as summarized above , three - dimensional ( 3d ) fiber arrays are disclosed , for reinforcing hydrogel layers in relatively thin and flexible surgical implants for replacing hyaline cartilage in mammalian joints . the reinforcing layers and implants disclosed herein can be manufactured in any desired widths and lengths , and can enable the replacement of entire segments of hyaline cartilage , rather than merely creating plug - type implants that will create gaps and discontinuities in a repaired cartilage surface . however , despite their relatively large surface areas , these implants can be thin enough to render them flexible , for insertion into a joint using arthroscopic methods and devices . if a suitable fabrication method is used to make the reinforcing layers ( such as by using a computer - controlled stitching machine , as described below ), these types of hydrogel implants can be made in ways that render them well - suited for : ( i ) permanent bonding to an anchoring rim , which can be made of a strong material such as a nitinol - type alloy ; and , ( ii ) providing a porous layer on the anchoring surface that will promote tissue growth into the porous layer , to create stronger and more durable anchoring of the implant to a bone surface . for convenience and clarity , all discussion below assumes that the computer - controlled stitching machine being used to create a 3d fiber array for reinforcing a hydrogel layer in an implant as described herein will have two principle operating components : ( 1 ) a single threaded needle that is active at a given time , and that is able to travel only vertically , while active ; and , ( 2 ) a fabric - holding device that can stretch and hold a piece of fabric ( or other sheet - like backing material ) in a relatively taut horizontal position while stitches are being created on the backing layer , and that also is designed to be able to move the sheet or segment of backing material in any horizontal direction that has been programmed into the software that control the machine . this discussion assumes that the needle - holder is positioned above the backing holder , thereby causing the tip and shaft of the needle to : ( i ) penetrate through ( and thereby engage ) the backing layer , during the downward portion of each needle stroke ; and , ( ii ) rise above ( and thereby disengage from ) the backing layer , during the upward portion of the needle stroke . downward movement of the needle during each stroke or cycle , and / or the moments when the needle penetrates and engages the backing layer , can be referred to as extension , thrust , lowering , engagement , or similar terms . upward travel of the needle , and / or the state of disengagement of the needle from the backing layer , can be referred to as retraction , withdrawal , raising , disengagement , or similar terms . as described in the background section , and because of how these types of stitching machines operate , the types of stitching that are of interest herein can be grouped into two main categories , which are tufted and sewn . as illustrated in fig1 , a tufted 3d array 100 is created when thread 110 is pushed through a backing layer 120 ( which is shown as strand 122 , interlaced between the cross - sectional ends of strands 124 ), in a manner that creates and preserves elongated loops 112 . in a machine where the needle holder 150 and needle 152 are positioned above the backing layer 120 , this initially will create tufts that point downward ; after the stitching operation has been completed , the resulting tufted material normally will be turned over , so that the tufted side 102 ( often called the face side , finished side , or similar terms ) will be on top , during subsequent processing . the vertical arrow next to the needle holder 150 and threaded needle 152 indicates that those devices will move only vertically , when in use . the horizontal arrow above the backing layer indicates that it will be pulled slightly to the left , each time the tip of needle 152 rises high enough to disengage from the backing layer 120 , when creating that row of tufted loops . multiple rows of tufting loops will be created , with each row having dozens , hundreds , or even thousands of miniaturized tufts , to create a fiber array that will have a moderate but not excessive “ areal density ”, as described below . as mentioned in the background section , two practical results arise from how tufted loops are formed . first : most of the thread mass and weight will be positioned on the side of the backing layer that is positioned away from the needle holder . second : the entry and exit points for any tufted loop must be immediately adjacent to each other , and cannot be separated by even a single fiber of backing layer 120 . the “ length ” of the tufts will become the tufting height , after the stitching operation has been completed , and the material is removed from the machine and turned over , so that the tufts point upward . this dimension , which is perpendicular to the backing layer 120 , might also be referred