimensional mapping, and threading warp yarns a and b into the heald frame; when threading the heald, a warp yarn a is set inside the inter-hole bridge with a length of less than 7.0 mm, and a warp yarn a is set outside the inter-hole bridge.

[0085] Method 15 refers to: threading warp yarns a and b into the heald frame; when threading the heald, one warp yarn a and a warp yarn X sufficient to fill a 5.87mm area are grouped into 7 groups of warp yarns from left to right; warp yarn X is located to the right of warp yarn a; in the 2nd and 5th groups, warp yarn X consists of one warp yarn a and several warp yarns b, and in the remaining groups, warp yarn X consists of warp yarns b.

[0086] Method sixteen refers to: mapping the calculated hole positions to the heald frame through three-dimensional mapping, and threading warp yarns a and b into the heald frame; when threading the heald, within the range of inter-hole bridges with a length between 0.8 and 2.5 mm, a warp yarn a is set every two inter-hole bridges from the inside of the winding (i.e. the end with the most dense perforations), and a warp yarn a is set on the outside of the inter-hole bridges.

[0087] Example 1

[0088] A method for preparing an artificial ligament, the specific steps of which are as follows:

[0089] (1) Preparation of materials;

[0090] Warp a: PET thread, with a breaking strength of 183N;

[0091] Warp yarn b: Multifilament, composed of 36 single yarns combined together, with a specification of 1800D / 36F; the single yarn is FDY yarn, and the material is PET.

[0092] Weft yarn: multifilament, composed of 640 single yarns combined, specification is 2000D / 640F; single yarn is FDY yarn, material is PET;

[0093] (2) Channel hole modeling;

[0094] Based on the size requirements and channel design parameters of the artificial ligament, a three-dimensional model (such as...) is established. Figure 3 The hole location was calculated and designed (as shown in the figure), and the hole location distribution diagram was obtained as follows. Figure 4 As shown;

[0095] (3) Arrange the warp yarns and thread the heddles according to method one;

[0096] (4) Fabric weaving;

[0097] The fabric was woven using a GA615A3 treadle-operated open plain weave loom manufactured by Shandong Lujia Textile Machinery Technology Co., Ltd. The warp density was controlled at 100 threads / 10cm, and the weft density at 80 threads / 10cm. During the weaving process, the weft was first beaten in to form the first knitting section (corresponding to the first bone tunnel knitting section below). Then, a central area was left untouched, retaining only the warp yarns to form the free yarn section (corresponding to the joint free yarn section below). Finally, the weft was beaten in again to form the second knitting section (corresponding to the second bone tunnel knitting section below).

[0098] (5) Laser drilling;

[0099] Based on the modeled hole distribution in step (2), a laser drilling machine is used to perform drilling operations, forming through holes in the first and second braided sections of the fabric. The fabric after laser drilling is as follows: Figure 5 As shown;

[0100] (6) The fabric is processed using winding scheme 1 to obtain an artificial ligament.

[0101] The final artificial ligament is shown in Figure 6(a), which has a cylindrical structure. The cylindrical structure forms a first bone tunnel braid, an intra-articular free wire 3, and a second bone tunnel braid in sequence along the axial direction.

[0102] The first bone tunnel braiding part consists of a first channelless region 1 and a first channeled region 2 arranged sequentially along the axial direction of the cylindrical bar structure. The second bone tunnel braiding part consists of a second channelless region 5 and a second channeled region 4 arranged sequentially along the axial direction of the cylindrical bar structure. The first channelless region 1, the first channeled region 2, the intra-articular free wire part 3, the second channeled region 4 and the second channelless region 5 are connected sequentially.

[0103] The diameter of the round rod structure is 9mm; the length of the first bone tunnel braid and the second bone tunnel braid is 17.5cm; the length of the first channeled region 2 and the second channeled region 4 is 6cm; and the length of the intra-articular free wire 3 is 30mm.

[0104] Both the first channel area 2 and the second channel area 4 are provided with through channels, which intersect with the central axis of the cylindrical bar structure; the channels are formed by multiple through holes, which are formed by the breakage of a portion of the warp yarn b;

[0105] The channels in the first bone tunnel weaving section are designated as the first group of channels 6, and the channels in the second bone tunnel weaving section are designated as the second group of channels 7. In the first group of channels 6 or the second group of channels 7, the channels are distributed on multiple layers perpendicular to the axial direction of the round bar structure.

