CA1314309C - Method and apparatus for reducing blockage in body channels - Google Patents
Method and apparatus for reducing blockage in body channelsInfo
- Publication number
- CA1314309C CA1314309C CA000555432A CA555432A CA1314309C CA 1314309 C CA1314309 C CA 1314309C CA 000555432 A CA000555432 A CA 000555432A CA 555432 A CA555432 A CA 555432A CA 1314309 C CA1314309 C CA 1314309C
- Authority
- CA
- Canada
- Prior art keywords
- catheter body
- distal end
- instrument
- conduit
- laser transmission
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
- A61B18/24—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor with a catheter
- A61B18/245—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor with a catheter for removing obstructions in blood vessels or calculi
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/09—Guide wires
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/09—Guide wires
- A61M2025/09058—Basic structures of guide wires
- A61M2025/09083—Basic structures of guide wires having a coil around a core
Abstract
ABSTRACT OF DISCLOSURE
An instrument for removing an obstruction in an internal body channel comprises an elongated catheter body adapted for insertion into a body channel having a first lumen throughout its length. An elongated guide and laser transmission conduit extends through the lumen of said catheter body and is movable therein so that its distal end can be extendable beyond the distal end of the catheter body. The proximal end of the movable conduit is connected to a controlled source of laser energy. A
treatment element is provided at the distal end of the catheter body for further reducing the channel obstruction following preliminary penetration thereof by the movable laser transmission conduit. The treatment element may be a fixed laser transmission conduit which terminates at the end of the catheter body or a dilatation balloon near its distal end. In method steps utilizing the instrument, the movable conduit is positioned near a channel obstruction to enlarge a passage through and then serves to guide the catheter body into position so as to further enlarge or remove the obstruction using its treatment element.
An instrument for removing an obstruction in an internal body channel comprises an elongated catheter body adapted for insertion into a body channel having a first lumen throughout its length. An elongated guide and laser transmission conduit extends through the lumen of said catheter body and is movable therein so that its distal end can be extendable beyond the distal end of the catheter body. The proximal end of the movable conduit is connected to a controlled source of laser energy. A
treatment element is provided at the distal end of the catheter body for further reducing the channel obstruction following preliminary penetration thereof by the movable laser transmission conduit. The treatment element may be a fixed laser transmission conduit which terminates at the end of the catheter body or a dilatation balloon near its distal end. In method steps utilizing the instrument, the movable conduit is positioned near a channel obstruction to enlarge a passage through and then serves to guide the catheter body into position so as to further enlarge or remove the obstruction using its treatment element.
Description
~ 31 ~309 METHOD AND APPARATUS FOR REDIJCIN(~
s 7 This invention pertains to the use of lasers in 8 medicine, and more particularly ~o the guidance and g positioning of light radiation using elongated, flexible transfer oonduits for diagnostic use and~or therapeutic lL removal of obstructive disease in an internal body channel 1~ or cavi~y.
Disease deposits which cause reduction of flow of 16 body fluids in internal body channels occur in various 17 body sites including the arteries, the ureters an~ the 18 bile ducts. Conventional surgical techniques which are 19 used to remove the obstructive material include operative procedures and minimally invasive procedures. In an 21 operative proceduret skin incision directly exposes the 22 disease site to facilitate removal of disease. In a 23 minimally invasive procedure, a surgical instrument is 24 inserted percutaneously (through the skin) into a body channel or cavity and advanced to the disease site. The 26 instrument may use various means (e.g. mechanical, 27 chemical, photophysical) to re~ove the diseased area and 28 restore normal flow~
I~ various techniques heretofore conceived for 31 using laser energy as a means to re~ove diseased areas 2 within body channels~ the laser energy enters the 33 proximal end of a radiation transfer conduit (e.g. an 34 optical fiber), travels through the fiber and exits from a more distal operative end within the body channel to reach 6 the treatment ~ite. A ma~or difficulty with these prior 37 techniques was in providing adequate means for 3~
- 2 - l 3 1 ~ 3 09 1 non-trauma~ically guiding the operative end of the 2 radiation transfer conduit to the treatment area and then 3 providing a sufficiently efficient mean~ for removing all 4 or a large portion of a diseased obstruction. Body channels may tortuously curve and branch and the radiation 6 transfer conduit must therefore be flexible and yet 7 maneuverable and controllable. Since manipulation of 8 the transfer conduit must be controlled at one end g thereof, the conduit must be capable of responding to both torsional and pushing forces applied to its proximal end.
