|Publication number||US20010037117 A1|
|Application number||US 09/883,658|
|Publication date||Nov 1, 2001|
|Filing date||Jun 18, 2001|
|Priority date||Sep 30, 1998|
|Also published as||DE69935723D1, DE69935723T2, EP1117334A2, EP1117334B1, EP1792584A2, EP1792584A3, US6248112, US6447522, WO2000018302A2, WO2000018302A3|
|Publication number||09883658, 883658, US 2001/0037117 A1, US 2001/037117 A1, US 20010037117 A1, US 20010037117A1, US 2001037117 A1, US 2001037117A1, US-A1-20010037117, US-A1-2001037117, US2001/0037117A1, US2001/037117A1, US20010037117 A1, US20010037117A1, US2001037117 A1, US2001037117A1|
|Inventors||Richard Gambale, John Ahern, Michael Parascandola|
|Original Assignee||Gambale Richard A., Ahern John E., Michael Parascandola|
|Export Citation||BiBTeX, EndNote, RefMan|
|Referenced by (12), Classifications (23), Legal Events (5)|
|External Links: USPTO, USPTO Assignment, Espacenet|
 This invention relates to delivery devices for implants placeable within tissue of the human body. Specifically, the invention relates to delivery of implants configured to aid in the restoration of blood flow to myocardial tissue of the heart. The invention includes a mechanism to monitor the position of the device and deliver drugs.
 Tissue becomes ischemic when it is deprived of adequate blood flow. Ischemia causes pain in the area of the affected tissue and, in the case of muscle tissue, can interrupt muscular function. Left untreated, ischemic tissue can become infarcted and permanently non-functioning. Ischemia can be caused by a blockage in the vascular system that prohibits oxygenated blood from reaching the affected tissue area. However, ischemic tissue can be revived to function normally despite the deprivation of oxygenated blood because ischemic tissue can remain in a hibernating state, preserving its viability for some time. Restoring blood flow to the ischemic region serves to revive the ischemic tissue.
 Although ischemia can occur in various regions of the body, often tissue of the heart, the myocardium, is affected by ischemia due to coronary artery disease, occlusion of the coronary artery, which otherwise provides blood to the myocardium. Muscle tissue affected by ischemia can cause pain to the individual affected. Ischemia can be treated, if a tissue has remained viable despite the deprivation of oxygenated blood, by restoring blood flow to the affected tissue.
 Treatment of myocardial ischemia has been addressed by several techniques designed to restore blood supply to the affected region. Coronary artery bypass grafting CABG involves grafting a venous segment between the aorta and the coronary artery to bypass the occluded portion of the artery. Once blood flow is redirected to the portion of the coronary artery beyond the occlusion, the supply of oxygenated blood is restored to the area of ischemic tissue.
 Early researchers, more than thirty years ago, reported promising results for revascularizing the myocardium by piercing the muscle to create multiple channels for blood flow. Sen, P. K. et al., “Transmyocardial Acupuncture—A New Approach to Myocardial Revascularization”, Journal of Thoracic and Cardiovascular Surgery, Vol. 50, No. 2, August 1965, pp.181-189. Although others have reported varying degrees of success with various methods of piercing the myocardium to restore blood flow to the muscle, many have faced common problems such as closure of the created channels. Various techniques of perforating the muscle tissue to avoid closure have been reported by researchers. These techniques include piercing with a solid sharp tip wire, hypodermic tube and physically stretching the channel after its formation. Reportedly, many of these methods still produced trauma and tearing of the tissue that ultimately led to closure of the channel.
 An alternative method of creating channels that potentially avoids the problem of closure involves the use of laser technology. Researchers have reported success in maintaining patent channels in the myocardium by forming the channels with the heat energy of a laser. Mirhoseini, M. et al., “Revascularization of the Heart by Laser”, Journal of Microsurgery, Vol.2, No.4, Jun. 1981, pp.253-260. The laser was said to form channels in the tissue were clean and made without tearing and trauma, suggesting that scarring does not occur and the channels are less likely to experience the closure that results from healing. U.S. Pat. No. 5,769,843 (Abela et al.) discloses creating laser-made TMR channels utilizing a catheter based system. Abela also discloses a magnetic navigation system to guide the catheter to the desired position within the heart. Aita U.S. Pat. Nos. 5,380,316 and 5,389,096 disclose another approach to a catheter based system for TMR.
