Patent Description:
The present disclosure generally relates to medical fastening devices, and more particularly, relates to sutures and suturing devices for fastening tissue and/or prosthetic material.

The fastening of tissues has long been a need in the medical industry, and correspondingly, a finite number of fastening devices have been developed for different applications and uses. Among these devices are laparoscopic fastening devices or tackers which are often used with minimally invasive procedures such as laparoscopic repair of hernias, and the like. A typical laparoscopic procedure involves the insertion of thin, elongated instruments into relatively small incisions or access ports in the abdomen to access hernia defects in the abdominal wall from the inside. Moreover, the laparoscopic instruments are used to position a prosthetic mesh over the defect and fasten the prosthetic mesh against the inner abdominal wall using tacks, or the like.

Conventional laparoscopic tackers provide a relatively thin and elongated tubular member containing deployable tacks and having an end-firing mechanism positioned at the distal tip thereof. In particular, the end-firing mechanism is configured to deploy tacks directly from the tip of the elongated member in an axial manner, and thus, ideal application suggests positioning the elongated member perpendicularly against the tissue surface to be tacked. However, due to several factors, such as the relatively rigid and elongated nature of the laparoscopic tacker, the limited locations and number of access ports available, and the typical location of hernia defects, it is difficult to position the end of the laparoscopic device squarely against the inner wall of the abdomen. In practice, a surgeon using a laparoscopic tacker typically positions the tacker with one hand, sometimes even slightly bending the instrument, while using his other hand to press against the outer wall of the abdomen in order to achieve the best possible angle for installing the tacks.

Furthermore, due to the limited access to hernia defects and the minimally invasive nature of typical hernia repairs, laparoscopic tackers tend to use simple-action type mechanisms to deploy tacks, and correspondingly, employ tacks with basic means for fastening prosthetic mesh to the inner abdominal wall. More specifically, conventional tackers employ screw-type or simple push-type actions to install tacks with threads or barbs which help embed the tacks within abdominal tissue. Over time, especially in the case of metal, coil-like tacks, these tacks may cause irritation or pain to the patient, become dislodged from the abdominal wall, or cause other complications post-surgery. To address such drawbacks associated with metal tacks, absorbable tacks have been developed and employed. Absorbable tacks are designed to be eventually absorbed by the body, and thus, cause less irritation or pain to the patient over time. However, absorbable tacks also tend to provide holding or tensile strength that is less than optimal. In such cases, suturing the hernia defects or suturing prosthetic mesh to the abdominal wall may prove to be more effective. Even still, the relatively complex nature involved with suturing makes it difficult to use sutures on hernia defects via laparoscopic or otherwise minimally invasive procedures.

Accordingly, there is a need for minimally invasive or laparoscopic means of tissue fastening or installing sutures in tissue which substantially facilitates the installation process for the surgeon or user. There is also a need for a medical fastening device which provides a more effective and reliable means for closing tissue and/or fastening prosthetic mesh to tissue. Furthermore, there is a need for a medical fastening device which employs fasteners that reduce irritation, pain, and other complications to the patient without adversely affecting tissue holding strength. Example of a device for suturing can be found in <CIT>. Example of a tissue fastener can be found in <CIT>.

In accordance with a non-claimed aspect, a suturing device may be provided. The suturing device may include at least a firing aperture, a drive mechanism and an autoloading mechanism. The firing aperture may include at least one needle rotatably disposed therein configured to engage a suture for deployment. The drive mechanism may be operatively coupled to the needle and configured to advance the needle from a retracted position to an extended position during engagement, and retract the needle from the extended position to the retracted position during disengagement. The autoloading mechanism may be operatively coupled to the drive mechanism and configured to slidably retrieve and position a suture to be deployed over the firing aperture after a prior suture has been deployed.

In accordance with another non-claimed aspect, a suturing device may be provided. The suturing device may include at least an elongate member, a drive mechanism and an autoloading mechanism. The elongate member may extend between a working end and a control end, and include a track for receiving one or more deployable sutures therein. The working end may include a firing aperture disposed in communication with the track, and a distal needle and a proximal needle rotatably disposed therein. The drive mechanism may be disposed within the elongate member and configured to operatively couple the control end with each of the distal and proximal needles. The drive mechanism may be configured to advance each of the distal and proximal needles from a retracted position to an extended position during engagement, and retract each of the distal and proximal needles from the extended position to the retracted position during disengagement. The autoloading mechanism may be disposed along the elongate member and proximate the working end. The autoloading mechanism may be operatively coupled to the drive mechanism and configured to slidably retrieve and position one of the deployable sutures over the firing aperture for deployment after a prior suture has been deployed.

In accordance with an aspect of the disclosure, a tissue fastener of the invention is provided in accordance with claim <NUM>. Further embodiments of the invention are provided in the dependent claims.

These and other aspects and features of the disclosure will be better understood upon reading the following detailed description when taken into conjunction with the accompanying drawings.

Referring now to the drawings, and with specific reference to <FIG>, a medical fastening or suturing device is generally referred to by reference numeral <NUM>. The suturing device <NUM>, as will be described in further detail herein, may advantageously enable convenient yet effective means of providing fasteners within a surgical environment. The disclosed embodiments may additionally facilitate the installation of fasteners or sutures during minimally invasive surgical procedures, such as laparoscopic procedures, and the like. As used for laparoscopic treatment of a hernia, the embodiment of <FIG>, for example, may be employed to reach beneath sections of tissue, within or around the abdominal region, to fasten tissues of the abdominal wall or to fasten prosthetic mesh to the abdominal wall from the inside. Although the embodiments disclosed herein demonstrate tissue fastening as applied to laparoscopic applications, it will be understood that the present disclosure may be equally or similarly applied to other medical procedures.

As shown in <FIG>, the suturing device <NUM> may generally include an elongate member <NUM> which extends between a control end <NUM> disposed at a proximal end thereof, and a working end <NUM> disposed at a distal end thereof. The control end <NUM> may generally include a grip <NUM> as well as a triggering mechanism <NUM>, or any other suitable means for receiving input or triggering actions from a user and converting the input or actions into a suturing action that is performed at the working end <NUM> of the suturing device <NUM>. The working end <NUM> may generally be configured with a firing aperture <NUM>, or a fastening interface disposed at a longitudinal side thereof, through which fasteners or sutures <NUM> may be deployed or installed in tissue and/or prosthetic material. Furthermore, one or more of the sutures <NUM> to be deployed may be provided along the elongate member <NUM> and distally advanced or fed toward the firing aperture <NUM> of the working end <NUM>, for example, along one or more guides or tracks <NUM> longitudinally disposed within the elongate member <NUM>.

As shown in more detail in <FIG>, the working end <NUM> of the suturing device <NUM> of <FIG> may at least partially enclose a first needle <NUM> and a second needle <NUM>, each of which may be substantially concealed within the firing aperture <NUM> of the working end <NUM> in a default or fully retracted position. More specifically, the first needle <NUM> may be rotatably and pivotally disposed about a first fixed axis <NUM>, and the second needle <NUM> may be rotatably and pivotally disposed about a second fixed axis <NUM>. Moreover, the first axis <NUM> may be axially offset but substantially parallel to the second axis <NUM>, for example, such that the first needle <NUM> is distally positioned relative to the suturing device <NUM> and the second needle <NUM> is proximally positioned relative to the suturing device <NUM>. In other alternative embodiments, each of the first and second needles <NUM>, <NUM> may be coaxially disposed about a common axis. In still further embodiments, a single needle or more than two needles may be disposed within the firing aperture <NUM> and comprise any one of a plurality of different arrangements.