~1 Furthermore, during the obstruction removal process, the 12 radiation transf2r conduit must often pass through an 13 area of obstruction to treat more distal areas within and 14 beyond a lesion. In some situations, the obstruction may be quite large compared with the size of the beam of la~er 16 energy being applied. Therefore, in order to dissolve or 17 reduce such obstructions the beam must be moved or 18 additional treatment means must be utilized to reduce the 19 obstructions after an initial or new channel has been made through the obstruction. Moreover, when any radiation 21 transfer conduit is moved within the body channel, it i5 22 eSsential that its laser energy not be directed at 23 non-contiguous sites within the obstructive deposits, and 24 thereby avoid creating a hazard of embolic events. In addition, the newly created channel must be sufFiciently 26 wide to permit adequate re-establishment of the flow of 27 body fluid despite the requirement of using a low profile 28 radiation transfer conduit. Finally, the aforesaid 29 problems were further complicated by specific site factors 3~ that often occur at different types of disease areas 31 le-9- atherosclerosis, ureteral stones, gallstones).
32 In U.S Patent No. 4,641,6~0 a method is disclosed 33 for destroying atheromatous plaque within an artery of a 34 patient using a catheter system including ~iberoptical cable means which includes optical diagnostic means and a 36 treatment fiber optical array means. The diagnostic means _ 3 - 131~3~9 1 is used to sense the presence and location of the plaque 2 in the artery so tha~ the treatment means can be directed 3 on the plaque and avoid damaging healthy tissue. However, desp;te the improvements in treatment results afforded by the aforesaid sensing system, there existed a need for a 6 more effective system for removing body channel 7 obstructions, and moreover one that was compa~ible with 8 and could encorporate ~he sensing system.
g Accordingly, a general object of the invention is to provide an improved method of delivering laser energy 11 for the treatment of an area within a body channel or 12 cavity.
13 Another object of the invention is to teach an 14 improved method and to provide an instrument usable in said method capable of tunneling through a body channel or 16 cavity and of also providing guidance and positioning 17 capabilities that will provide an improved treatment 18 modality in terms of safety and efficacy.
19 Another object of the invention is to teach an improved method and provide an instrument for enlarging 21 an opening within a body channel or cavity by providing a 22 means to deliver laser energy to a contiguous area of 23 disease and thus diminish the chance of embolic events.
24 Yet another, more specific object of the invention is to provide an improved instrument of 26 radiation transfer which can be inserted into a body 27 channel having an obstruction and then be controlled to 28 create or enlarge a first opening ~brough the obstructive 29 body channel such that said instrument can advance further 3~ through this first channel and thereafter serve as a 1 directional guide for another component of the instrument 32 capable of providing subsequent treatment when 33 operationally interfacea with the diseased site.
34 Still another object of the present invention is to provide a catheter assembly for removing obstructions 36 from a body channel wherein a first movable guidewire 3~
_ 4 1 ~ 1 ~309 1 element with radiation capabilities is movable within a 2 second larger catheter body having at least one radiation 3 transfer conduit, so that the first element can be 4 positioned to form an initial opening in the body channel obstruction being treated and then can serve as a guide 6 means to advance the second large~ catheter body so that 7 its radiation transfer conduit can be positioned near the 8 channel obstruction to further dissolve diseased tissue and greatly enlarge the opening through the obstruction.