 Although there has been some published recognition of the desirability of performing transmyocardial revascularization (TMR) in a non-laser catheterization procedure, there does not appear to be evidence that such procedures have been put into practice. For example, U.S. Pat. No. 5,429,144 Wilk discloses inserting an expandable implant within a preformed channel created within the myocardium for the purposes of creating blood flow into the tissue from the left ventricle.
 Performing TMR by placing stents in the myocardium is also disclosed in U.S. Pat. No. 5,810,836 (Hussein et al.). The Hussein patent discloses several stent embodiments that are delivered through the epicardium of the heart, into the myocardium and positioned to be open to the left ventricle. The stents are intended to maintain an open channel in the myocardium through which blood enters from the ventricle and perfuses into the myocardium.
 Angiogenesis, the growth of new blood vessels in tissue, has been the subject of increased study in recent years. Such blood vessel growth to provide new supplies of oxygenated blood to a region of tissue has the potential to remedy a variety of tissue and muscular ailments, particularly ischemia. Primarily, study has focused on perfecting angiogenic factors such as human growth factors produced from genetic engineering techniques. It has been reported that injection of such a growth factor into myocardial tissue initiates angiogenesis at that site, which is exhibited by a new dense capillary network within the tissue. Schumacher et al., “Induction of Neo-Angiogenesis in Ischemic Myocardium by Human Growth Factors”, Circulation, 1998; 97:645-650. The authors noted that such treatment could be an approach to management of diffused coronary heart disease after alternative methods of administration have been developed.
 The present invention provides a delivery system for placing implants within tissue in the human body. The implant delivery system of the present invention provides several novel features, which are useful in delivering implants into tissue.
 In one aspect of the invention a delivery device is provided that is especially configured to carry multiple tubular shaped implants at its distal end, engaging the implants by their inside surfaces. The delivery devices are inserted percutaneously into a patient and navigated to the site where the implant is to be located. The delivery systems of the present invention are particularly well suited for delivering implants into the myocardium to perform transmyocardial revascularization (TMR). Implants such as stents may be placed by the delivery device into the myocardial tissue to a proper depth to encourage revascularization of ischemic tissue. In such a procedure, positioning the implants into the proper depth within the myocardium is important to the success of the procedure because it has been observed that areas of the myocardium closer to the endocardial surface and to the epicardial surface are more likely to be responsive to revascularization. Additionally, spacing of the implants relative to one another in an area of ischemic tissue is important to the success of the revascularization process and avoiding undesirable side effects of placing foreign objects in the muscle tissue of the myocardium. Additionally, it may be desirable to deliver a therapeutic substance to the implant location, before, after or during delivery of the implant to promote revascularization activity such as angiogenesis. The features of the present invention address these concerns as will be discussed in greater detail below.
 Reaching the intended implant delivery location with the delivery devices of the present invention first requires placement of a guide catheter prior to navigation of a deliverable catheter into the left ventricle. A steerable catheter that is placeable within the left ventricle and positionable in multiple locations with one catheterization is disclosed in U.S. application Ser. No. 09/073,118 filed May 5, 1998, the entirety of which is herein incorporated by reference. The delivery devices as described herein are insertable through the lumen of the delivery catheter and are extendible pasts its distal end to place the implants within the myocardial tissue. The delivery catheter provides directional control so that the delivery devices of the present invention can deliver multiple implants to a variety of locations within a given area of ischemic tissue.
 In one embodiment of a delivery device of the present invention the device comprises a catheter having a compressible sleeve at its distal end which forms into a plurality of random folds when it is compressed expanding its diameter and serving to capture the inside surface of any tubular object placed over it. The crinkle tube may be formed from a polymer such as polyethylene terethalate (PET). The crinkle tube can securely retain tubular implants over its crinkle, radially expanded surface to a sufficient degree such that delivery into tissue does not push the implant off of the delivery device. Additionally, the crinkle tube catheter may be used in conjunction with an outer catheter shaft having a plurality of interior projections which engage a plurality of implants in cue while the crinkle tube shaft delivers the implants from the distal end of the catheter sequentially.