to as the thickness of the 3d fiber array ; however , since a hydrogel layer subsequently will increase the thickness of the final device , use of the term “ thickness ” might be confusing , if applied to only the tufted layer that will be embedded inside the hydrogel . therefore , “ tufting height ” is preferred , when referring to a tufted 3d array without a hydrogel layer affixed to it . tufting height can be determined relative to any of three “ baseline ” or starting point levels , which are : ( i ) the top surface of the backing layer ; ( ii ) the centerline of the backing layer ; or ( iii ) the bottom surface of the fiber array , including the backing layer . since it is convenient to measure the thickness of an entire fiber array , without having to discount the thickness of the backing layer , tufting heights preferably should refer to the thickness of an entire tufted fiber array , including the backing layer and any additional thickness imparted by the small loops of material on the “ bottom side ” of the array . the hydrogel normally will not be affixed to the fiber array until after the fiber array has been removed from the stitching machine . as implied by fig1 , the hydrogel layer should be thick enough to prevent any fiber strands or loop tips from being exposed on the articulating surface of the hydrogel , since any fiber strands exposed on that smooth surface could create unwanted abrasion by the implant , after surgery . unlike a tufted carpet , in which the tufts are packed together tightly , to provide resistance and resilience against the weight of people walking repeatedly on the carpet , the tufts in a 3d fiber array that reinforces a hydrogel do not need to be packed tightly together , since they generally will need to provide only tensile strength , to prevent the hydrogel from being torn . the hydrogel itself , if made of a sufficiently strong polymer , will provide all necessary compressive strength and resistance . therefore , the tufts generally should have a limited and somewhat loose “ areal ” density ( such as less than about 50 %), to prevent air or gas bubbles from being trapped in the fiber array when the hydrogel material is being added and affixed to the fiber array , and to help sustain the permeability of the hydrogel to water , after implantation of the device . areal density can be expressed as the fraction ( or percentage ) of a horizontal cross - sectional area of a hydrogel material containing a fiber reinforcing array , measured at or near the middle of the height of the fiber array . unless and until data from in vitro tests of prototype samples indicate otherwise , it is believed that areal densities ranging from about 5 % to about 50 % can provide sufficient reinforcement without seriously impeding water travel through fiber - reinforced hydrogel materials , and areal densities of about 10 to 30 % offer preferred candidates for early evaluation . the preferred density for any particular fiber - reinforced hydrogel will depend on various factors , such as whether monofilaments or yarns are used , the thicknesses of the strands of fiber or yarn , and the intended location for a particular implant ( for example , implants for finger joints are likely to require less reinforcement than implants for knee joints ). it also should be recognized that the tufting height ( or other measures of the thickness , height , or depth of a 3d fiber array ) does not need to reach any particular fraction or percentage of a hydrogel thickness , for all implants . depending on factors such as the strength and toughness of a hydrogel polymer , the type of joint an implant will be used to repair , and the size and dimensions of the implant , some implants that are intended to repair loaded joints ( such as knee joints ) may be strongest and most durable , if their reinforcing 3d fiber arrays extend through 90 % or more of the thickness of the hydrogel layer . by contrast , other implants that will subjected to lower loadings and stresses ( such as in finger joints ) may have sufficient reinforcement , so long as their 3d fiber arrays merely provide an adequate transition zone between a backing layer or anchoring component , and a softer hydrogel . transition zones in such implants might occupy , for example , only about 10 % to about 30 % of the thickness of the hydrogel layer . finally , fig1 also indicated a “ margin ” area 180 , where backing layer 120 does not have any tufts or stitches . this margin area , which generally will extend around the periphery of a segment of tufted ( or sewn ) material , is designed to allow subsequent handling and processing of a stitched fiber array , in ways that would be rendered impractical or more difficult , if stitching covered the margins . for example , as discussed below , the presence of unstitched margins around the periphery of a fiber array can allow ultrasonic welding of the backing layer to a polymer component that is gripped and held by a “ shape - memory ” material ( such as a nitinol alloy ) that is part of an anchoring rim . fig2 illustrates