Still referring to <FIG>, each of the first and second needles <NUM>, <NUM> may be configured to rotate in opposing directions between respective retracted and extended positions. For example, during advancement, the first or distal needle <NUM> may be configured to proximally rotate toward the elongate member <NUM>, while the second or proximal needle <NUM> may be configured to distally rotate away from the elongate member <NUM>. Conversely, during retraction, the first needle <NUM> may be configured to distally rotate away from the elongate member <NUM>, while the second needle <NUM> may be configured to proximally rotate toward the elongate member <NUM>. Moreover, each of the first and second needles <NUM>, <NUM> may be configured to advance and retract between respective retracted and extended positions simultaneously, or in substantially equal increments or at substantially equal rates of angular displacement. Each of the first and second needles <NUM>, <NUM> may further comprise a low-profile arcuate geometry which enables the needles <NUM>, <NUM> to be substantially concealed within the firing aperture <NUM> while in the fully retracted position, and have maximized reach during advancement. Furthermore, each arcuate needle <NUM>, <NUM> may be shaped and/or otherwise configured to rotate in a cammed fashion such that, it creates a progressively tighter pull as it travels through the tissue, and thus, creates a tighter fastening of the tissue.

In addition, each of the first and second needles <NUM>, <NUM> of <FIG> may include one or more of needle hooks <NUM>, grooves, tines, recesses, canted surfaces, or any other suitable structure configured to enable engagement with a fastener or suture <NUM>, or one or more needle guides <NUM> thereof. As shown in <FIG>, for example, a hook <NUM> may be disposed on an outer edge of each of the first and second needles <NUM>, <NUM> and configured to engage with a needle guide <NUM> of a suture <NUM> as the respective needle <NUM>, <NUM> is retracted from the fully extended position. While the embodiments of <FIG> may depict the needles <NUM>, <NUM> with retrograde-type hooks <NUM> configured to engage a suture <NUM> during retraction, it will be understood that other configurations may be equally or similarly employed, such as antegrade-type hooks configured to engage a suture <NUM> during advancement, or the like. In still further alternatives, one or more hooks may be disposed on an inner edge of each of the needles <NUM>, <NUM>.

Turning now to <FIG>, more detailed drawings of the first and second needles <NUM>, <NUM> are provided illustrating the relative rotational positions thereof as the needles <NUM>, <NUM> are advanced from fully retracted positions to fully extended positions. As shown, each of the first and second needles <NUM>, <NUM> may be operatively coupled to a drive mechanism <NUM> that is configured to advance the needles <NUM>, <NUM> from the retracted positions to the extended positions during an engagement of the drive mechanism <NUM> received via the control end <NUM> of the suturing device <NUM>, and conversely, to retract the needles <NUM>, <NUM> from the extended positions to the retracted positions during a disengagement of the drive mechanism <NUM> received via the control end <NUM>. Furthermore, the drive mechanism <NUM> may include a multi-bar linkage, such as a three-bar linkage, or the like, which operatively couples the control end <NUM> to each of the first and second needles <NUM>, <NUM>.

As shown in <FIG>, the drive mechanism <NUM> may include at least a first drive link <NUM> for driving the first needle <NUM> and a second drive link <NUM> for driving the second needle <NUM>, each of which may be slidably disposed within the elongate member <NUM> and in operative communication between the control end <NUM> and the working end <NUM>. The drive mechanism <NUM> may additionally include a first intermediate link <NUM> for driving the first needle <NUM> and a second intermediate link <NUM> for driving the second needle <NUM>, each of which may configured to pivotally couple the corresponding drive link <NUM>, <NUM> to the corresponding needle <NUM>, <NUM>. In other modifications, one or more links may be omitted or added to the drive mechanism <NUM>. As the needles <NUM>, <NUM> are opposedly arranged, the drive links <NUM>, <NUM> and the intermediate links <NUM>, <NUM> may be configured to be slidably and pivotally driven in substantially equal increments or rates of displacement, but in opposing directions relative to one another. For example, during advancement, the first drive link <NUM> of the first needle <NUM> may be slidably driven distally toward the working end <NUM> at substantially the same rate or in similar increments as the second drive link <NUM> of the second needle <NUM> being driven proximally away from the working end <NUM>.

In the fully retracted positions, as shown in <FIG> for example, each of the first and second needles <NUM>, <NUM> may be substantially concealed beneath the firing aperture <NUM> and within the working end <NUM> of the suturing device <NUM> so as to facilitate insertion thereof into minimal incisions or access ports, or the like. The first and second needles <NUM>, <NUM> may further include a low-profile geometry which enables the working end <NUM> of the suturing device <NUM> as well as the access ports to be generally smaller in size. During advancement or during engagement of the drive mechanism <NUM>, as shown in <FIG> for example, the first drive link <NUM> may drive or push the first intermediate link <NUM> toward the distal end of the firing aperture <NUM> thereby causing the first needle <NUM> to rotate about the first fixed axis <NUM> and upwardly extend from the distal end of the firing aperture <NUM>, while the second drive link <NUM> may drive or pull the second intermediate link <NUM> toward the proximal end of the firing aperture <NUM> thereby causing the second needle <NUM> to rotate about the second fixed axis <NUM> and upwardly extend from the proximal end of the firing aperture <NUM>. Moreover, the drive mechanism <NUM> may be configured to rotatably extend the needles <NUM>, <NUM> such that the reach of each needle <NUM>, <NUM> is maximally extended during advancement even with a low-profile geometry so as to sufficiently penetrate tissue and/or prosthetic material to be fastened or sutured.

The drive mechanism <NUM> may continue advancing each of the first and second needles <NUM>, <NUM> until the needles <NUM>, <NUM> respectively reach the fully extended positions, as shown for example in <FIG>. In particular, the drive mechanism <NUM> may be configured such that each of the first and second needles <NUM>, <NUM> extend until at least one or more of the hooks <NUM> thereof engage with a fastener or suture <NUM> for deployment. For example, positioning of the first and second needles <NUM>, <NUM>, the drive mechanism <NUM>, the firing aperture <NUM>, and the sutures <NUM> may be configured such that retrograde-type hooks <NUM> on the outer edges of the needles <NUM>, <NUM> are able to fully engage with one or more corresponding needle guides <NUM> of a given suture <NUM>. In other alternatives, each of the needles <NUM>, <NUM> may employ a retrograde-type hook disposed on the inner edge thereof, an antegrade-type hook disposed on the outer edge thereof, an antegrade-type hook disposed on the inner edge thereof, or any other suitable variation thereof, to which each of the drive mechanism <NUM>, the firing aperture <NUM>, and the like, may be modified to enable sufficient engagement with the corresponding needle guide <NUM> of a given suture <NUM>.

Once the first and second needles <NUM>, <NUM> respectively reach the fully extended positions thereof as shown for example in <FIG>, and once a suture <NUM> is fully engaged, the drive mechanism <NUM> may be released or disengaged, so as to retract the needles <NUM>, <NUM> and deploy the engaged suture <NUM> within tissue and/or prosthetic material to be fastened. Moreover, the needles <NUM>, <NUM> may be retracted toward the positions shown in <FIG> by substantially reversing the drive mechanism <NUM>. During retraction or during disengagement of the drive mechanism <NUM>, for example, the first drive link <NUM> may drive or pull the first intermediate link <NUM> toward the proximal end of the firing aperture <NUM> thereby causing the first needle <NUM> to rotate in reverse about the first fixed axis <NUM> and downwardly retract into the distal end of the firing aperture <NUM>. Correspondingly, the second drive link <NUM> may drive or push the second intermediate link <NUM> toward the distal end of the firing aperture <NUM> thereby causing the second needle <NUM> to rotate in reverse about the second fixed axis <NUM> and downwardly retract into the proximal end of the firing aperture <NUM>. Furthermore, each of the first and second needles <NUM>, <NUM> may be retracted until the needles <NUM>, <NUM> return to the fully retracted positions of <FIG> and until a previously engaged suture <NUM> is completely deployed and released therefrom, at which point the needles <NUM>, <NUM> may be advanced again to engage with a new suture <NUM> for deployment.