 In another embodiment, a tubular implant is maintained on the catheter behind an oval shaped segment of the catheter which presents a larger profile than the inside diameter of the tubular implant. A member is slidable within the catheter engages the oval portion to deform into a round shape, thereby permitting the implant to slip off the distal end of the shaft. Simultaneously with deformation of the oval to a circle shape, the inner member causes arms to protrude from the interior of the catheter and to engage the implant and push it in a distal direction so that it becomes implanted in the tissue. Additionally, the catheter has the ability to carry multiple implants over its shaft. The implants waiting in cue are also maintained in position on the shaft by a oval shape segment of the shaft that can be deformed to a circular shape thereby permitting advancement of the next implant.
 In yet another embodiment of the delivery system, the delivery catheter comprises an elongate shaft that contains pressurized fluid within its lumen to motivate a plunger located at the distal end of the shaft and attached to a single implant attachment device. When fluid within the lumen of the delivery catheter is pressurized, the plunger moves from its position against proximal stops distally to its position against distal stops. That length of travel is sufficient to push the implant attached to the plunger into the intended tissue location. The benefit of the fluid pressure delivery system is the reduction in moving components needed to cause distal movement of the implant at the distal end of the catheter from the proximal end of the catheter which is manipulated outside of the patient.
 Another feature of the present invention includes a dual bladder drug delivery system which may be associated with the delivery catheters discussed above. The dual bladder arrangement provides a first bladder which contains a therapeutic substance near the distal end of the delivery catheter and a second bladder arranged near the first bladder so as to impinge upon the space of the first bladder when the second bladder is inflated. The second bladder is inflated with an inexpensive fluid simply to cause the evacuation of the first bladder, which contains a therapeutic substance to be delivered. The first bladder may be provided with a series of perfusion ports through which the therapeutic substance can be forced through when pressurized by the reducing volume imposed by the inflation of the second bladder.
 The benefit of the system is to avoid the waste of expensive therapeutic substances by filling an entire full length lumen with the substance in order to force it from the distal end of a delivery catheter. With the dual bladder delivery system, an expensive fluid can be used to occupy the space along the full length of the delivery catheter, yet its pressurization force can be applied to deliver a small quantity of the therapeutic substance maintained only at the distal end of the catheter.
 Another feature of the present invention is a depth monitor, which may be applied to any of the above delivery catheters. The depth monitor uses changes in pressure being measured at the distal end of the catheter to signal the operator that the distal end of the catheter has been placed within myocardial tissue to a certain depth sufficient to implant the device. This depth monitoring is accomplished by providing one or a plurality of pressure ports at the distal end of the catheter that will be inserted into tissue in order to deliver the implant that it carries. The pressure port(s) are spaced a known distance from the distal end of the delivery catheter. The interior lumen of the catheter can transmit the pressure experienced at the distal end of the catheter through individual lumens to the proximal end where a pressure monitoring device for each pressure port is attached to the proximal end of the delivery device. When the distal end of the delivery catheter is in the left ventricle, pressure readings at the distal end will be dynamic. However, after the distal end of the delivery catheter enters the tissue to implant the device, the pressure ports become covered with surrounding tissue resulting in dampened or static signal. The most proximal pressure port when covered by the surrounding tissue, will act likewise and signals the operator that the distal end of the delivery catheter has been placed to a sufficient depth within the tissue to deliver the implant.
 Another feature of the present invention is a navigation system utilizing magnetic fields transmitted over the body to identify the location within a patient of a catheter having sensing electrodes that interact with the electromagnetic coils. Computer software processes the information obtained from the magnetic pick-up coils and places the catheter on a virtual image of the heart to give the operator a general idea of where the catheter is located and what areas of ischemic tissue have been treated with implant devices. Because the delivery devices of the present invention are capable of delivering more than one implant to an area of ischemic tissue with one catheterization, a navigation system helping to guide the placement of the delivery catheter and implants is helpful.
 It is an object of the present invention to provide an implant delivery system that is simple and effective to use. It is yet another object of the present invention to provide an implant delivery system that is suitable for varying implant devices to the myocardium of the heart that will aid in revascularization of ischemic tissue.
 It is yet another object of the invention to provide an implant delivery device that operates to grasp a tubular shaped implant by its inside surface. The implant may be inserted into tissue. It is another object of the invention to provide an implant delivery device that utilizes fluid pressure through the delivery catheter to insert the implant into the subject tissue.