a sewn 3d fiber array 200 , having stitches 210 with their longest portions on the same side of backing layer 220 as needle holder 240 and needle 242 . only small loops 212 are positioned below backing layer 220 , and fig2 illustrates an “ interlocked ” stitching structure , in which a locking fiber 222 is passed through each loop 212 , by means of a “ floating bobbin ” mechanism , before the loop 212 is pulled tight against the locking fiber . as illustrated in fig2 , each sewn stitch 210 usually will traverse some distance across backing layer 220 , with the entry point and exit point for a stitch separated by at least one fiber in the backing layer 220 . since the longer stitch portions 210 are above the backing layer while the short locking loops 212 are below the backing layer , most of the thread mass and weight will be created on the same side of the backing layer as the needle holder 240 . fig2 also shows an unstitched margin around the periphery of the sewn fiber array , to enable attachment of the fiber array to another implant component , such as ultrasonic welding attachment to a polymer component in a nitinol anchoring rim . tufted 3d arrays may be able to provide greater consistency , uniformity and control over thickness , than sewn fiber arrays in which the stitches are not pulled tight and have substantial surplus length . this is especially true if a stitching machine that is being used to create tufts uses a “ looper ” device to momentarily grab the tip of each tufting loop , as it is being created , and it should be noted that the amaya machine does not have or use such “ looper ” devices . however , alternate means can be used to create sewn stitches with relatively consistent “ heights ” above a backing layer . for example , on an amaya machine , an adjustable mechanical wheel ( which is not directly controllable by any software , coding , or similar instructions , but which can be readily accessed and manipulated by an operator ) can be used to vary the setting of a device called the “ presser foot ” during a stitching operation . a higher presser foot setting will create stitches that have taller heights , in a consistent manner . if testing ( using microscopic analysis and photography , in a manner comparable to histological examination of cells and tissues ) indicates that additional steps must be taken to prevent any tufting loops or sewn stitches from reaching and disrupting the smooth articulating surface of a hydrogel layer , such steps can be taken . for example , a layer of mesh or screen material can be placed over the outer surface of a set of tufted or sewn stitches ; alternately , if thicker fibers with greater stiffness are used , they are likely to establish curves and arcs that have greater consistency and less variability , compared to thinner and more flexible fibers . it should also be noted that if a 3d fiber array rises to only a limited and partial height ( such as less than about 80 % of the thickness of the hydrogel layer ), the risk of protruding stitches disrupting a smooth surface may be minimal or nonexistent . it also should be kept in mind that the types of fabrics usually known as felt , velour , and chenille offer additional examples of fabric types where loop or stitch length and height must be kept consistent . accordingly , if variations in loop or stitch length and height , in 3d reinforcing arrays as described herein , create problems of unwanted variability that jeopardize quality control , the methods and machines used to create those three other classes of fabrics can be studied and evaluated in detail , to determine whether such methods and / or machines can be adapted for use in reducing any such unwanted variability and other problems . a hydrogel polymer can be affixed to a 3d fiber array , by means of a molding and curing process that uses a liquid referred to herein as a “ prepolymer ”. various means are known for converting liquid prepolymers into cured , solid but gelatinous polymers ; for example , polyacrylonitrile polymers are often cured by heating a homogenous liquid to a reaction temperature , and then allowing the polymer to cool again , while polyurethane polymers are often created by mixing a resin with a catalyst , and then allowing the two liquids to chemically react with each other . normally , to help ensure a smooth and flat top surface , a liquid prepolymer will be poured or otherwise distributed on top of a 3d fiber array that is resting in a tray or similar holder ; alternately , it is possible to use methods that involve dipping a fiber array into a tray that holds a liquid prepolymer . if desired , a vibrating or impact - generating support device , sonic waves , a raking or combing device , a roller or other compressor device , or other means can be used to help dislodge and remove any air bubbles that may initially be trapped beneath the liquid surface , after a prepolymer liquid has been poured on top of the fiber array . the shape and size of a backing layer used to create any particular type of implant also can be