11 Summary of the Invention 12 In accordance with one aspect of the inventionf 13 there is contemplated a method of removing atheromatous 14 plaque to create a new channel within an artery of a patient comprising the steps of introducing a first 16 fiberoptical, light transmitting conduit into the artery 17 and advancing its distal end so that it is operatively 1~ opposite the plaque site. At the appropriate time laser l9 energy is introduced into the proximal end of this first fiberoptical conduit which is emitted from its distal 21 end to remove disease deposits and thereby allow the 22 fiberoptical conduit to form a new channel and advance 23 further in the artery. The first conduit is movable 24 Within a larger catheter body which also has a second fiberoptical conduit fixed therein~ After the first, 26 movable conduit has formed a new channel in an 27 obstruction, the catheter body is guided by and tracks 28 along the first fiberoptical conduit to become 29 operatively interfaced with any remaining atherosclerotic obstruction. With the second ~iberoptical conduit so 31 positioned, laser energy is introduced into its proximal 32 end to exit its distal end and remove additional disease deposits contiguous to the new channel, thereby producing 34 a wider channel along the axis of ~he f irst ~iberoptic conduit. In addition to or in lieu of the use of laser 36 energy through the second conduit the catheter body may _ 5 _ 131~309 l also utilize other treatment means at the disease site 2 (e.g. dilatation balloon, slicing device, ultrasonic 3 energy), to widen further the new channel along the axis 4 of the first fiberoptical conduit.
To implement the method o~ the invention~ it is 6 contemplated that the first conduit comprise a single 7 strand or bundle of light transmitting fibers at least 8 the distal end of which is situated within a relatively 9 flexible coiled wire sheath capable of serving as a guide means within the body channel being treated. This first ll conduit means is movable within ~he catheter assembly 12 having the second fiberoptic conduit. ~sing linear and 13 torsional control of the first fiber conduit instrument 14 with its coiled wire sheath, the physician operator can then manipulate and position its distal end within the 16 artery even during the emission of light radiation from 17 the operative end. Thus, the first fiber conduit can first 18 create an enlarged channel and then advance through it.
19 The catheter assembly with its fixed fiber conduit can then track over the first fiber conduit, encounter the 21 disease areas contiguous to the new channel, and operate 22 to widen the channel, either with the application of more 23 laser energy or by performing a conventional dilatation 24 balloon angioplasty.
In accordance with the invention when used to 26 remove atherosclerotic plaque from an artery, the first 27 fiber conduit with its coiled wire exterior serves as a 28 guidewire as it is advanced across an area of 29 constriction in the body channel. ~hereafter, the catheter body having ~ingle or muItiple lumens and single or 31 multiple fiber conduits can be moved forwardly aIong the 32 fir5t fiber conduit which rests within the lumen of said 33 catheter assembly~ After the first conduit has provided 34 partial reduction of the artery plaque, additional laser energy can be directed into the proximal end of the fiber 36 or fibers of the catheter body to remove more diseased 3~
- 6 - 1 31 ~30q 1 tissues when encountered and thus widen the channel in the 2 contiguous area of disease adjacent to the guidewire like 3 fiber conduit.
~ Other objects, advantages, features of the invention will be appare~t from the following detailed 6 description of preferred embodiments thereof, presented 7 in conjunction with the accompanying drawings~
; 8 g BRIEF DESCRIPTION OF DRAWINGS
Fig. 1 is a partially schematic and fragmentary 11 view in elevation of a catheter assembly embody;ng 12 principles of the present invention.
13 Fig. 2 is an enlarged view in section taken at 14 line 2-2 of Fig. 1.
Fig. 3 is enlarged view in section taken at line 16 2-2 of Fig. 1 showing a balloon section of the assembly, 17 with the inflated balloon shown in dotted lines.
18 Fig~ 4 is a further enlarged distal end view of 19 the catheter assembly of Fig. 1, taken at line 4-4 thereof.
21 Fig. 5 is an enlarged distal end view of a 22 modified form of catheter assembly according to the 23 invention.
24 Fig. 6 is an enlarged distal end view of another modified form of catheter assembly according ~o the 26 invention.
27 Fig. 7 is an enlarged distal end view of another 28 modified form of cathe~er assembly according to the 29 invention.
Fig. 8 is a fragmentary view in elevation and in 31 section showing the movable guidewire/fiber means for the 32 catheter assembly of Fig. 1.
33 Fig. g is a view in section of the guidewire/fiber means taken at line 9-9 of Fig. 8.
Fig. 9A is a distal end view of the 3G guidewire/iber means taken at line 9A-9A thereof.
_ 7 _ 1 31 ~30q 1 Fig. 10 is a schematic view in elevation of the 2 guidewire/fiber means of Fig. 8 showing different sections 3 along its length.