 It is yet another object of the invention to provide an implant delivery device that includes a dual bladder drug delivery system that reduces waste of expensive therapeutic substances in its application to a treatment site through a catheter.
 It is still another object of the invention to provide a depth monitor capable of being associated with a delivery device that utilizes pressure sensed at the distal end of the catheter to reliably determine the location of the distal end of the device.
 It is yet another object of the invention to provide a navigation system that is capable of identifying the location of a catheter delivering mechanical TMR inducing devices, within the human heart so that the catheter can be moved to various locations delivering multiple devices with one insertion into the heart.
 The foregoing and other objects and advantages of the invention will be appreciated more fully from the following further description thereof, with reference to the accompanying diagrammatic drawings wherein:
FIG. 1 shows a sectional illustration of the left ventricle of a human heart;
FIG. 2A-2D illustrate the steps of percutaneously delivering an implant to an area of the myocardium;
FIG. 3A is a partial sectional illustrational of the crinkle tube delivery device;
FIG. 3B is a detail of the crinkle tube in compression;
FIG. 3C is a detail of the crinkle tube in tension;
FIG. 3D is a partial sectional illustration of the crinkle tube device delivering an implant;
FIG. 3E is a partial sectional illustration of the crinkle tube device being withdrawn from the implant location;
FIG. 3F is a partial sectional illustration of a delivery device having a depth monitor;
FIG. 4A-4C are partial sectional illustrations of a multiple implant device;
FIG. 5A is a partial sectional view of a oval tube delivery device;
FIG. 5B is a sectional view taken along the line 5B-5B of FIG. 5A;
FIG. 5C is a sectional view taken along the line 5C-5C of FIG. 5A;
FIG. 6A is a partial sectional view of an oval tube delivery device;
FIG. 6B is a sectional view taken along the line 6B-6B of FIG. 6A;
FIG. 60 is a sectional view taken along the line 6C-6C of FIG. 6A;
FIG. 7A is a partial sectional view of an oval tube delivery device;
FIG. 7B is a sectional view taken along the line 7B-7B of FIG. 7A;
FIG. 7C is a sectional view taken along the line 7C-7C of FIG. 7A;
FIG. 8 is a sectional view of a pressurized fluid delivery device;
FIG. 9A is a sectional view of a double bladder therapeutic substance delivery device;
FIG. 9B-9C are sectional views of the double bladder therapeutic substance delivery device.
 DESCRIPTION OF THE ILLUSTRATIVE EMBODIMENTS
FIG. 1 shows a sectional illustration of the left ventricle 2 of a human heart 1. Several implants 8 are placed within the myocardium 4 adjacent the endocardial surface 6. As shown in FIGS. 2A-2D, access to the endocardial surface 6 of the myocardium 8 is gained through a steerable delivery catheter 36 inserted into the left ventricle 2. It is through the delivery catheter 36 that the delivery devices of the present invention are inserted to carry the individual implants into the myocardial tissue 8. The steerable delivery catheter 36. It is noted, throughout the description of the delivery devices and their associated methods, “proximal” refers to the direction along the delivery path leading external of the patient and “distal” refers to the direction leading internal to the patient.
 To access the left ventricle of the heart percutaneously, a guide catheter (not shown) may be navigated through the patient's vessels to reach the left ventricle 2 of the heart 1. A barbed tip guidewire 34 may then be inserted through the guide catheter and into the ventricle where it pierces the myocardium 4 and becomes anchored within the tissue. After anchoring the guidewire, the steerable delivery catheter 36 may be advanced over the guidewire to become positioned within the ventricle in close proximity to the endocardium to facilitate delivery of implants. To facilitate delivery of multiple implants, the guidewire lumen of the delivery catheter 36 may be eccentrically located on the catheter. Therefore, when the catheter is rotated about the guidewire, the center of the catheter will rotate through a circular path as demonstrated in FIGS. 2C and 2D, to encompass a broader delivery area with only a single guidewire placement. The outside diameter of the delivery catheter is preferably less than 0.100 inch. Additionally, the delivery catheter may be provided with steering capability by means of a pull wire extending the length of the catheter and attached at its distal end such that pulling on the wire from the proximal end causes the distal tip of the catheter to be deflected. Therefore, the steering capability provides a broader range of delivery area with a single catheterization. A detailed description of the construction of a delivery catheter for reaching multiple sites within the left ventricle is described in U.S. patent application Ser. No. 09/073,118 filed May 5, 1998, the entire disclosure of which is herein incorporated by reference.