controlled and varied by methods known to those skilled in the art , such as by using a fabric or plastic backing layer that was created with ( or subsequently given ) a curvature or other “ bias ”. in this manner , implants having controlled shapes can be created for different types of joints , and for patients of different sizes . as examples , stitched 3d fiber arrays as described herein can be sized and shaped in ways that will accommodate entire unicompartmental segments of femoral runners , tibial plateaus , or patellar surfaces in knee joints , ball or socket surfaces in hips or shoulders , knuckle joints in fingers or toes , or any other articulating joint surfaces that may need repair , in people suffering from injuries , arthritis , or other disorders , and they can also be creating with smaller sizes , if desired , to serve as plug - type implants that will be stronger and more durable ( and that can be anchored more securely ) that other types of plug - type implants available today , such as salucartilage implants , described in the background section . orthopedic manufacturing companies are already very familiar with the sizes and shapes of implants that are needed for the various joints of the body that commonly need repair , and the exact size of any targeted bone surface in any patient can be readily determined by x - rays or other medical imaging methods before surgery begins , when time is available to order and receive an implant that will be optimally sized and shaped for that individual patient . as mentioned above , if a cartilage - replacing implant is not specifically designed to be dissolved and resorbed by the body , the reinforcing fiber array should be made of nonresorbable synthetic polymers . candidate polymers include polyesters , high ( or ultra - high ) molecular weight polyethylene , polycarbonate urethane , polyacrylonitrile , and others that are known to those skilled in the art . numerous companies ( such as secant , putnam plastics , the depuy - mitek division of johnson & amp ; johnson , etc .) sell synthetic sutures , and researchers , technical support specialists , and vendors at such companies are experts in the performance traits and comparatives advantages and disadvantages of such materials for various surgical uses . in at least some cases , a design requirement is likely to result in selection of one type of polymer for the backing layer , and a different type of polymer for the stitches . this trait arises from the need to be able to securely and permanently affix the 3d fiber array that will reinforce a hydrogel polymer , to an implant component referred to herein as an anchoring member . when used with implants for replacing hyaline cartilage , the anchoring member normally will be used to help securely affix the implant to a hard bone surface from which the native cartilage has been removed . examples of such anchoring devices , specifically designed to securely anchor cartilage - replacing hydrogel implants to prepared bone surfaces , are discussed in more detail in patent cooperation treaty patent application pct / us05 / 43444 , by mansmann et al , filed in november 2005 . that pct application claims priority based on u . s . provisional applications 60 / 631 , 652 ( filed in november 2004 ), 60 / 656 , 606 ( filed in february 2005 ), and 60 / 685 , 345 ( filed in may 2005 ), and it is scheduled to be published in about may 2006 . the contents and teachings of that pct application , and of all three provisional applications listed above , are incorporated herein by reference , as though fully set forth herein . briefly , those patent applications describe the design and use of anchoring rims that are attached to anchoring pegs ( or studs , posts , or similar terms ). during a surgical procedure , the anchoring pegs will be pressed into eternally - threaded barrels ( or sleeves , cylinders , etc . ), which will be emplaced and secured in holes that are drilled into a prepared bone surface . in order to provide the surgeon with room to work and maneuver , the holes will be drilled into the bone , and the anchoring barrels will be positioned and secured in the drilled holes , before the body of the implant device is inserted into the joint . the rim of this type of anchoring component will comprise a flexible polymer , which can be reinforced if desired by a metallic or other hard component made of a “ shape - memory material ”. these materials grew out of the discovery in the 1930 &# 39 ; s of an alloy called “ nitinol ”, which shrinks when heated . other shape - memory materials known today will shrink when chilled ; these can allow insertion of temporarily “ shrunken ” implant devices that have been chilled , in ways that minimize any damage to surrounding tissue during the insertion step . after the chilled implant has been properly positioned , the shape - memory material will be warmed up again , by body tissues and fluids , and it will expand back into its original shape . if a metallic alloy or comparable shape - memory material forms a rim component or similar