4 Fig's. 11-16 are a series of schematic views showing one mode of an operation for the removal of 6 atheromatous plaque from an artery in accordance with the 7 principles of the present inventionO
g DETAILED l:)ESCRIPTIl:)N OF EMBODIMENTS
With reference to the drawing, Fig. 1 shows a 11 catheter instrument 20 for removing diseased obstructions 12 from body channels, such as atheromatous plaque fro~ an 13 artery, in accordance with principles of the present 14 invention. In broad terms, the instrument comprises a multi-lumen thin-walled flexible body 22 having a tapered 16 distal end 24 that is adapted for initial insertion into 17 an artery or vein. This flexible body 22 is preferably 1~ made from a suitable plastic material such as polyethylene 19 or polyurethane, although other flexible materials could also be used. Near its proximal end 26, the device is 21 coupled, by a suitable conduit coupling 27, to a plurality 22 of branch conduits connected from certain controllable 23 appliances to lumens within the body 22, as will be 24 described below. Within one lumen 28, as shown in Fig. 2, is a movable, first radiation transmission conduit 30 26 which also serves as a guidewire and has a surrounding 27 coiled wire sheath 32. Separated by a septum 34 from the 2~ first lumen 28 in the body 22 is a second lumen 36 within 29 which is a second laser transmission conduit 38 that is fixed in place ~nd is thus non-movable therein.
31 As shown in Fig. 2, a pair of addi~ional lumens 3~ 40 and 42 are provided at spaced apart locations extending 33 along the length of the body 22. Both of these lumens are 3~ smaller in diameter than the lumens 28 and 36. One lumen 40 is connected to a flexible tube 44 at the proximal end 36 of the catheter body 22 and has an opening 46 in the wall - 8 - l 31 ~309 1' of the body near its distal end. The tube 44 is adapted 2 for connection to a source of a pre-selected liquid such 3 as a sui~able radio opaque dye substance that may be used 4 during a treatment procedure with the instrument 20. The proximal end of the lumen 42 is connected to a flexible 6 tube 48 that is connectable to a $ource of air pressure 7 through a suitable coupling and valve (not shown).
8 As shown in Fig. 3, an opening 50 from the distal g end of the lumen 42 is provided in the wall of the catheter body 22. This opening is located between the ends 11 of an elastomeric tubular sleeve 52 that extends around 1~ the body 22 and is retained by suitable annular sealant 13 ,members 54 at its opposite ends~ When compressed air is 14 supplied to the lumen 42, it exits the opening 50 and inflates the sleeve 52 which forms a toroidal balloon 16 around the catheter body, as indicated by the dotted lines 17 in Fig. 3. During use of the instrument 20, this balloon 18 52 may be used to stabilize the instrument within a body 19 channel and also block the flow of blood during a treatment operation. Attached to the outer surface of the 21 catheter body 22 under the balloon 52 is marker band 63 of 22 a suitable radiation opaque material such as a nickel 23 platinum alloy which enables the exact location of the 24 balloon to be monitored during an operation. Similar marker bands may be attached to the catheter body such as 26 near its tapered tip.
27 At the proximal end 26 of the catheter body 22, 28 the lumen 28 for the movable laser transmitting guide wire 29 conduit 30 is connected via a short conduit 55 ~o a "y~
fitting 56 having a pair of branch members 58 and 60. One 1 branch member 58~contains an extension 62 o~ the fixed or ~2 second fiber conduit 38 that terminates with a coupling ~ hich, facilitates its connection to a laser generator 34 indicated schematically by the box 64. The other branch member 60 is tubular and has a shutoff valve 65 with an 1 3 1 ~309 g 1 end itting 67 that facilitates its connection to a 2 selected source of liquid such as a saline solution that 3 may be used in a typical body channel tr~eatment procedure.
~ The movable laser transmission conduit 30 that is slidable and rotatable within the lumen 28 will be 6 described in detail with reference to Figs. 8-10.