While one possible implementation is provided in the drawings, other drive mechanisms and configurations therefor will be apparent to those skilled in the art without departing from the scope of the appended claims. For example, in other modifications, the suturing device <NUM> may employ more than two needles which, for instance, partially oppose one another, or alternatively, rotate in like manner and direction relative to one another. In alternative modifications, the needles <NUM>, <NUM> may be configured to be rotated sequentially rather than simultaneously relative to one another, and/or configured to be rotated at non-identical rates of angular displacement relative to one another. In additional modifications, the needles <NUM>, <NUM> may be configured to rotate about a common axis rather than axially offset. In further modifications, the suturing device <NUM> may provide a needle that is configured to rotate about an axis that is parallel, or otherwise generally not perpendicular, to the elongate member <NUM>. In still further modifications, the working end <NUM> of the suturing device <NUM> may be articulated, such as pivotable or otherwise movable, relative to the elongate member <NUM> about one or more axes.

Referring now to <FIG>, one exemplary triggering mechanism <NUM> that may be employed to operate the drive mechanism <NUM> of <FIG> is provided. As shown, the triggering mechanism <NUM> may be disposed within a housing <NUM> provided at the control end <NUM> of the suturing device <NUM> and configured to interface with the first and second needles <NUM>, <NUM> via the elongate member <NUM> and the drive mechanism <NUM> disposed therein. Furthermore, one or more of the elongate member <NUM> and the drive mechanism <NUM> therein may be rotatably coupled to the housing <NUM> via a rotating collar <NUM> which may be used to adjust the radial position of the firing aperture <NUM> relative to the control end <NUM>. The housing <NUM> may further provide a grip <NUM> relative to which a trigger <NUM> of the triggering mechanism <NUM> may be pivotally anchored by an anchoring pin <NUM> and movable in one of two directions. For example, the trigger <NUM> may be configured to engage the drive mechanism <NUM> and advance the needles <NUM>, <NUM> when pulled toward the grip <NUM>, and disengage the drive mechanism <NUM> and retract the needles <NUM>, <NUM> when pushed away from the grip <NUM>. Correspondingly, as shown in <FIG>, the trigger <NUM> may be provided with a proximal handle <NUM> for pulling the trigger <NUM> toward the grip <NUM>, as well as a distal handle <NUM> for pushing the trigger <NUM> away from the grip <NUM>.

Still referring to <FIG>, the triggering mechanism <NUM> may further include a yoke <NUM> that is rigidly and axially coupled to the elongate member <NUM> and rotatably disposed within the housing <NUM>. The triggering mechanism <NUM> may additionally include a drive collar <NUM> that is axially movable relative to the yoke <NUM> and pivotally anchored to the trigger <NUM> via a lynch pin <NUM>. Furthermore, as shown in <FIG>, the interface between the drive collar <NUM> and the lynch pin <NUM> may be configured such that the drive collar <NUM> is pivotally anchored to the trigger <NUM> irrespective of the rotational position of the drive collar <NUM> relative to the trigger <NUM> and the housing <NUM>. The drive collar <NUM> may additionally be linked to the yoke <NUM> via a collar link <NUM> and a reversing lever <NUM> such that the rotational position of the drive collar <NUM> follows the rotational position of the yoke <NUM>. As shown in <FIG>, for example, the proximal end of the collar link <NUM> may be pivotally as well as radially coupled to the drive collar <NUM>, and the distal end of the collar link <NUM> may be pivotally and radially coupled to the yoke <NUM>.

The triggering mechanism <NUM> of <FIG> may further provide means for translating a single action received by a user at the control end <NUM> of the suturing device <NUM> into two or more simultaneous but opposing actions effectuated at the working end <NUM>. For example, the distal end of the collar link <NUM> may be coupled to the yoke <NUM> via a reversing lever <NUM>, the substantial center of which may be pivotally anchored to the yoke <NUM>. In particular, a first end of the reversing lever <NUM> may be pivotally coupled to a first sliding block <NUM> that is rigidly coupled to the first drive link <NUM> but slidably movable relative to the yoke <NUM>. Correspondingly, a second end of the reversing lever <NUM>, opposite the first end, may be pivotally coupled to a second sliding block <NUM> that is rigidly coupled to the second drive link <NUM> but also slidably movable relative to the yoke <NUM>. In addition, the collar link <NUM> may be pivotally coupled proximate and biased to one of the first and second ends of the reversing lever <NUM> such that, for example, pushing the collar link <NUM> in a distal direction rotates the reversing lever <NUM> relative to the yoke <NUM> in a first direction, and pulling the collar link <NUM> in a proximal direction rotates the reversing lever <NUM> in a second direction opposite to the first direction.

As illustrated in <FIG>, for example, the collar link <NUM> may be coupled proximate to the second end of the reversing lever <NUM> which may further be coupled to the second sliding block <NUM>. In this particular arrangement, when the trigger <NUM> is moved toward the grip <NUM> as indicated by the arrow in <FIG>, the drive collar <NUM> and the collar link <NUM> may be pulled toward the control end <NUM> of the suturing device <NUM>, thereby causing the reversing lever <NUM> to pivot in the manner shown and slidably urge the first sliding block <NUM>, as well as the first drive link <NUM> coupled thereto, in the distal direction while simultaneously urging the second sliding block <NUM>, as well as the second drive link <NUM> coupled thereto, in the proximal direction. Moving the trigger <NUM> in the manner shown in <FIG> may thus cause the drive mechanism <NUM> to engage and actuate the first and second needles <NUM>, <NUM>. Conversely, when the trigger <NUM> is moved away from the grip <NUM> as indicated by the arrow in <FIG>, the drive collar <NUM> and the collar link <NUM> may be pushed toward the working end <NUM> of the suturing device <NUM>, thereby causing the reversing lever <NUM> to pivot in the opposite direction and slidably urge the first sliding block <NUM>, as well as the first drive link <NUM>, in the proximal direction while simultaneously urging the second sliding block <NUM>, as well as the second drive link <NUM>, in the distal direction. Correspondingly, moving the trigger <NUM> in the manner shown in <FIG> may cause the drive mechanism <NUM> to disengage and retract the first and second needles <NUM>, <NUM>.

Turning to <FIG>, the suturing device <NUM> may additionally include an autoloading mechanism <NUM> for successively feeding and automatically loading one of a plurality of sutures <NUM> into position relative to the firing aperture <NUM> for deployment. As shown in <FIG>, for example, a plurality of successively deployable sutures <NUM>, in the form of replaceable suture cartridges, suture ribbons, suture strings, or the like, may be removably inserted along guides or tracks <NUM> disposed within the elongate member <NUM>. The autoloading mechanism <NUM> may provide a pusher member <NUM> that is also slidably disposed along the tracks <NUM> and configured to successively or incrementally urge the sutures <NUM> toward the firing aperture <NUM> for deployment. As shown in <FIG> for example, the pusher member <NUM> may include at least one flexible pusher tab <NUM> extending therefrom that is biased so as to unidirectionally interface with one or more catches <NUM> that are disposed along one of the first and second drive links <NUM>, <NUM> of the drive mechanism <NUM>. Moreover, the pusher tab <NUM> and the catches <NUM> may be configured such that the pusher member <NUM> urges the sutures <NUM> toward the firing aperture <NUM> during engagement of the drive mechanism <NUM> or advancement of the needles <NUM>, <NUM>.