structure that will be used to anchor a cartilage - replacing implant to a bone or other tissue , the rim component or similar structure can be provided with an insert ( which can also be called an inset , component , member , or similar terms ) made of a selected type of polymer . this polymer insert will need to be an elastomer , to enable it to change shapes as the anchoring device is chilled and shrunk for insertion , then expanding again after insertion , into its normal shape . accordingly , in this type of implant , the 3d fiber array must be securely and permanently affixed to the anchoring member ( which in most cases will surround the implant device , establishing its periphery ). if suitable materials have been selected for all components involved , this permanent attachment can be created , reliably and without using potentially toxic or leachable chemical adhesives , by means of a process that is usually called “ ultrasonic welding ”. this process uses focused sound waves at a very high frequency , in a manner that can soften , melt , and join two pieces of compatible plastic that are being pressed against each other . skilled use of this welding method can create the highest local temperatures at a contact zone or interface , where two pieces of plastic are being pressed against each other ( this creation of localized heat is analogous to the way unwanted heat is often created at an imperfect electrical connection , when current is forced through the connection ). if ultrasonic welding will be used to permanently affix the 3d fiber array to an anchoring member , then the polymer that is selected and used to make the backing layer of the fiber array should be different than the polymer used to create the stitches . the backing layer , and the “ weldable polymer ” component of the anchoring member , should be made of a first class of selected polymers that will allow those components to be ultrasonically welded to each other , without affecting the stitches in the 3d fiber array ; and , the stitches in the 3d fiber array should be made of a second class of polymers that will not be affected by the ultrasonic welding operation that will be used to affix a backing layer to an anchoring component . accordingly , fig3 depicts an implant assembly 300 , shown in a simplified cutaway view , before the hydrogel polymer has been added to the implant . this implant comprises a tufted 3d fiber array 100 as illustrated in fig1 , with backing layer 120 , tufts 112 , and a non - tufted “ margin ” 180 of backing layer 120 only , around the periphery of backing layer 120 . the margin 180 of backing layer 120 has been ultrasonically welded to a compatible polymer ring 320 , which is largely enclosed and secured within an annular ring 330 , made of a nitinol - class alloy or other suitable shape - memory material . the polymer ring 320 and annular ring 330 are components of a generally circular or oval anchoring ring . a plurality of anchoring pegs 332 ( illustrated in more detail in above - cited patent application pct / us05 / 43444 ) also are affixed to the anchoring surface of annular ring 330 , at distributed locations . in most cases , it likely will be preferable to weld the reinforcing fiber array to the anchoring member , before the hydrogel material is affixed to the fiber array . sequencing the steps in this manner can avoid any risk that the hydrogel might interfere with ( or be damaged by ) the ultrasonic welding process . fig3 also shows an optional layer 350 , on the anchoring surface of the implant . this optional layer 350 will be impermeable to the prepolymer liquid that will be poured onto the fiber array , to form a reinforced hydrogel . however , it will be designed in any of various known ways that can be used to provide a porous exposed surface 352 on the bottom of the implant , by the time the manufacturing process has been completed . for example , layer 350 can be made of a bilayer material with a nonporous top and a porous bottom ; alternately or additionally , some or all of layer 350 can be embedded with particles or fibers made of a substance that can be removed by a finishing step ( such as , for example , salt particles that can be dissolved by water and rinsed out , or a nontoxic wax with a low melting temperature ). the porous surface on the exposed bottom surface of the implant will encourage tissue ingrowth into that bottom layer , after the surgery has been performed , leading to stronger anchoring of the implant to the bone . whenever a synthetic device is being designed as a replacement for natural tissue , all aspects of the natural tissue ( including its molecular , microscopic , and macroscopic structures , its form , its functions , etc .) should be studied carefully , and kept in mind . as mentioned in the background section , and as shown in photographs by electron microscope ( published in sources such as clark et al 1990 and 1991 ), collagen fibers that establish the structure of natural and healthy hyaline cartilage , in mammals , emerge from the subchondral bone surface in a