[0106] The aperture of the channel is 300μm; in the first group of channels 6 and the second group of channels 7, there are 46 channels in each group, 1 channel is located on the same layer, and the distance between two adjacent layers along the axial direction of the cylindrical structure is 1mm.

[0107] The fracture strength of the artificial ligament is 5856 N, and the ultimate strain is 8.5%. The deformation rate of the artificial ligament after being left to stand for 24 hours under a tensile force of 300 N is 1%.

[0108] Examples 2-8

[0109] Except for Table 1, Examples 2-8 are the same as Example 1.

[0110] Table 1: Comparison of key process parameters and performance indicators of artificial ligaments in Examples 1-8

[0111]

[0112] Comparative Example 1

[0113] The method for preparing an artificial ligament differs from Example 1 only in that the warp arrangement and heddle threading process is as follows: warp a and warp b are threaded into the heddle frame, with one warp a and one warp b forming a group, arranged from left to right in 32 groups. In groups 1, 4, 5, 8, 9, 12, 15, 17, 19, 22, 24, 26 and 28, warp b is located to the left of warp a, and in the remaining groups, warp b is located to the right of warp a.

[0114] The final artificial ligament had a fracture strength of 3762 N and an ultimate strain of 6.3%; the artificial ligament had a deformation rate of 6.5% after being left to stand for 24 hours under a tensile force of 300 N.

[0115] Compared with Comparative Example 1 and Example 1, the fracture strength, ultimate strain and deformation rate of the artificial ligament were significantly worse. This is because the core stress-bearing suture warp yarns were damaged, resulting in poorer mechanical properties.

[0116] Comparative Example 2

[0117] A method for preparing an artificial ligament differs from Example 1 only in that both warp yarn b and weft yarn are replaced with multifilament yarn (warp yarn a).

[0118] The final artificial ligament had a fracture strength of 3300 N and an ultimate strain of 3.7%; the deformation rate of the artificial ligament after being left to stand for 24 hours under a tensile force of 300 N was 4.6%.

[0119] Compared with Example 1, the fracture strength, ultimate strain and deformation rate of the artificial ligament were significantly worse. This is because the warp yarns, which act as the mechanical skeleton, broke completely after the perforation, resulting in a collapse in strength.

[0120] Example 9

[0121] A method for preparing an artificial ligament, the specific steps of which are as follows:

[0122] (1) Preparation of materials;

[0123] Warp a: UHMWPE thread, with a breaking strength of 432N;

[0124] Warp yarn b: Multifilament, composed of 30 single yarns combined together, specification 1800D / 30F; the single yarn is FDY yarn, material is UHMWPE;

[0125] Weft yarn: multifilament, composed of 30 single yarns combined, specification is 1800D / 30F; single yarn is FDY yarn, material is UHMWPE;

[0126] (2) Channel hole modeling;

[0127] Based on the size requirements and channel design parameters of the artificial ligament, a three-dimensional model (such as...) is established. Figure 3 The hole location was calculated and designed (as shown in the figure), and the hole location distribution diagram was obtained as follows. Figure 4 As shown;

[0128] (3) Arrange the warp yarns and thread the heddles according to method five;

[0129] (4) Fabric weaving;

[0130] The fabric was woven using a GA615A3 treadle-operated open plain weave loom manufactured by Shandong Lujia Textile Machinery Technology Co., Ltd. The warp density was controlled at 90 threads / 10cm, and the weft density at 65 threads / 10cm. During the weaving process, the weft was first beaten in to form the first knitting section (corresponding to the first bone tunnel knitting section below). Then, a central area was left untouched, retaining only the warp yarns to form the free yarn section (corresponding to the joint free yarn section below). Finally, the weft was beaten in again to form the second knitting section (corresponding to the second bone tunnel knitting section below).

[0131] (5) Laser drilling;

[0132] Based on the modeled hole distribution in step (2), a laser drilling machine is used to perform drilling operations, forming through holes in the first and second braided sections of the fabric. The fabric after laser drilling is as follows: Figure 5 As shown;

[0133] (6) The fabric is processed using winding scheme 1 to obtain an artificial ligament.

[0134] The final artificial ligament is shown in Figure 6(a), which has a cylindrical structure. The cylindrical structure forms a first bone tunnel braid, an intra-articular free wire, and a second bone tunnel braid in sequence along the axial direction.