As shown in the particular arrangement of <FIG>, for example, the pusher member <NUM> may be configured such that at least one pusher tab <NUM> engages with one of the catches <NUM> disposed on the first drive link <NUM>, and thereby moves the pusher member <NUM> in direct correspondence with the first drive link <NUM>. In this configuration, as shown in <FIG>, the pusher member <NUM> may be urged to push the sutures <NUM> toward the firing aperture <NUM> while the first and second drive links <NUM>, <NUM> are being engaged and while the first and second needles <NUM>, <NUM> are being advanced. Furthermore, in this particular configuration, when the drive mechanism <NUM> is being disengaged and when the needles <NUM>, <NUM> are being retracted, as shown in <FIG>, the catches <NUM> of the first drive link <NUM> may be free to return and move away from the working end <NUM> while the pusher member <NUM> remains stationary relative to the sutures <NUM> and the firing aperture <NUM>. Moreover, the pusher member <NUM> may include support members <NUM> as shown in <FIG> configured to essentially wedge the pusher member <NUM> within the guides or tracks <NUM> of the elongate member <NUM> and provide the pusher member <NUM> at least some resistance against longitudinal movement therealong. The positioning of the catches <NUM> along the first drive link <NUM> may be spaced according to the distance allotted for each suture <NUM>. In addition, the number of catches <NUM> and the freedom of travel of the pusher member <NUM> may also be configured so as to sufficiently adapt to the changing length of the string of available sutures <NUM> which incrementally shortens after each deployment.

While the embodiments shown may disclose interactions between the pusher tab <NUM> and catches <NUM> provided on the first drive link <NUM>, the pusher tab <NUM> may alternatively interact with catches <NUM> disposed on the second drive link <NUM> or any combination of the first and second drive links <NUM>, <NUM>. In still further alternative embodiments, the pusher member <NUM> may be configured to interact with the drive mechanism <NUM> in other manners not shown, so long as the drive mechanism <NUM> is able to engage the pusher member <NUM> to timely and appropriately urge one or more sutures <NUM> toward the firing aperture <NUM> for deployment upon deployment of a prior suture <NUM>.

While the pusher member <NUM> and the catches <NUM> of the first drive link <NUM> of <FIG> may aid in urging the string of sutures <NUM> toward the working end <NUM> for deployment, the extent to which the sutures <NUM> are pushed may be limited so as not to obstruct the firing aperture <NUM> through which the first and second needles <NUM>, <NUM> will need to extend in order to deploy a prior suture <NUM>. Accordingly, the autoloading mechanism <NUM>, as shown in <FIG>, may further include a shuttle <NUM> configured to retrieve the next suture <NUM> in line for deployment and position the suture <NUM> over the firing aperture <NUM> in alignment with the needles <NUM>, <NUM> upon full deployment and release of a prior suture <NUM>. As shown in <FIG>, the shuttle <NUM> may be slidably disposed along the elongate member <NUM> and beneath the string of sutures <NUM> to be deployed. Moreover, the shuttle <NUM> may be movably disposed in communication between the working end <NUM> and the elongate member <NUM> such that the distance of travel of the shuttle <NUM> extends between at least the firing aperture <NUM> and the next suture <NUM> in line for deployment.

As shown in <FIG>, the shuttle <NUM> may further include one or more suture pawls <NUM> for engaging with a suture <NUM> prior to deployment. More specifically, the suture pawls <NUM> may be configured such that the shuttle <NUM> is engaging when traveling in one direction but non-engaging when traveling in the opposite direction. In the embodiments of <FIG>, for example, each of the suture pawls <NUM> may include a ramped edge <NUM> facing the proximal direction and a hooked edge <NUM> facing the opposite, distal direction. In addition, each of the suture pawls <NUM> may be formed of a partially flexible material and allowed to deflect within recesses <NUM> formed within the shuttle <NUM>. In such a way, the deflectable ramped edges <NUM> may enable the suture pawls <NUM> and the shuttle <NUM> to proximally travel from the firing aperture <NUM> to beneath the sutures <NUM> without substantial obstruction and without adversely affecting the position of the sutures <NUM>. Once the shuttle <NUM> is in the appropriate position beneath the next suture <NUM> in line for deployment, as shown in <FIG>, the hooked edges <NUM> may be upright and in position to slidably engage with the suture <NUM>. As the shuttle <NUM> returns toward the working end <NUM>, the hooked edges <NUM> of the suture pawls <NUM> may distally slide the next suture <NUM> onto the firing aperture <NUM>. Moreover, the suture <NUM> may be positioned such that any needle guides <NUM> thereof are appropriately aligned with one or more corresponding needles <NUM>, <NUM>.

Turning to <FIG>, the autoloading mechanism <NUM> may further interface with the drive mechanism <NUM> to at least cause the shuttle <NUM> of <FIG> to move between the firing aperture <NUM> and the string of suture <NUM>. As shown, the autoloading mechanism <NUM> may include a shuttle pawl <NUM> that is generally disposed beneath the shuttle <NUM> and coupled to one of the first and second drive links <NUM>, <NUM> of the drive mechanism <NUM>. While other configurations are possible, in the particular embodiments shown, for example, the shuttle pawl <NUM> may be coupled to the first drive link <NUM>. Moreover, the shuttle pawl <NUM> may include a ramped edge <NUM> facing the distal direction that is configured such that the first drive link <NUM> and the shuttle pawl <NUM> are freely movable in the distal direction relative to the shuttle <NUM> without substantial obstruction or interference therewith, such as during advancement of the needles <NUM>, <NUM>. As illustrated, the shuttle pawl <NUM> may be formed of a flexible material that can be deflected within a recess <NUM> of the first drive link <NUM>. The shuttle pawl <NUM> may additionally include a hooked edge <NUM> facing the proximal direction that is configured such that the shuttle pawl <NUM> pulls the shuttle <NUM> with the first drive link <NUM> when the first drive link <NUM> moves in the proximal direction, such as during retraction of the needles <NUM>, <NUM>.

As shown more particularly in <FIG>, during engagement of the drive mechanism <NUM> or during advancement of the first and second needles <NUM>, <NUM>, the first drive link <NUM> along with the shuttle pawl <NUM> may be distally pushed toward the working end <NUM> of the suturing device <NUM> in the manner shown. As the shuttle pawl <NUM> approaches the shuttle <NUM>, the ramped edge <NUM> thereof may enable the shuttle pawl <NUM> to deflect into the recess <NUM> of the first drive link <NUM>, and further, enable the shuttle pawl <NUM> to glide under the shuttle <NUM> without altering the position of the shuttle <NUM> relative to the sutures <NUM>. Each of the first drive link <NUM> and the shuttle pawl <NUM> may progress in such a way at least until the hooked edge <NUM> of the shuttle pawl <NUM> reaches and interfaces with the distal end of the shuttle <NUM>. Both the first drive link <NUM> and the shuttle pawl <NUM> may be sized and configured such that the hooked edge <NUM> interfaces with distal end of the shuttle <NUM> once the needles <NUM>, <NUM> are in the fully extended positions and ready to engage and deploy the prior suture <NUM> as shown in <FIG>. Correspondingly, during disengagement of the drive mechanism <NUM> or during retraction of the needles <NUM>, <NUM>, the first drive link <NUM> along with the shuttle pawl <NUM> and the engaged shuttle <NUM> may be proximally pulled toward the string of sutures <NUM> so as to retrieve the next suture <NUM> in line for subsequent deployment.