7 Throughout its length the conduit 30 has a core 66 of ~ uniform cross-section formed of either a single glass g fiber strand or a bundle of glass fibers, as shown, capable of transmitting laser energy. Surrounding the 11 glass fiber core 66 ~or most of the length of the conduit 12 30 is the coiled wire sheath 32. This wire is preferably 13 rectangular in cross-section and is made of a resilient, 1~ non-corrosive metal such as stainless steel. The sheath 32 is spaced radially outwardly from the core by a series of 16 insulative annular spacers 68 which are preferably made 17 of a radiation opaque material such as a nickel platinum 18 alloy so that, like the markers 63, they serve as 19 internal markers for a physician during a fluoroscopic 2~ treatment procedure. As ~hown in Fig. 8, at the distal end 21 of the movable member 30 is a short tip portion 70 22 having a modified "J" shape that forms a small angle (e.g.
~3 2-5) with the longitudinal axis of the member 30. An 2~ annular spacer 68 is provided within this tip portion to secure the front end of the fiber core to the surrounding 26 wire coil 32 and to mark its extreme distal end during 27 use. The distal end of the wire coil on the tip portion 70 28 is preferably tapered to a smaller diameter.
29 Spaced longitudinally inwardly from the tip portion 70 is another spacer-marker 68A. As shown in 31 Fig. 8, a front section of the wire coil sheath 32 32 extends longitudinally to a termination point 72 where it 33 surrounds a third annular spacer 68B and abuts against a 3~ shorter section 74 of a plastic material such as polyethylene or polyurethane and having the same outer 6 diameter but completely surrounding the glass iber core lo 1 3 1 ~309 1 66. Since this plastic section i~ essentially bonded or 2 fixed to the fiber core, it provides a means for applying 3 a torsional or twisting force to the entire movable 4 conduit 30.
S As shown in Fig. 10, a complete movable conduit 6 30 preferably has at least two pl~stic sections 74 and 7 74Ao Thus, in the embodiment shown, the conduit 30 is 8 comprised of the front or first wire coil section 32 9 having a length of around 125cms,o the second section 74, which is plastic having a length of 20cms; a third wire 11 coil section 32A having a length of 80cms; a fourth 12 section 74A which is plastic, having a length of 50cm;
13 and a fifth section 32B of coiled wire having a length of 14 115cm. The latter wire section has a suitable end coupler for the surrounded core which is connectable to a 16 laser generator 76 (Fig. 1). The aforesaid length 17 dimensions are presented as being typical for a particular 18 application of the device 20, but they may vary for 19 different operational procedures.
The two plastic sections 74 and 74A afford 21 alternative locations where torsional force can be applied 22 to turn the conduit 30 about its longitudinal axis and 23 thus change the direction of the laser energy emitted from 24 its distal tip portion 70. The coil wire sheath 32 around the laser transmitting core affords the conduit 30 with a 26 degree of flexibility that enables it to bend when 27 necessary and to be controllable by torsional and pushing 28 forces at its proximal end. Yet it also has a sufficient 29 degree of stiffness that enables the conduit to function as a guide wire for the main catheter body 22, to help 31 move it through a body channel after the conduit 30 has 32 initially moved beyond the distal end of the body 22.
33 Thus, as the conduit 30 emits laser energy from its distal 34 end to destroy diseased tissue, it may be moved longitudinally (as well as be rotated) within the 36 catheter body 22 until it extends a substantial distance - 11 131~309 ~ beyond the end of the catheter body. Now, as the catheter 2 body is also moved forwardly in the body channel to 3 further remove blocking plaque or tissue, the member 30 4 is sufficiently strong to serve as a guide means for the catheter body.
In the embodiment of the invention shown in Figs.
7 2 and 4, the lumens 28 and 36 containing the first movable 8 radiation transmjssion element 30 and the fixed radiation g transmission conduit 38 are both cylindrical with their centerlines spaced apart from the centerline of the 11 catheter body 22. Also, the l~men 36 for the fixed glass 12 fiber conduit 38 has a sli~htly smaller diameter than the 13 lumen 28 for the movable element 30. With this embodiment, 14 the entire catheter body 22 would be rotated in use so that the fixed laser transmission conduit 38 can move 16 in an arc to direct laser energy against blocking tissue 17 in the body channel being treated.