[0135] The first bone tunnel braiding part consists of a first channelless region and a first channeled region arranged sequentially along the axial direction of the cylindrical bar structure. The second bone tunnel braiding part consists of a second channelless region and a second channeled region arranged sequentially along the axial direction of the cylindrical bar structure. The first channelless region, the first channeled region, the intra-articular free wire part, the second channeled region and the second channelless region are connected sequentially.

[0136] The diameter of the round rod structure is 9mm; the length of the first bone tunnel braid and the second bone tunnel braid is 16cm; the length of the first channel area and the second channel area is 6cm; and the length of the free wire part inside the joint is 30mm.

[0137] Both the first and second bone tunnel braiding sections have through channels within their channeled areas, and these channels intersect with the central axis of the round bar structure. The channels are formed by multiple through holes, which are created by the breakage of a portion of the warp yarn b.

[0138] The channels in the first bone tunnel weaving section are referred to as the first group of channels, and the channels in the second bone tunnel weaving section are referred to as the second group of channels. In the first group of channels or the second group of channels, the channels are distributed on multiple layers perpendicular to the axis of the round bar structure.

[0139] The aperture of the channel is 500 μm; in the first group of channels and the second group of channels, there are 46 channels in each group, and the number of channels located on the same layer is 1. The distance between two adjacent layers along the axial direction of the cylindrical structure is 3 mm.

[0140] The artificial ligament has a tensile strength of 6380 N and an ultimate strain of 9%; the artificial ligament has a deformation rate of 1% after being left to stand for 24 hours under a tensile force of 1700 N.

[0141] Examples 10-16

[0142] Except for Table 2, Examples 10-16 are the same as Example 9.

[0143] Table 2: Comparison of key process parameters and performance indicators of artificial ligaments in Examples 9-16

[0144]

[0145]

[0146]

[0147] Example 17

[0148] A method for preparing an artificial ligament, the specific steps of which are as follows:

[0149] (1) Preparation of materials;

[0150] Warp a: PEEK No. 5 thread, with a breaking strength of 300N;

[0151] Warp yarn b: Multifilament, composed of 20 single yarns combined together, specification 2000D / 20F; the single yarn is FDY yarn, material is PEEK;

[0152] Weft yarn: multifilament, composed of 20 single yarns combined together, specification 2000D / 20F; single yarn is FDY yarn, material is PEEK;

[0153] (2) Channel hole modeling;

[0154] Based on the size requirements and channel design parameters of the artificial ligament, a three-dimensional model (such as...) is established. Figure 3 The hole location was calculated and designed (as shown in the figure), and the hole location distribution diagram was obtained as follows. Figure 4 As shown;

[0155] (3) Arrange the warp yarns and thread the heddles according to method nine;

[0156] (4) Fabric weaving;

[0157] The fabric was woven using a GA615A3 treadle-operated open plain weave loom manufactured by Shandong Lujia Textile Machinery Technology Co., Ltd. The warp density was controlled at 110 threads / 10cm, and the weft density at 85 threads / 10cm. During the weaving process, the weft was first beaten in to form the first knitting section (corresponding to the first bone tunnel knitting section below). Then, a central area was left untouched, retaining only warp yarns to form the free yarn section (corresponding to the joint free yarn section below). Finally, the weft was beaten in again to form the second knitting section (corresponding to the second bone tunnel knitting section below).

[0158] (5) Laser drilling;

[0159] Based on the modeled hole distribution in step (2), a laser drilling machine is used to perform drilling operations, forming through holes in the first and second braided sections of the fabric. The fabric after laser drilling is as follows: Figure 5 As shown;

[0160] (6) The fabric is processed using winding scheme 1 to obtain an artificial ligament.

[0161] The final artificial ligament is shown in Figure 6(a), which has a cylindrical structure. The cylindrical structure forms a first bone tunnel braid, an intra-articular free wire, and a second bone tunnel braid in sequence along the axial direction.

[0162] The first bone tunnel braiding part consists of a first channelless region and a first channeled region arranged sequentially along the axial direction of the cylindrical bar structure. The second bone tunnel braiding part consists of a second channelless region and a second channeled region arranged sequentially along the axial direction of the cylindrical bar structure. The first channelless region, the first channeled region, the intra-articular free wire part, the second channeled region and the second channelless region are connected sequentially.