Once the shuttle <NUM> is sufficiently pulled beneath the next suture <NUM> to be deployed, the shuttle pawl <NUM> may be configured to automatically release the shuttle <NUM> so as to enable the shuttle <NUM> to return to the working end <NUM> and send the retrieved suture <NUM> therewith to the appropriate position over the firing aperture <NUM>. As shown in <FIG>, for example, the autoloading mechanism <NUM> may thus provide a declutch feature, such as a declutch pin <NUM>, or the like, configured to release the shuttle pawl <NUM>, or release the shuttle <NUM> from the first drive link <NUM>, once the shuttle <NUM> is appropriately positioned beneath the next suture <NUM> in line for deployment. For example, the declutch pin <NUM> may be coupled within the elongate member <NUM> and fixedly positioned relative to the shuttle pawl <NUM> such that, as the shuttle pawl <NUM> proximally passes thereby, the shuttle pawl <NUM> is caused to deflect within the recess <NUM> of the first drive link <NUM> and allow the shuttle <NUM> to return to the working end <NUM>. Furthermore, the shuttle pawl <NUM> may further provide a ramped interface <NUM> which proximally precedes the hooked edge <NUM> and is configured to sufficiently deflect and release the shuttle pawl <NUM> from the shuttle <NUM> at the appropriate moment, for instance, when the suture pawls <NUM> of the shuttle <NUM> are ready to engage with the next suture <NUM> in line for deployment.

Still referring to <FIG>, once the shuttle pawl <NUM> is fully deflected, the shuttle <NUM> and the retrieved suture <NUM> may be sent to the firing aperture <NUM> by a bias mechanism <NUM> configured to continuously bias or urge the shuttle <NUM> toward the working end <NUM>. As shown, the bias mechanism <NUM> may employ a compression spring, or the like, that is longitudinally disposed within the elongate member <NUM> and configured to distally push the shuttle <NUM> away therefrom. In further modifications, the proximal end of the shuttle <NUM> may further provide a centering rod <NUM> longitudinally extending therefrom configured to interface with the compression spring of the bias mechanism <NUM> and maintain centering of the shuttle <NUM> relative to the elongate member <NUM> and the firing aperture <NUM>. Similarly, other bias mechanisms <NUM> may be employed to achieve comparable results so long as the biasing force applied upon the shuttle <NUM> in the distal direction does not exceed the force exerted thereon in the proximal direction by the shuttle pawl <NUM> and the first drive link <NUM>.

Turning now to <FIG>, one exemplary embodiment of the autoloading mechanism <NUM> is shown as it progressively retrieves the next suture <NUM> in line for deployment, and appropriately positions the suture <NUM> upon the firing aperture <NUM>. More specifically, as shown in <FIG>, the shuttle <NUM> as well as the suture pawls <NUM> are proximally pulled toward the string of sutures <NUM> as the drive mechanism <NUM> is disengaged or as the needles <NUM>, <NUM> are retracted. As illustrated, the shuttle <NUM> is proximally pulled until at least the suture pawls <NUM> are in position to slidably engage respective sections of the suture <NUM>. For instance, each suture pawl <NUM> may be configured to engage an exterior of a needle guide <NUM> of the suture <NUM>, an interior of a needle guide <NUM>, or any other portion of the suture <NUM> that is suitable for carrying the suture <NUM> to the firing aperture <NUM>. Once released, the shuttle <NUM> and the suture pawls <NUM>, as well as the next suture <NUM> to be deployed, may be distally pushed toward the firing aperture <NUM> while leaving the remaining string of sutures <NUM> behind, as shown for instance in <FIG>. Furthermore, as shown in <FIG>, the shuttle <NUM> may continue carrying the suture <NUM> toward the firing aperture <NUM> until each of the needle guides <NUM> of the suture <NUM> is appropriately aligned to be engaged by the corresponding needle <NUM>, <NUM>.

In addition, as shown in <FIG>, the autoloading mechanism <NUM> may also provide one or more release mechanisms <NUM>, <NUM> for completely deploying or releasing an engaged suture <NUM> from the first and second needles <NUM>, <NUM> during retraction thereof. For example, each release mechanism <NUM>, <NUM> may employ a blade or a cutting edge <NUM> that is longitudinally disposed within the firing aperture <NUM> and fixedly positioned proximate the retracted position of the corresponding needle <NUM>, <NUM> such that, as the needle <NUM>, <NUM> is retracted back into the firing aperture <NUM> and restored to its fully retracted position, the movement thereof relative to the cutting edge <NUM> causes the needle guide <NUM> of the suture <NUM> to be cut and released therefrom. In the particular embodiment of <FIG>, for instance, a first release mechanism <NUM> is fixedly disposed within the firing aperture <NUM> and proximate the first needle <NUM>, while the second release mechanism <NUM> is fixedly disposed within the firing aperture <NUM> and proximate the second needle <NUM>. Moreover, in each release mechanism <NUM>, <NUM>, the cutting edge <NUM> may be specifically positioned such that an engaged suture <NUM> is cut and completely released by the time the corresponding needle <NUM>, <NUM> returns to its retracted position. While only cutting edges <NUM> are shown, the release mechanisms <NUM>, <NUM> may alternatively employ hooks, pawls, ramped edges, or any suitable device capable of releasing the suture <NUM> from the needles <NUM>, <NUM> or hooks <NUM> thereof either by cutting or unlatching the suture <NUM> therefrom.

Referring now to <FIG>, one exemplary embodiment of a tissue fastener or suture <NUM> constructed in accordance with the teachings of the present disclosure is provided. As shown, the suture <NUM> may generally comprise an elongated filament <NUM> extending between a first end and a second end, and at least one needle guide <NUM> disposed at one or more of the first and second ends of the elongated filament <NUM>. The suture <NUM> may be unitarily formed of a material that is sufficiently flexible and compliant so as to be appropriately deployable by a suturing device <NUM>, while also providing sufficient resilience or rigidity to maintain closure between tissue and/or prosthetic material upon deployment. Additionally, the elongated filament <NUM> may be formed with one or more planar curves, such as the S-shaped curve shown, or the like, so as to provide for a more compact overall package and to increase the number of sutures <NUM> that can be made available for deployment, for example, along the elongated member <NUM> of a given suturing device <NUM>. Furthermore, the planar curves of the elongated filament <NUM> may be configured according to the anticipated geometry of the suture <NUM> once deployed and installed within tissue and/or prosthetic material.

Still referring to the sutures <NUM> of <FIG>, each needle guide <NUM> may be sufficiently sized and configured to be engaged by, for example, one of the needles <NUM>, <NUM> of the suturing device <NUM> of <FIG>, or one the needle hooks <NUM> thereof, while also being sufficiently easily released from the needles <NUM>, <NUM>, for example, via any of the release mechanisms <NUM>, <NUM> provided in <FIG>. The needle guides <NUM> may further be shaped, for example, with a relatively tapered tip that is configured to facilitate advancement thereof through tissue and/or prosthetic material during deployment, as well as resist retraction thereof to promote a secure closure. For example, the needle guides <NUM> may be shaped in the substantial form of an oval, an ellipse, a circle, a semi-circle, a triangle, a polygon, or the like. As shown, each needle guide <NUM> may additionally include one or more retention elements <NUM> that are also configured to facilitate advancement thereof through sections of tissue and/or prosthetic material, and further aid in resisting retraction thereof once deployed. The retention elements <NUM> may be shaped in the form of a tine, a fin, a canted element, or any design sufficiently capable resisting retraction through tissue and/or prosthetic material.