FIG. 3A shows a partial cut-away view of a preferred delivery device 10 for the TMR implants 8. The delivery device 10 shown in FIG. 3A may be used with a guide catheter 12 rather than the steerable catheter 36 discussed above. A delivery device 10 comprises an elongate solid shaft 14 having a sharp obturator head 16 at its distal end. The obturator head 16 is formed at the distal end of the core wire 14 by any convenient means of building a mass at the end of a core wire. For example, several thin and small sleeves and springs may be amassed at the distal end and melted together to form a bulbous tip which is later ground to form a sharp, piercing tip 18. Included within the mass of melted materials that form the distal obturator head 16, should be a radiopaque material such as gold or platinum to make the distal area of the device visible under fluoroscopy. Heat bonded to the proximal end 20 of the obturator head 16 is a flexible crinkle tube 22, shown in detail in FIG. 3B, formed from polyethylene terephthalate (PET): Attached to the proximal end 24 of the crinkle tube 22 by heat bonding is push tube 26 which is formed from a closely wound spring having a PET shrink tube formed around its outer surface filing in the voids created by the coils. The crinkle tube 22 collapses under compressive load to form a random pattern of folds 28, which serve to increase the overall diameter of the crinkle tube such that it comes into frictional contact with the inside diameter of a hollow or generally tubular implant 8 that is placed over it. When placed in tension as shown in FIG. 3C, the crinkle tube elongates and returns to a low diameter configuration without folds. The configuration of the crinkle tube is manipulated by relative movement of the core wire 14 having its obturator 16 joined to the distal end 25 of the crinkle tube relative to the push tube 26, which is joined to the proximal end of the crinkle tube 24. The shaft and push tube are slidable relative to each other and controllable from the proximal end of the device by a handle 38 and core wire extension 30. Movement of the handle and push tube in a distal direction and movement of the core wire and its extension in the proximal direction compress the crinkle tube 22 to capture the interior of an implant 8 for delivery into tissue as shown in FIG. 3A. It is in this large diameter, crinkled configuration that the delivery device must maintain to restrain the implant during delivery into tissue. As shown in FIGS. 3D and 3E after delivery into tissue, the crinkle tube may be placed in tension, to withdraw the plurality of folds that engage the interior of the implant 8. With the crinkle tube 22 placed in a low profile configuration, the core wire extension 30 is advanced distally within the handle 38 and handle 38 advanced distally into the associated guide catheter 12 as shown in FIG. 3D. After reducing the profile of the crinkle tube 22 the implant easily slides off of the crinkle tube 22 over the obturator 16 as the device is withdrawn from the tissue as shown in FIG. 3E.
 An alternative embodiment of the crinkle tube delivery device may be additionally equipped with a pressure dependent depth monitor. The depth monitor may be comprised of at least one pressure port 21, shown in FIGS. 3B and 3F, formed in the push tube 26 adjacent its distal end 27 and location of the crinkle tube 22 and implant. Pressure sensed through the port 21 is transmitted through lumen defined by the push tube and is detected by a pressure detector 31 joined to the handle 38. Readings from the pressure detector may be shown on a hydraulic gauge or electronic readout.
 The location of the pressure port 21 is a significant factor in interpreting the pressure information for proper implant delivery. When the pressure port is open to the left ventricle, pressure readings are dynamic. However, when the pressure port 21 is submerged and covered by tissue, pressure readings drop or become static. With placement of the pressure port just proximal of the implant mounting location on the push tube, a significant pressure dampening during delivery of an implant will signal the operator that, not only has the pressure port become embedded in the tissue, but also the implant, located distal to the pressure port, has become sufficiently imbedded in the tissue. Thus the implant can be released from the delivery device and into the tissue. Multiple pressure ports spaced along the distal end of the delivery device can provide an indicator of how deep the delivery device is in the tissue because as each successive pressure is monitored.