radial direction ( i . e ., generally perpendicular to the surface of the bone , at the site where the fibers emerge from the bone ). those fibers go through a rounded transition , to reach a generally tangential orientation at the articulating surface of the cartilage . that tangential arrangement of the fibers , on the surface of the cartilage , helps provide a smooth and nonabrasive surface . if a synthetic hydrogel reinforced by a 3d fiber array is being created , an important design principle indicates that the reinforcing fibers should not be exposed , at all , on the smooth articulating surface of the hydrogel . however , despite that principle , there may nevertheless be some value in imparting , to a 3d fiber array made by stitching , a “ bias ” to the tufts or stitches . the term “ bias ” is used herein in a structural and mechanical rather than social or political sense ; however , the overlap in terms becomes apparent , since the result ( in layman &# 39 ; s terms ) is to create strands that will “ lean ” in a certain direction . this type of bias can be “ fixed ” in a way that will render it permanent , for the life of the implant . two different types of fiber biases may turn out to be important in this invention , and both can be evaluated using in vitro tests , on a machine , without requiring any animal testing or clinical trials . one type of bias relates to the directions of any tufted loops or sewn stitches , when considered from a “ plan ” view , while looking down at the articulating surface of a hydrogel implant . for example , because of how the knees are structured , nearly all of the relative motion between femoral runners and tibial plateaus is in a forward and backward direction ( i . e ., along the anterior - posterior axis ), rather than in a side - to - side direction ( along the medial - lateral axis ). therefore , there may be some type of minor and marginal advantage ( which may not become apparent until multiple years have passed , after implantation ), for tufts or stitches that are oriented mainly in an anterior - posterior direction , for femoral runner or tibial plateau implants . this type of bias can be easily provided , merely by programming a computer - controlled stitching machine to do so . wear - testing of such implants , both with and without that type of bias , over millions of stress cycles , can then be performed on a tribometer machine . a different type of fiber bias can be visualized by considering a reinforced hydrogel in an “ elevation ” cutaway view , rather than a plan view . this type of bias , and a method of creating it in reinforcing tufts embedded in a hydrogel , is illustrated in fig4 and 5 . in implant 400 , shown in fig4 , the synthetic tufts 410 are shown as having a transition from vertical , at their base , to horizontal , near the articulating surface of the hydrogel . this is similar to the rounded transition that the collagen protein fibers in natural cartilage pass through , as they travel from the subchondral transition zone ( where they emerge from the bone in an essentially perpendicular or radial direction ), to the articulating surface of a hyaline cartilage segment . this type of biased fiber orientation , to create a transitional structure for strands of synthetic tufts , can be created by any of several approaches . for example , as illustrated by fig4 , it can be created by using a shearing - type displacement of a molding device , comprising a lower tray - type supporting surface 422 , and an upper molding surface 424 . this shearing - type displacement is carried out during a manufacturing step that is normally referred to as curing , setting , hardening , etc ., when a pre - polymer liquid 412 is being chemically converted into its final gelatinous polymer form . alternately or additionally , a displacement step can be carried out on the tufting strands alone , after the tufting material has been properly positioned in a mold , and before the pre - polymer liquid is loaded into the mold . for example , a combing , rubbing , blowing , or similar operation can be carried out on the tufting material , before the liquid is applied . as another option , a molding operation can be carried out at an inclined angle , in a way that allows gravity to help create or sustain the desired bias in the tufting strands . as illustrated in fig5 , a molding tray 500 is positioned at a sloped or slanted angle ( designated as “ alpha ” in fig1 ) relative to the horizontal , while a pre - polymer gel - forming liquid 510 is poured over , spread across , or otherwise applied to a set of reinforcing tufts 512 affixed to a backing layer that rests on the tray surface . in some situations , this type of sloped molding operation may eliminate the need for an upper molding surface . alternately or additionally , this type of sloped arrangement can be used during only a portion of a molding operation , such as during the period when a liquid pre - polymer is initially being poured on top of the tufting material ; subsequently , as the liquid begins to cure into