Each of the needle guides <NUM> in <FIG> may further be provided with one or more constriction elements <NUM> configured to further secure an engagement between the needle guide <NUM> and a corresponding needle <NUM>, <NUM> or needle hook <NUM> thereof. More specifically, the constriction element <NUM> may be disposed within the needle guide <NUM> in a manner configured to at least partially bias or constrict the needle guide <NUM> against one of the needles <NUM>, <NUM> received therethrough. As shown in <FIG>, for example, the constriction element <NUM> may take the form of a tab, flap, or the like, that is disposed within the needle guide <NUM> and extending toward the tapered end of the needle guide <NUM> or extending toward any other the portion of the needle guide <NUM> that is anticipated to be engaged by a needle hook <NUM>. Moreover, the constriction elements <NUM> may be formed of a material that is sufficiently flexible and compliant so as to receive a needle <NUM>, <NUM> therethrough, but also formed of a material with sufficient resilience and rigidity so as to bias the needle guide <NUM> against the needle <NUM>, <NUM> and needle hook <NUM>.

Turning to <FIG>, one exemplary interaction between the suture <NUM> of <FIG> and a given set of needles <NUM>, <NUM> and respective needle hooks <NUM> is provided. As shown, once the first and second needles <NUM>, <NUM> are advanced into the fully extended positions and received through the respective needle guides <NUM>, the constriction elements <NUM> are caused to bend, thereby pushing or exerting an outward force against the inner edge of the needles <NUM>, <NUM>. This outward pushing force exerted by the constriction element <NUM> may effectively exert a substantially equal and opposite inward force on the tapered end of the needle guide <NUM>, thereby biasing the needle guide <NUM> into the needle hook <NUM> of the respective needle <NUM>, <NUM>. Thus, the constriction elements <NUM> of the sutures <NUM> may provide an otherwise absent constricting force on a received needle <NUM>, <NUM>, which may further serve to secure an engagement between the needle hook <NUM> and the needle guide <NUM> of the suture <NUM>. While disclosed in the form of a tab or flap, the constriction elements <NUM> may be provided on the needle guides <NUM> in any one of variety of different forms, sizes and configurations. Alternatively, the constriction element <NUM> may be configured to substantially close the needle guide <NUM> except for one or more slots, apertures or other voids disposed toward the tapered end thereof in a manner which would effectively bias the needle guide <NUM> against a given needle hook <NUM>. In still further alternatives, the constriction element <NUM> may be completely closed but penetrable by a needle <NUM>, <NUM> in a manner which would effectively bias the needle guide <NUM> against the needle hook <NUM>.

As shown in <FIG>, another exemplary embodiment of a tissue fastener or suture <NUM>-<NUM> that may be used in association with a suturing device <NUM> is provided. Similar to the suture <NUM> of <FIG>, the suture <NUM>-<NUM> shown may generally comprise an elongated filament <NUM>-<NUM> extending between a first end and a second end, and at least one needle guide <NUM>-<NUM> disposed at one or more of the first and second ends of the elongated filament <NUM>-<NUM>. The suture <NUM>-<NUM> may be formed of a material that is sufficiently flexible and compliant so as to be appropriately deployable by a suturing device <NUM>, while also providing sufficient resilience or rigidity to maintain closure between tissue and/or prosthetic material upon deployment. The elongated filament <NUM>-<NUM> of the suture <NUM>-<NUM> may further include a cross member <NUM> as well as filament guides <NUM> configured to stabilize the suture <NUM>-<NUM> as it is moved within the tracks <NUM> and along the elongate member <NUM> of a suturing device <NUM>. For example, the cross member <NUM> may aid in increasing the structural integrity laterally across the suture <NUM>-<NUM> and reduce binding, while the filament guides <NUM> may be sized and configured to interface with the tracks <NUM> of the elongate member <NUM> of a suturing device <NUM> so as to provide the suture <NUM>-<NUM> with additional lateral support and maintain proper alignment thereof. Furthermore, any one or more of the cross member <NUM> and the filament guides <NUM> may be configured with retention features configured to aid in resisting retraction thereof once deployed into tissue and/or prosthetic material.

As in previous embodiments, the needle guides <NUM>-<NUM> of <FIG> may be sufficiently sized and configured to be engaged by a needle <NUM>, <NUM> of a suturing device <NUM>, or one of the needle hooks <NUM> thereof, while also being sufficiently thin or easily released from the needles <NUM>, <NUM>, for example, via any of the release mechanisms <NUM>, <NUM> provided in <FIG>. As shown, the needle guides <NUM>-<NUM> may be provided with a relatively tapered tip, as well as provided with one or more retention elements <NUM>-<NUM>, configured to facilitate advancement thereof through tissue and/or prosthetic material during deployment, and resist retraction thereof to promote a secure closure. Each of the needle guides <NUM>-<NUM> in <FIG> may be provided with constriction elements <NUM>-<NUM> which substantially conform to the shape of the needle guides <NUM>-<NUM> and serve to secure an engagement between the needle guide <NUM>-<NUM> and a corresponding needle <NUM>, <NUM> or needle hook <NUM> thereof. Specifically, each constriction element <NUM>-<NUM> may be configured to increase the integrity or lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is not inserted therethrough, such as when the suture <NUM>-<NUM> is being moved along the tracks <NUM> of the elongate member <NUM> of a suturing device <NUM>, but also configured to effectively reduce the lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is received therethrough, such as during advancement through tissue and/or prosthetic material. As shown in <FIG>, for example, the constriction elements <NUM>-<NUM>, when in the non-deflected state, may substantially fill the width of the needle guides <NUM>-<NUM>, and thereby provide lateral support thereacross. When in the deflected state, the constriction elements <NUM>-<NUM> may enable the needle guides <NUM>-<NUM> to substantially collapse and narrow so as to promote insertion or advancement thereof through a tissue, and the like. Furthermore, the constriction elements <NUM>-<NUM> may continue to provide lateral rigidity and support for the retention elements <NUM>-<NUM> once deployed and released into tissue and/or prosthetic material. For example, once the suture <NUM>-<NUM> is deployed and needle guides <NUM>-<NUM> are released, for instance cut, from the corresponding needles <NUM>, <NUM>, the constriction elements <NUM>-<NUM> may be configured to return to the non-deflected default state and thereby substantially prevent the retention elements <NUM>-<NUM> from collapsing and retracting from the tissue and/or prosthetic material.

As additionally shown in <FIG>, another exemplary embodiment of a tissue fastener or suture <NUM>-<NUM> that may be used in association with a suturing device <NUM> is provided. As in previous embodiments, the suture <NUM>-<NUM> may generally comprise an elongated filament <NUM>-<NUM> extending between a first end and a second end, and at least one needle guide <NUM>-<NUM> disposed at one or more of the first and second ends of the elongated filament <NUM>-<NUM>. The suture <NUM>-<NUM> may be formed of a material that is sufficiently flexible and compliant so as to be appropriately deployable by a suturing device <NUM>, while also providing sufficient resilience or rigidity to maintain closure between tissue and/or prosthetic material upon deployment. The elongated filament <NUM>-<NUM> of the suture <NUM>-<NUM> may further include a cross member <NUM> as well as filament guides <NUM> configured to stabilize the suture <NUM>-<NUM> as it is moved within the tracks <NUM> and along the elongate member <NUM> of a suturing device <NUM>. Additionally, any one or more of the cross member <NUM> and the filament guides <NUM> may be configured with retention features configured to aid in resisting retraction thereof once deployed into tissue and/or prosthetic material.