FIG. 4A shows a variation of the crinkle tube delivery device, which is configured to sequentially delivery several preloaded implants 8. The multiple implant delivery device 34 operates much the same way as the single implant delivery device described above. The crinkle tube 22 grips the most distal implant 8 only, while the other implants wait in cue within the guide catheter 12 and over the push tube 26. The additional implants are restrained in their relative positions behind the most distal implant by resilient fingers 44 which project inwardly from the interior wall 46 of guide catheter 12. After the most distal stent is urged out of the guide catheter by the distal movement of the core wire and push shaft, as shown in FIG. 4B, the core wire and push shaft may be retracted back into the guide catheter as the remaining stents are indexed distally by the sliding distal movement of index cue 40 which may be manually slidable within the guide catheter 12 by indexing shaft 42. As the core wire 14 and push tube 26 are withdrawn proximally back into the guide catheter, the area of the crinkle tube 22 resides in the interior of the newly placed most distal stent. The push tube and core wire are again moved relative to each other to cause compression along the crinkle tube 22 so that the folds 28 of the crinkle tube 22 contact the interior surface of the next implant 8 to be delivered. The next implant to be delivered is preferably placed in a different location, spaced apart from the first implant by movement of the guide catheter 12 to a new area.
 FIGS. 5A-C shows another embodiment of the implant delivery device 50. The device operates to maintain an implant 8 over its outer shaft 54 by having a distal oval area where the shaft defines an oval cross-sectional shape, as shown in FIG. 5B, that defines a diameter that is larger than the circular shape of the tubular implant 8, to thereby preventing the implant from sliding off the end of the outer shaft 54. Additionally, the proximal oval area 68 on the outer shaft 54 maintains the implant 8 that is second in line in its mounted configuration on the catheter shaft. The natural tendency of the shaft 54 to maintain an oval shape at these areas serves to lock the implants 8 in place on the shaft as is shown in FIG. 5A. It is in this locked configuration that the most distal implant is navigated to the myocardium. The oval areas of the outer shaft 54 lock the implants in place so that they do not move as they are navigated to the tissue location.
 FIGS. 6A-C shows an implant 8 being delivered from the oval shaft embodiment 50. Once the delivery device is adjacent the tissue to be penetrated, the shaft 52 is advanced distally causing the sharpened distal tip 70 of the shaft to emerge from the distal end 72 of the delivery device. The sharpened distal tip 70 pierces tissue as it is advanced in a distal direction to facilitate insertion of the implant 8 into the tissue. Also with the distal movement of the shaft 52, the distal cam 56 moves into engagement with the distal shims 62, thereby causing the naturally oval area 66 to be elastically deformed into a round shape as is shown in FIG. 6B. The round configuration of the outer shaft 54 in this area permits the round implant to slide off the distal end of the device. Further distal movement of the shaft 52 causes distal movement of the split tube 76, which is engaged by the proximal cam 60 joined to the shaft 52 . The vanes 78 of the split tube move distally and curve radially outward through radial passages 80 formed into the sidewall of the outer shaft 54 to engage the interior of the most distal implant. The natural curvature of the vanes and the presence of biasing member 84 underneath the vanes urge them in a radially outward direction so that as they are moved distally within the shaft 54 the vanes are urged out of the radial passages 80 that are formed in the tube. Though the vanes serve to push the implant into the desired tissue location, their radial extent from the catheter shaft 54 could potentially interfere with the passage of the proximal end 9 of the implant over the vanes. Therefore, to ensure that the implants are not hindered as they are pushed off the catheter shaft, the implants used with the present embodiment of delivery device should be configured to have a proximal opening that is larger than the distal opening and as large as the maximum extent of the natural extent of the vanes.
 During delivery into the myocardium the proximal oval area 68 is maintained in the oval configuration to lock in place on the shaft 52 the implants 8 that are in cue to be delivered. However, after delivery of an implant into tissue, the shaft is retracted proximally within the shaft 54 to shield the sharp distal tip 70 from tissue during movement of the shaft to the next location, as shown in FIG. 7A. Distal movement of the shaft 52 also causes the proximal cam 60 to engage the proximal shim 62 located on the inner surface of the outer shaft lumen directly adjacent the proximal oval area 68, which forces the shaft to become circular temporarily in that area, as shown in FIG. 7C. Thus the secondary implants become free to cue forward, the next implant 8 moving up to be the next delivered. The arrangement of cams on the shaft dictates that when the proximal oval area is deformed to be round, the distal oval area remains in its undeformed oval configuration to prevent continued distal movement of implants 8 distally on the shaft until they are ready to be delivered into tissue.