a gelatinous polymer , the molding tray can be rotated into a flat horizontal position . as yet another option , when using some types of polymers , it may be possible to carry out a biasing step by using heat ( or possibly some other suitable treatment , such as addition of a solvent that can later be removed ) to temporarily soften a polymer that has already been created . when softened in this manner , some polymers can be physically manipulated , in a manner that will allow reinforcing fibers to be subjected to a biasing step , and then allowed to cool or otherwise set in a manner that causes them to solidify into a modified configuration . any other currently - known or hereafter - discovered technique or device that provides additional options for use during a molding procedure can also be evaluated for use as described herein . for example , some types of molding operations utilize a specialized “ releasing film ”, which is placed between a molding surface and a moldable material , to ensure that the moldable material does not adhere to the molding surface . alternately or additionally , one or more types of post - setting procedures ( often referred to as finishing or polishing steps , or similar terms ) can also be evaluated for use herein . as one example , application of infrared radiation or other sources of heat can cause the surface of a gelatinous material to soften somewhat , in a manner that may help ensure a completely smooth and flat surface without disturbing or altering a tufting bias that has been imparted to tufting strands that are positioned below the surface of the gel material . a number of test runs were carried out , using an amaya computer - controlled stitching machine under the control of a person who had not previously worked with such a machine , but who was familiar with home - type sewing , and who had attended the basic introductory training program on how to work the machine . roughly two dozen trials were run , each one taking only a few minutes for the machine to complete , once the instructions had been programmed into the machine . these trial runs were for general evaluation purposes only , and the resulting stitched arrays were not intended to be actually embedded in hydrogels that would be tested in vitro or in animals ; therefore , these trial runs used conventional and inexpensive thread from a fabric store , which was stitched onto a conventional inexpensive woven cotton fabric as the backing layer . typically , the results of a small batch of trial runs ( typically involving about 5 to 10 samples , made with various different input parameters that had been controlled by the operator , all of which were recorded in a table or spreadsheet format for comparison and evaluation purposes ) were shown to the surgeon during each session when the surgeon and the machine operator met to discuss the progress of the project . typically , each batch of samples would vary two or three parameters in particular , which had been chosen for evaluation by the surgeon and operator . based on the apparent results for each batch of samples , the surgeon and operator would agree on which samples appeared to have the best traits , and the next set of samples would be made with those varied parameters being held constant , while other parameters were varied . by the time roughly thirty circular or ring - shaped samples had been made and evaluated , the settings that were regarded as being suitable for testing and evaluation in subsequent work generally fell within the ranges listed below . all of these settings used interlocked stitching , created with the aid of a “ floating bobbin ” system beneath the fabric . although some specific parameters use different systems , the numbers used for most parameters refer to “ points ”, in which 10 points equals one millimeter of linear distance . fill stitch length : 5 to 15 provided samples that were fairly tightly packed ; 20 to 40 provided samples that covered larger areas in addition , various presser foot settings were tested , ranging from 0 to 10 . as mentioned above , this parameter is not controlled by software or a computer ; instead , it is adjusted by turning a mechanical wheel that is mounted on the stitching machine . higher numbers , in presser foot settings , will lead to greater stitch lengths and heights , and settings of 5 and 10 generally provided good results , in the materials created in the initial testing stage . the samples that were regarded as most promising usually had both a primary layer of stitching ( which was stitched onto the backing layer in a first stitching operation ), and a secondary layer of stitching ( which was stitched onto the combined backing layer and primary stitching , after the primary stitching operation had been completed ). this approach will create stitched fiber arrays that have greater height and thickness than single - layer stitching . to create stronger , more consistent , and more uniform products , it usually is preferred to have the secondary stitching layer oriented at an angle to the primary