The needle guides <NUM>-<NUM> of <FIG> may be sufficiently sized and configured to be engaged by a needle <NUM>, <NUM> of a suturing device <NUM>, or one of the needle hooks <NUM> thereof, while also being sufficiently thin or easily released from the needles <NUM>, <NUM>, for example, via any of the release mechanisms <NUM>, <NUM> provided in <FIG>. The needle guides <NUM>-<NUM> may be provided with a relatively tapered tip, as well as provided with one or more retention elements <NUM>-<NUM>, configured to facilitate advancement thereof through tissue and/or prosthetic material during deployment, and resist retraction thereof to promote a secure closure. Each of the needle guides <NUM>-<NUM> in <FIG> may be provided with constriction elements <NUM>-<NUM> configured to further secure an engagement between the needle guide <NUM>-<NUM> and a corresponding needle <NUM>, <NUM> or needle hook <NUM> thereof. Specifically, each constriction element <NUM>-<NUM> may be provided with a widened feature configured to increase the integrity or lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is not inserted therethrough, such as when the suture <NUM>-<NUM> is being moved along the tracks <NUM> of the elongate member <NUM> of a suturing device <NUM>, but also configured to effectively reduce the lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is received therethrough, such as during advancement through tissue and/or prosthetic material. As shown in <FIG>, for example, the widened feature of the constriction element <NUM>-<NUM>, when in the non-deflected state, may substantially abut the inner walls of the needle guide <NUM>-<NUM>, and thereby provide lateral support thereacross. When in the deflected state, the constriction element <NUM>-<NUM> may enable the needle guide <NUM>-<NUM> to substantially collapse and narrow so as to promote insertion or advancement thereof through a tissue, and the like. Furthermore, the constriction elements <NUM>-<NUM> may continue to provide lateral rigidity and support for the retention elements <NUM>-<NUM> once deployed and released into tissue and/or prosthetic material. For example, once the suture <NUM>-<NUM> is deployed and needle guides <NUM>-<NUM> are released, for instance cut, from the corresponding needles <NUM>, <NUM>, the constriction elements <NUM>-<NUM> may be configured to return to the non-deflected default state and thereby substantially prevent the retention elements <NUM>-<NUM> from collapsing and retracting from the tissue and/or prosthetic material.

In still further alternatives, another exemplary embodiment of a tissue fastener or suture <NUM>-<NUM> is provided in <FIG>. As in previous embodiments, the suture <NUM>-<NUM> may generally comprise an elongated filament <NUM>-<NUM> extending between a first end and a second end, and at least one needle guide <NUM>-<NUM> disposed at one or more of the first and second ends of the elongated filament <NUM>-<NUM>. The suture <NUM>-<NUM> may be formed of a material that is sufficiently flexible and compliant so as to be appropriately deployable by a suturing device <NUM>, while also providing sufficient resilience or rigidity to maintain closure between tissue and/or prosthetic material upon deployment. The elongated filament <NUM>-<NUM> of the suture <NUM>-<NUM> may further include a cross member <NUM> as well as filament guides <NUM> configured to stabilize the suture <NUM>-<NUM> as it is moved within the tracks <NUM> and along the elongate member <NUM> of a suturing device <NUM>. Additionally, any one or more of the cross member <NUM> and the filament guides <NUM> may be configured with retention features configured to aid in resisting retraction thereof once deployed into tissue and/or prosthetic material.

The needle guides <NUM>-<NUM> of <FIG> may be sufficiently sized and configured to be engaged by a needle <NUM>, <NUM> of a suturing device <NUM>, or one of the needle hooks <NUM> thereof, while also being sufficiently thin or easily released from the needles <NUM>, <NUM>, for example, via any of the release mechanisms <NUM>, <NUM> provided in <FIG>. The needle guides <NUM>-<NUM> may be provided with a relatively tapered tip, as well as provided with one or more retention elements <NUM>-<NUM>, configured to facilitate advancement thereof through tissue and/or prosthetic material during deployment, and resist retraction thereof to promote a secure closure. Each of the needle guides <NUM>-<NUM> in <FIG> may be provided with constriction elements <NUM>-<NUM> configured to further secure an engagement between the needle guide <NUM>-<NUM> and a corresponding needle <NUM>, <NUM> or needle hook <NUM> thereof. Specifically, each constriction element <NUM>-<NUM> may be provided with a substantially webbed feature configured to increase the integrity or lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is not inserted therethrough, such as when the suture <NUM>-<NUM> is being moved along the tracks <NUM> of the elongate member <NUM> of a suturing device <NUM>, but also configured to effectively reduce the lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is received therethrough, such as during advancement through tissue and/or prosthetic material. As shown in <FIG>, for example, the webbed feature of the constriction element <NUM>-<NUM>, when in the non-deflected state, may provide rigidity and lateral support against the inner walls of the needle guide <NUM>-<NUM>. When the constriction element <NUM>-<NUM> is at least partially deflected state due to the insertion of a needle <NUM>, <NUM>, the needle guide <NUM>-<NUM> may be enabled to substantially collapse and narrow so as to promote insertion or advancement thereof through a tissue, and the like. Furthermore, the constriction elements <NUM>-<NUM> may continue to provide lateral rigidity and support for the retention elements <NUM>-<NUM> once deployed and released into tissue and/or prosthetic material. For example, once the suture <NUM>-<NUM> is deployed and needle guides <NUM>-<NUM> are released, for instance cut, from the corresponding needles <NUM>, <NUM>, the constriction elements <NUM>-<NUM> may be configured to return to the non-deflected default state and thereby substantially prevent the retention elements <NUM>-<NUM> from collapsing and retracting from the tissue and/or prosthetic material.

Referring now to <FIG>, another exemplary embodiment of a tissue fastener or suture <NUM>-<NUM> is provided. As in previous embodiments, the suture <NUM>-<NUM> may generally comprise an elongated filament <NUM>-<NUM> extending between a first end and a second end, and at least one needle guide <NUM>-<NUM> disposed at one or more of the first and second ends of the elongated filament <NUM>-<NUM>. The suture <NUM>-<NUM> may be formed of a material that is sufficiently flexible and compliant so as to be appropriately deployable by a suturing device <NUM>, while also providing sufficient resilience or rigidity to maintain closure between tissue and/or prosthetic material upon deployment. The elongated filament <NUM>-<NUM> of the suture <NUM>-<NUM> may further include a cross member <NUM> as well as filament guides <NUM> configured to stabilize the suture <NUM>-<NUM> as it is moved within the tracks <NUM> and along the elongate member <NUM> of a suturing device <NUM>. Additionally, any one or more of the cross member <NUM> and the filament guides <NUM> may be configured with retention features configured to aid in resisting retraction thereof once deployed into tissue and/or prosthetic material.