FIG. 8 is partial sectional view of another embodiment of the delivery device of the present invention that uses pressurized fluid to provide the implantation force needed to insert a self-piercing stent into myocardial tissue. The fluid pressure delivery device 90 comprises an elongate shaft 92 having at least one lumen 94, which carries the pressurized fluid 96 such as water or saline. The fluid and a pressurization source are joined to the lumen at proximal luer fitting 98. The shaft may have a guidewire lumen 99 containing a barbed tip guidewire 34, as with the delivery catheter 36 described above . The barbed tip guidewire implanted within adjacent tissue helps provide leverage to resist movement of the distal tip 100 of the catheter when when substantial fluid force is being applied to the tissue surface by the entering implant 8.
 The distal portion 102 of the lumen 94 is configured as a track 104 to receive a slidable plunger 106 that forms a fluid tight seal with the track. Fluid pressure within the lumen 94 creates a force against the plunger causing it to slide distally. The plunger has joined to its distal face a catch member 108 that is configured to be releasably engagable with the interior of an implant 8 with which the device is intended to deliver into tissue. The extent of travel of the plunger within the track 104 is limited by proximal stops 110 and distal stops 112 that engage the plunger to limit its movement so that it does not become disassociated from the shaft lumen 94 when travel is maximized. To avoid the necessity of attaching a piercing member to the plunger, self-piercing implants are preferred for use with the present embodiment, such as shown in FIG. 8. Examples of self piercing implants intended for placement in the myocardium are described in U.S. patent application Ser. No. 09/073,118, filed May 5, 1998.
 FIGS. 9A-9C show a double bladder therapeutic substance delivery system 110 that may be employed with the implant delivery systems of the present invention that can be configured to have an open lumen through their lengths. In particular the crinkle tube 22 and oval shaft 50 embodiments may be configured to employ the therapeutic substance delivery system 110. FIG. 9A shows a double bladder system 110 positioned within the central lumen 112 of a tube 111 of an implant delivery system similar to the crinkle tube delivery device. It is noted that other implant delivery sytems or catheter devices not disclosed herein may employ the therapeutic substance delivery system or the system could be deployed alone through a conventional catheter having a lumen.
 The drug delivery system shown in FIGS. 9A-9C employs a first flexible bladder 114 filled with a therapeutic substance and mounted about a tube,116 and in close longitudinal proximity to (FIG. 9B), or surrounding (FIG. 9C) a second flexible bladder 118 attached to the shaft 116 and inflatable with a conventional medium such as saline. The second bladder 118 is in fluid communication with a lumen 120 that extends through shaft 116 via a port 122. Expansion of the second bladder 118 within a confined space such as within a lumen 112 adjacent the first bladder 114 (FIG. 9B) or from within the first bladder (FIG. 9C) applies pressure to the first bladder, reducing its volume which increases fluid pressure in the first bladder sufficiently to cause the therapeutic substance to be ejected through tiny orifices 124 to the intended treatment site.
 The bladders may be similar to dilatation balloon in their shape, size and manner of attachment to the shaft 116. The bladders may be made from a strong but flexible material such as PVC or Nylon. The bladders may be approximately the same size so that volume reduction of the first bladder corresponds to the volume expansion of the second bladder. The first bladder may be filled with a therapeutic substance during the process of joining it the bladder to the shaft. After bonding the proximal neck 130 to the shaft, the catheter may be oriented so that the distal neck 132 is elevated. In this orientation, the therapeutic substance can be injected, by a syringe, inserted between the distal neck and the shaft, without the chance of the substance running out of the bladder or contaminating the bonding area between the distal neck and the shaft. After filling the bladder 114 with the substance, the distal neck is bonded to the shaft.
 A plurality of tiny orifices 124 may be preformed in the drug bladder prior to use of the device and either prior or after being filled with the substance and bonded. Because the orifices are small, on the order of 0.001″, and the substance within the first bladder is not pressurized it is expected that most therapeutic substances can be formulated to have a sufficiently high viscosity that the substance will not leak out from the orifices in the absence of pressure applied by the second bladder. For this reason, an alternative method of prefilling the first bladder with a therapeutic substance may comprise the steps of piercing the surface of a bladder with a tiny syringe needle and injecting the substance through the bladder wall.