[0163] The diameter of the round rod structure is 9mm; the length of the first bone tunnel braid and the second bone tunnel braid are both 17.5cm, the length of the first channel area and the second channel area are both 5.5cm, and the length of the free wire part inside the joint is 20mm.

[0164] Both the first and second bone tunnel braiding sections have through channels within their channeled areas, and these channels intersect with the central axis of the round bar structure. The channels are formed by multiple through holes, which are created by the breakage of a portion of the warp yarn b.

[0165] The channels in the first bone tunnel weaving section are referred to as the first group of channels, and the channels in the second bone tunnel weaving section are referred to as the second group of channels. In the first group of channels or the second group of channels, the channels are distributed on multiple layers perpendicular to the axis of the round bar structure.

[0166] It should be noted that the aperture of the channel is 500μm; in both the first and second groups of channels, there are 46 channels, with 1 channel located on the same layer, and the distance between two adjacent layers along the axial direction of the cylindrical structure is 3mm.

[0167] The artificial ligament has a tensile strength of 5400 N and an ultimate strain of 8.5%; the artificial ligament has a deformation rate of 0.9% after being left to stand for 24 hours under a tensile force of 500 N.

[0168] Examples 18-24

[0169] Except for Table 3, Examples 18-24 are the same as Example 17.

[0170] Table 3: Comparison of key process parameters and performance indicators of artificial ligaments in Examples 17-24

[0171]

[0172]

[0173]

[0174] Example 25

[0175] A method for preparing an artificial ligament, the specific steps of which are as follows:

[0176] (1) Preparation of materials;

[0177] Warp a: Carbon Fiber No. 5 thread, with a breaking strength of 600N;

[0178] Warp yarn b: Multifilament, composed of 25 single yarns combined together, with a specification of 2500D / 25F; the single yarns are FDY yarn, made of Carbon Fiber;

[0179] Weft yarn: multifilament, composed of 25 single yarns combined together, specification 2500D / 25F; single yarn is FDY yarn, material is Carbon Fiber;

[0180] (2) Channel hole modeling;

[0181] Based on the size requirements and channel design parameters of the artificial ligament, a three-dimensional model (such as...) is established. Figure 3 The hole location was calculated and designed (as shown in the figure), and the hole location distribution diagram was obtained as follows. Figure 4 As shown;

[0182] (3) Arrange the warp yarns and thread the heddles according to method thirteen;

[0183] (4) Fabric weaving;

[0184] The fabric was woven using a GA615A3 treadle-operated open plain weave loom manufactured by Shandong Lujia Textile Machinery Technology Co., Ltd. The warp density was controlled at 100 threads / 10cm, and the weft density at 80 threads / 10cm. During the weaving process, the weft was first beaten in to form the first knitting section (corresponding to the first bone tunnel knitting section below). Then, a central area was left untouched, retaining only the warp yarns to form the free yarn section (corresponding to the joint free yarn section below). Finally, the weft was beaten in again to form the second knitting section (corresponding to the second bone tunnel knitting section below).

[0185] (5) Laser drilling;

[0186] Based on the modeled hole distribution in step (2), a laser drilling machine is used to perform drilling operations, forming through holes in the first and second braided sections of the fabric. The fabric after laser drilling is as follows: Figure 5 As shown;

[0187] (6) The fabric is processed using winding scheme 2 to obtain an artificial ligament.

[0188] The final artificial ligament is shown in Figure 6(a), which has a cylindrical structure. The cylindrical structure forms a first bone tunnel braid, an intra-articular free wire, and a second bone tunnel braid in sequence along the axial direction.

[0189] The first bone tunnel braiding part consists of a first channelless region and a first channeled region arranged sequentially along the axial direction of the cylindrical bar structure. The second bone tunnel braiding part consists of a second channelless region and a second channeled region arranged sequentially along the axial direction of the cylindrical bar structure. The first channelless region, the first channeled region, the intra-articular free wire part, the second channeled region and the second channelless region are connected sequentially.

[0190] The diameter of the round rod structure is 7.5 mm; the length of the first bone tunnel braid and the second bone tunnel braid is 16 cm; the length of the first channel area and the second channel area is 6 cm; and the length of the free wire part inside the joint is 25 mm.