18 In a modified arrangement for a instrument 20A, 19 shown in Fig. 5, the centerline of the lumen 28 for the ~0 movable radiation conduit 30 is coincident with the ~1 centerline of the catheter body 22. Circumferentially 22 spaced around the lumen 28 are a series of three arcuately 23 shaped lumens 78 in the catheter body 22. Each of these 2~ arcuate lumens contains a plurality of glass fibers 80, each thereby forming a separate laser transmission 26 conduit. With these circumferentially spaced apart arcuate 27 shaped conduits, rotational movement of the catheter 28 body 22 can be minimized and laser energy can be supplied 29 through any of the selected fiberoptic conduits 80 in use, as will be explained more fully below.
31 A further modified form of the invention is shown 32 in Fig. 6 which is ~ front end view of an instrument 33 catheter assembly 20B. Here, the lumen 28 for the movable 34 radiation conduit 30 has a centerline that is spaced from the main catheter centerline. Spaced to one side of the 6 lumen 28 is a second lumen 82 having a generally arcuate - 12 - 1 3 1 ~30q 1 or nV-like" shape within which are fixed a plurality of 2 glass fibers 84 for transmitting laser energy. This 3 latter lumen, which is fully packed with glass fibers, 4 covers a large percentage of the frontal cross-sectional area of the catheter body 22 so that the laser energy 6 emitted therefrom can be directed toward a substantial 7 area of ohstructive material within a body channel with 8 li~tle or no rotational movement of the catheter body g during treatment.
In another embodiment of the invention, a 11 catheter assembly 20C is shown in Fig~ 7 with the lumen 12 28 for the movable radiation conduit 30 being centrally 13 located within the catheter body 22 so that its 1~ centerline is coincident with the body centerline. Here, near the end of the distal end of the catheter body, an 16 inflatable balloon 86 is provided in lieu of a l~men 17 having fixed fiber optic strands for transmitting laser 18 energy. An opening 88 to the inside of this balloon is 19 provided at the distal end of another lumen provided within the catheter body 22 for supplying compressed air 21 to inflate the balloon 86.
22 A typical operation of the instrument 2Q in 23 accordance with principles of the present invention will 24 be described with reference to Figs. 11-16 utilizing the example of the removal of an atheromatous plaque from an 26 artery 89 as shown in Fig. 11. Before treatment 2i commences~ the distal end of the movable radiation conduit 28 30 is inserted into the lumen 28 of the catheter body 29 22, and the proximal end of this movable element is connected to the laser generator system, as shown in Fig.
31 1. The distal end of catheter body 22 i5 inserted into 32 the patient's artery and is moved to near the treatment 33 site, i.e. the arterial blockage 90. A guiding catheter 3~ (not shown~ of the type well know in the art, may be used to initially place the instrument 20 within the patient's 36 artery or body channel. As shown in Fig. 12, the toroidal ~: ( - 13 - 131 ~ 3 09 1 balloon ~2 on the catheter body 22 can be inflated to 2 block the artery and stabili~e the body 22. The distal end 3 of the movable radiation conduit 30 is then advanced 4 beyond the distal end of catheter body 2~ until it is operatively opposite the treatment site 90. The glass 6 fiber core within the conduit 30 can now trans~it and 7 receive lisht radiation from the treatment site. At ~his 8 point, the conduit 30 can be used to sense the direction g and proximity of diseased blocking tissue in accordance with the principles of V.S Patent No. 4,641,650. At the 11 appropria~e time, the laser generator 76 is activated to 12 transmit laser energy into the proximal end of the iber 13 conduit 30 which is emitted from its aistal end, thereby 14 illuminating a portion of the treatment site 90. The impinged portion of atherosclerosis is vaporized and the 16 movable conduit 30 is advanced into the resultant crater 17 which ultimately becomes a larger opening through the 18 diseased tissue. This process is repeated until the distal 19 end of the movable conduit has advanced completely through the lesion as shown in Fig. 13. This advancement 21 may require torsional as well as linear manipulation of 22 the movable conduit 30 applied by the physician on its 23 proximal end (which remains external to the body 22) in 24 order to negotiate curves in the artery.