 Another aspect of the invention utilizes electromagnetic guidance technology to provide a guidance system for use with an implant delivery system such as the systems discussed above. U.S. Pat. No. 5,769,843 (Abela), the entirety of which is incorporated herein by reference, discloses such a guidance system for positioning a laser catheter within the ventricle of the heart. An electromagnetic guidance system would be especially useful in the delivery of multiple mechanical implants to an area of ischemic myocardial tissue such as is described above. The delivery devices of the present invention may be equipped with two non-coplanar magnetic sensing coils in the distal ends of their shafts to cooperate with three sets of three magnetic fields generating external coils located outside the patient. The sensing coils of the catheter receive tthe electromagnetic field and thus, with assistance with from a computer can be located within the patient.
 From the foregoing, it will be appreciated that the invention provides delivery devices for delivering implants and therapeutic substances to the myocardium. The invention is particularly advantageous for delivering devices and therapeutic substances to promote TMR and angiogenesis within ischemic myocardial tissue. The implants are simple and readily insertable into the intended tissue location with a minimum of steps. The delivery systems are simple to operate to implant the devices quickly.
 It should be understood, however, that the foregoing description of the invention is intended merely to be illustrative thereof and that other modifications, embodiments and equivalents may be apparent to those skilled in the art without departing from its spirit. Having thus described the invention what we desire to claim and secure by letters patent is:
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US6605053||Sep 8, 2000||Aug 12, 2003||Percardia, Inc.||Conduit designs and related methods for optimal flow control|
|US6610100||Apr 10, 2001||Aug 26, 2003||Percardia, Inc.||Designs for left ventricular conduit|
|US6638237||Aug 1, 2000||Oct 28, 2003||Percardia, Inc.||Left ventricular conduits and methods for delivery|
|US6641610||Aug 4, 1999||Nov 4, 2003||Percardia, Inc.||Valve designs for left ventricular conduits|
|US6962574||Jun 13, 2003||Nov 8, 2005||Biomet Manufacturing Corp.||Therapeutic agent delivery device|
|US7704222||Aug 30, 2004||Apr 27, 2010||Jenavalve Technology, Inc.||Methods and conduits for flowing blood from a heart chamber to a blood vessel|
|US7736327||May 9, 2008||Jun 15, 2010||Jenavalve Technology, Inc.||Methods and conduits for flowing blood from a heart chamber to a blood vessel|
|US8147517||May 23, 2006||Apr 3, 2012||Warsaw Orthopedic, Inc.||Systems and methods for adjusting properties of a spinal implant|
|US8216174||Apr 30, 2010||Jul 10, 2012||Jenavalve Technology, Inc.||Methods and conduits for flowing blood from a heart chamber to a blood vessel|
|US8597226||Jun 12, 2012||Dec 3, 2013||Jenavalve Technology, Inc.||Methods and conduits for flowing blood from a heart chamber to a blood vessel|
|CN100508902C||Sep 26, 2005||Jul 8, 2009||伊西康内外科公司||Applier having automated release mechanism of surgical device|
|DE102008043452A1 *||Nov 4, 2008||May 6, 2010||Biotronik Crm Patent Ag||Vorrichtung zum Einbringen von medizinischen Implantaten|
|International Classification||A61B17/12, A61B17/00, A61F2/06, A61M25/12, A61M37/00|
|Cooperative Classification||A61B17/3468, A61B2017/00247, A61B2017/00243, A61B17/3478, A61M25/06, A61B2019/5251, A61B19/5244, A61B2019/464, A61B2018/00392, A61B2019/462, A61F2/2493, A61F2/95, A61F2/88|
|European Classification||A61B17/34J, A61F2/24Y, A61B17/34Q, A61F2/95|
|Feb 13, 2006||FPAY||Fee payment|
Year of fee payment: 4
|Feb 25, 2010||FPAY||Fee payment|
Year of fee payment: 8
|Apr 18, 2014||REMI||Maintenance fee reminder mailed|
|Sep 10, 2014||LAPS||Lapse for failure to pay maintenance fees|
|Oct 28, 2014||FP||Expired due to failure to pay maintenance fee|
Effective date: 20140910