[0191] Both the first and second bone tunnel braiding sections have through channels within their channeled areas, and these channels intersect with the central axis of the round bar structure. The channels are formed by multiple through holes, which are created by the breakage of a portion of the warp yarn b.

[0192] The channels in the first bone tunnel weaving section are referred to as the first group of channels, and the channels in the second bone tunnel weaving section are referred to as the second group of channels. In the first group of channels or the second group of channels, the channels are distributed on multiple layers perpendicular to the axis of the round bar structure.

[0193] The aperture of the channel is 500 μm; in the first group of channels and the second group of channels, there are 46 channels in each group, and the number of channels located on the same layer is 1. The distance between two adjacent layers along the axial direction of the cylindrical structure is 3 mm.

[0194] The artificial ligament has a tensile strength of 5400 N and an ultimate strain of 9%; the artificial ligament has a deformation rate of 1.1% after being left to stand for 24 hours under a tensile force of 800 N.

[0195] Examples 26-32

[0196] Except for Table 4, Examples 26-32 are the same as Example 25.

[0197] Table 4: Comparison of key process parameters and performance indicators of artificial ligaments in Examples 25-32

[0198]

[0199]

[0200]

Claims

1. An artificial ligament having a cylindrical rod structure, wherein the cylindrical rod structure forms a first bone tunnel braided portion, an intra-articular free yarn portion, and a second bone tunnel braided portion connected sequentially along the axial direction, the cylindrical rod structure comprising warp yarns and weft yarns, the warp yarns extending along the axial direction of the cylindrical rod structure, the weft yarns extending along the circumferential direction of the cylindrical rod structure, both the first bone tunnel braided portion and the second bone tunnel braided portion comprising the warp yarns and the weft yarns, and the intra-articular free yarn portion comprising only the warp yarns; Its features are, Both the first bone tunnel braid and the second bone tunnel braid are provided with through channels, and the extension direction of the channels is perpendicular to the axial direction of the round bar structure; The channel is formed by multiple through holes; There are two types of warp yarns: sewing thread and multifilament yarn. The breaking strength of a single sewing thread is 140-720N. The through-hole is formed by the breakage of a portion of the multifilament yarn. The weft yarn is multifilament.

2. The artificial ligament according to claim 1, characterized in that, The aperture of the channel is 300-600μm.

3. The artificial ligament according to claim 1, characterized in that, The channel intersects the central axis of the cylindrical structure.

4. The artificial ligament according to claim 1, characterized in that, The channels in the first bone tunnel braid are referred to as the first group of channels, and the channels in the second bone tunnel braid are referred to as the second group of channels; in the first group of channels or the second group of channels, the channels are distributed on at least two layers perpendicular to the axial direction of the round bar structure.

5. An artificial ligament according to claim 4, characterized in that, In the first group of channels or the second group of channels, the distance between two adjacent layers along the axial direction of the cylindrical structure is 1-3 mm.

6. The artificial ligament according to claim 1, characterized in that, The cylindrical structure is obtained by processing a fabric with the through hole. The processing steps include a winding operation around a rotation axis and a sewing and fixing operation. The rotation axis is parallel to the warp direction of the fabric.

7. An artificial ligament according to claim 6, characterized in that, The fabric has a warp density of 90-110 threads / 10cm and a weft density of 65-85 threads / 10cm.

8. The artificial ligament according to claim 1, characterized in that, The first bone tunnel braiding portion consists of a first channelless region and a first channeled region arranged sequentially along the axial direction of the cylindrical bar structure. The second bone tunnel braiding portion consists of a second channelless region and a second channeled region arranged sequentially along the axial direction of the cylindrical bar structure. The first channelless region, the first channeled region, the intra-articular free wire portion, the second channeled region, and the second channelless region are connected sequentially.

9. An artificial ligament according to claim 8, characterized in that, The diameter of the round bar structure is 7.5-9.5 mm; the length of the first bone tunnel braid or the second bone tunnel braid is 16-17.5 cm, the length of the first channeled area or the second channeled area does not exceed 6 cm, and the length of the free wire part inside the joint is 20-30 mm.

10. An artificial ligament according to claim 1, characterized in that, The multifilament is composed of 12-36 single yarns combined together. The specification of the multifilament is 1800-2500D. The single yarn is FDY yarn and the material is high molecular weight polyethylene, polyethylene terephthalate, polyetheretherketone or carbon fiber.

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