stitching layer ( this is analogous to how plywood is created , with the wood fibers oriented in different directions in the layers of a sheet , for maximum overall strength ). the angles that are most commonly used , to give a secondary stitching layer a different orientation compared to a primary stitching layer , are 45 , 90 , or 135 degrees . several relatively long stitch lengths were tested for secondary stitching layers , in several of the samples ( ranging up to 100 units , compared to 20 or 25 units for the primary stitching layer ). multi - layer stitching ( i . e ., using more than two layers ) was not evaluated in the initial round of tests , using cotton threads and fabrics ; however , multilayer stitching can be evaluated for use as described herein , if desired , and anyone testing that approach should evaluate both monofilaments and yarns to form the various layers , since they are likely to perform differently in such uses . hydrogel implants to replace the arc - shaped meniscal cartilage segments in knees are not covered or claimed by this particular application ; however , they are of active interest to the inventors herein , and are covered by other patents and patent applications that remain active . accordingly , a number of arc - shaped prototypes were created and evaluated , using inexpensive cotton thread and fabric as described in example 1 , to narrow down the range of parameters that would need to be tested after trials began with more expensive medical - grade fibers and fabrics . the samples that were regarded as most promising , and worth subsequent evaluation , generally used lower fill densities ( in a range of about 13 to 16 ), while run fill / feed settings of 110 were used in the most promising samples . fill stitch lengths ranging from 20 to 85 were tested ; although they give very different appearances , none were clearly and obviously unsuitable , and the midpoint of that range is regarded as a suitable range for testing , using medical - grade fibers and backing layers to create reinforced hydrogels that will be tested for strength and durability . bilayer and multilayer stitching were not tested in this initial round of arc - shaped segment tests ; however , that approach is believed to be promising , for creating 3d fiber arrays having the thicknesses that will be required to adequately reinforce meniscal wedges , which generally are thicker ( at their thickest points ) than the relatively thin layers of hyaline cartilage that coat the bone surfaces in mammalian joints . thus , there has been shown and described a new and useful type of 3d fiber array , to reinforce hydrogel layers in surgical implants designed to replace hyaline cartilage , which can be created by specialized machines at low cost . although this invention has been exemplified for purposes of illustration and description by reference to certain specific embodiments , it will be apparent to those skilled in the art that various modifications , alterations , and equivalents of the illustrated embodiments are possible . any such changes which derive from the teachings herein , and which do not depart from the spirit and scope of the invention , are deemed to be covered by this invention . clark , j . m ., et al , “ the organisation of collagen fibrils in the superficial zones of articular cartilage ,” j . anatomy 171 : 117 - 130 ( 1990 ) clark , j . m ., et al , “ variation of collagen fiber alignment in a joint surface : a scanning electron microscope study of the tibial plateau in dog , rabbit , and man ,” j . orthopaedic research 9 : 246 - 257 ( 1991 ) karamuk , e ., et al , “ embroidery technology for medical textiles and tissue engineering ,” technical textiles international , july / august 2000 : 9 - 12 lange , j ., et al , “ results of salucartilage implantation for stage iv chondral defects in the knee joint area ,” unfallchirurg . 108 ( 11 ): ( e - published nov . 23 , 2005 ) mcquaid , m ., “ stronger ,” pp . 50 - 55 in extreme textiles ( princeton architectural press , new york city , 2004 ) meyer , c ., et al , “ dislocation of artificial cartilage ( salucartilage ),” unfallchirurg . 108 ( 2 ): 163 - 6 ( 2005 )
implants with hydrogel layers reinforced by three - dimensional fiber arrays can replace hyaline cartilage . such implants should replace an entire cartilage segment , rather than creating a crevice around a plug , so these implants must be thin and flat , they must cover large areas , the tips of any tufts or stitches must not reach the hydrogel surface , and they must be flexible , for arthroscopic insertion . the use of computerized stitching machines to create such arrays enables a redesigned and modified test sample to be made with no delays , and no overhead or startup costs . this provides researchers with improved tools for making and testing implants that will need to go through extensive in vitro , animal , and human testing before they can be approved for sale and use . fiber - reinforced hydrogels also can be secured to strong shape - memory rims , for securing anchoring to bones .