The needle guides <NUM>-<NUM> of <FIG> may be sufficiently sized and configured to be engaged by a needle <NUM>, <NUM> of a suturing device <NUM>, or one of the needle hooks <NUM> thereof, while also being sufficiently thin or easily released from the needles <NUM>, <NUM>, for example, via any of the release mechanisms <NUM>, <NUM> provided in <FIG>. The needle guides <NUM>-<NUM> may be provided with a relatively tapered tip, as well as provided with one or more retention elements <NUM>-<NUM>, configured to facilitate advancement thereof through tissue and/or prosthetic material during deployment, and resist retraction thereof to promote a secure closure. Each of the needle guides <NUM>-<NUM> in <FIG> may be provided with constriction elements <NUM>-<NUM> configured to further secure an engagement between the needle guide <NUM>-<NUM> and a corresponding needle <NUM>, <NUM> or needle hook <NUM> thereof. As in the suture <NUM>-<NUM> of <FIG>, the constriction elements <NUM>-<NUM> of <FIG> may be provided with a webbed feature configured to increase the integrity or lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is not inserted therethrough, such as when the suture <NUM>-<NUM> is being moved along the tracks <NUM> of the elongate member <NUM> of a suturing device <NUM>, but also configured to effectively reduce the lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is received therethrough, such as during advancement through tissue and/or prosthetic material. Unlike the previous suture <NUM>-<NUM>, however, the constriction elements <NUM>-<NUM> of the suture <NUM>-<NUM> of <FIG> may be arched or otherwise contrasted with the general plane of the suture <NUM>-<NUM> and biased to exert a lateral force against the inner walls of the needle guide <NUM>-<NUM> when in the non-deflected state. When the constriction element <NUM>-<NUM> is at least partially deflected due to the insertion of a needle <NUM>, <NUM>, the needle guide <NUM>-<NUM> may be enabled to substantially collapse and narrow so as to promote insertion or advancement thereof through a tissue, and the like. Furthermore, the constriction elements <NUM>-<NUM> may continue to provide lateral rigidity and support for the retention elements <NUM>-<NUM> once deployed and released into tissue and/or prosthetic material. For example, once the suture <NUM>-<NUM> is deployed and needle guides <NUM>-<NUM> are released, for instance cut, from the corresponding needles <NUM>, <NUM>, the constriction elements <NUM>-<NUM> may be configured to return to the non-deflected default state and thereby substantially prevent the retention elements <NUM>-<NUM> from collapsing and retracting from the tissue and/or prosthetic material.

Referring further to <FIG>, yet another exemplary embodiment of a tissue fastener or suture <NUM>-<NUM> is provided. Similar to previous embodiments, the suture <NUM>-<NUM> may generally comprise an elongated filament <NUM>-<NUM> extending between a first end and a second end, and at least one needle guide <NUM>-<NUM> disposed at one or more of the first and second ends of the elongated filament <NUM>-<NUM>. The suture <NUM>-<NUM> may be formed of a material that is sufficiently flexible and compliant so as to be appropriately deployable by a suturing device <NUM>, while also providing sufficient resilience or rigidity to maintain closure between tissue and/or prosthetic material upon deployment. The elongated filament <NUM>-<NUM> of the suture <NUM>-<NUM> may also include breakaway tabs <NUM> configured to help stabilize the suture <NUM>-<NUM> as it is moved within the tracks <NUM> and along the elongate member <NUM> of a suturing device <NUM>. As shown, each breakaway tab <NUM> may be coupled between a needle guide <NUM>-<NUM> and a corresponding section of the elongated filament <NUM>-<NUM> in the folded position, and configured to be detachable upon deployment. In particular, the breakaway tabs <NUM> may be sized and configured to provide, not only sufficient planar and lateral rigidity to the suture <NUM>-<NUM> prior to deployment, but also configured with sufficient detachability so as not to interfere with the deployment thereof. As better seen in <FIG>, for example, each of the breakaway tabs <NUM> may incorporate attenuated features <NUM>, such as in the form of grooves, slits, perforations, or the like. Furthermore, the breakaway tabs <NUM> may be angled or otherwise positioned relative to the needle guides <NUM>-<NUM> in a way to help resist retraction thereof once deployed into tissue and/or prosthetic material.

The needle guides <NUM>-<NUM> of <FIG> may be sufficiently sized and configured to be engaged by a needle <NUM>, <NUM> of a suturing device <NUM>, or one of the needle hooks <NUM> thereof, while also being sufficiently thin or easily released from the needles <NUM>, <NUM>, for example, via any of the release mechanisms <NUM>, <NUM> provided in <FIG>. The needle guides <NUM>-<NUM> may be provided with a relatively tapered tip, as well as provided with one or more retention elements <NUM>-<NUM>, configured to facilitate advancement thereof through tissue and/or prosthetic material during deployment, and resist retraction thereof to promote a secure closure. As shown, the edges of the needle guides <NUM>-<NUM> may additionally be beveled, rounded, or otherwise configured to further facilitate advancement thereof. In addition, each of the needle guides <NUM>-<NUM> in <FIG> may be provided with generally linear constriction elements <NUM>-<NUM> positioned to further secure an engagement between the needle guide <NUM>-<NUM> and a corresponding needle <NUM>, <NUM> or needle hook <NUM> thereof. Moreover, the constriction elements <NUM>-<NUM> may serve to increase the integrity or lateral rigidity of each needle guide <NUM>-<NUM> when a needle <NUM>, <NUM> is not inserted therethrough, such as when the suture <NUM>-<NUM> is being moved along the tracks <NUM> of the elongate member <NUM> of a suturing device <NUM>. Furthermore, the constriction elements <NUM>-<NUM> may continue to provide lateral rigidity and support for the retention elements <NUM>-<NUM> once deployed and released into tissue and/or prosthetic material. For example, once the suture <NUM>-<NUM> is deployed and needle guides <NUM>-<NUM> are released from the corresponding needles <NUM>, <NUM>, the constriction elements <NUM>-<NUM> may be configured to prevent the retention elements <NUM>-<NUM> from collapsing and retracting from the tissue and/or prosthetic material.

In addition, the suture <NUM>-<NUM> of <FIG> may further include one or more nesting elements <NUM>, or extended features disposed along the elongated filament <NUM>-<NUM>, which may be sized and configured to detachably couple to a counterpart section of an adjacent suture <NUM>-<NUM> in a string of sutures <NUM>-<NUM>. As shown in <FIG>, for example, each nesting element <NUM> may be configured to couple to the tip of the needle guide <NUM>-<NUM> of an adjacent suture <NUM>-<NUM>. Correspondingly, the tips of each needle guide <NUM>-<NUM> may be beveled, rounded, or otherwise sized and shaped to be mateably received within the nesting elements <NUM> of an adjacent suture <NUM>-<NUM>. In such a way, each suture <NUM>-<NUM> may include two sets of nesting elements <NUM>, such as forward-facing nesting elements <NUM> for coupling to the trailing needle guide <NUM>-<NUM> of a preceding suture <NUM>-<NUM>, and rearward-facing nesting elements <NUM> for coupling to the leading needle guide <NUM>-<NUM> of a subsequent suture <NUM>-<NUM>. Furthermore, the nesting elements <NUM> may be coupled to corresponding sections of adjacent sutures <NUM>-<NUM> using, for example, flexible bonding material or adhesives, friction fitments, attenuated connections, or any other suitable arrangement that is, not only capable of maintaining rigidity of the string of sutures <NUM>-<NUM> prior to deployment, but also capable of being easily detached so as not to interfere with deployment.

Claim 1:
A tissue fastener (<NUM>), comprising:
an elongated filament (<NUM>) extending between a first end and a second end; a needle guide (<NUM>) disposed on each one of the first and second ends, each needle guide configured to be at least partially engaged by a needle (<NUM>, <NUM>) during deployment;
one or more retention elements (<NUM>) disposed on each needle guide (<NUM>) configured to resist retraction through at least one of a tissue and a prosthetic material; and characterised by
one or more constriction elements (<NUM>) disposed within each needle guide (<NUM>) configured to at least partially constrict the needle guide (<NUM>) against the needle (<NUM>, <NUM>) during deployment.