In a related embodiment of the invention, the 26 movable fiber optic conduit 30 is inserted into the lumen 27 28 of the catheter body 22 and in a similar fashion the 28 entire catheter assembly 20 is inserted into an artery to 29 be treated. The movable fiber conduit 30 is moved to the 3~ blockage lesion where it utili~es laser energy with its 31 9uidance and positioning functions to create a new 32 channel in the treatment site. Once the movable fiber 33 element is distal to the lesion or treatment site, the 4 catheter body 22 is advanced along its axis until the distal end of the fixed optical fiber conduit 38 in the 36 catheter body is operatively opposite the remaining 1 atherosclerotic areas, as shown in Fig. 14. With the fixed 2 glass fiber condui~ 38 so positioned, the second laser 3 generator means 64 is activated to transmit light 4 radiation or laser energy into the proximal end of the fixed optical fiber conduit 62. Energy from this fixed 6 conduit 38 illuminates the portion of the atherosclerotic 7 lesion contiguous to the movable fiber conduit 30, more 8 plaque is removed and the new channel is widened. During g activation of the f;xed fiber conduit, the entire catheter body 22 may be rotated to some degree to sweep an 11 add;tional cross sectional area of the blockage lesion.
12 The process of tissue removal by laser energy may continue 13 until the lesion is reduced in size and a clinically 1~ successful result is achieved, as shown in Figs. 15 and 16. At this point, with the channel through the blocking 16 lesion 90 substantially increased, the entire catheter 17 instrument 20 can be advanced, and the movable conduit 30 18 can be pushed further into the artery 89 ahead of the 19 body 22.
Once the conduit 30 is distal to the lesion 90, 21 the catheter body 22 may be advanced ~urther along the 22 axis of the movable conduit 30 which at this point serves 23 as a guide wire for the catheter body. When the catheter 24 body 22 reaches the lesion area, dilatation balloon 53 similar to the balloon 52 or the frontal balloon 86 of 26 Fig. 7 may be positioned across the remaining 27 atherosclerotic plaque area as shown in Fig. 15.
28 conventional balloon angioplasty can be then performed if 29 desired to further widen the body channel at this point.
Using the embodiment of Fig. 4, the catheter body 31 22 may be rotated a~ least partially as the fixed fiber 32 CQnduit 38 is transmitting laser energy, so that a greater area of lesion being trea~ed can be swept and thus removed. With the embodiment of Fig. 5 this can be accomplished by selective activation of the fixed plural 36 fiber conduits 80. If the embodiment of Fig. 6 i9 - 15 - l 3 1 ~ 3 09 l utilized, an increased cross sectional area of blockage 2 tissue can be contacted and vaporized with little or no 3 rotational movement of the catheter body 22 when laser 4 energy is transmitted through the "V-shaped" fiber conduit 84. With both embodiments, the movable conduit 30 is 6 utilized to accomplish the initial enlarclement of the body 7 channel being treated and thereafter, the fixed conduits 8 80 or 84 are energized (with some partial rotation of the 9 catheter body 22, when necessary) to remove additional diseased tissue or plaque and ~urther enlarge the channel.
11 While only the treatment of plaque has been 12 described herein, the present invention may be used for 13 the treatment of other diseases which include but are not 1~ limited to blood clots, foreign bodies in non-vascular channels, tumors, stones in the urinary tract and gall 16 bladder as well as prostate obstructions. The movable 17 radiation transfer conduit 30 can be but is not limited to 18 a fiberoptic conduit which can be a single fiber or ~9 multiple fibers. The fiberoptic cable can be coupled with other catheter designs which include, but are not limited 21 to, such features as endoscopy, balloon devices, steerable 22 guiding systems, multiple lumens for infusion and suctioning, ultrasonic guidance, monitoring devices, 24 ablation devices such as mechanical rotors, slicers or ultrasonic pulverizers, magnetic resonance imaging means, 26 pressure, flow or temperature monitoring and catheter 27 devices. The operative end of the radiation transfer 2~ conduits can include but are not limited to be at the 29 distal tip of the fiber~ coils or catheters, can be directed a~ angles, ~ocus or expand the laser beam, 1 protected by tran~parent windows circumferential or 3~ through balloon materials located other than at the distal 33 tip-34 To those skilled in the art to which this invention relates, many changes in construction and widely differing embodiments and applications of the invention - 16 - 1 31 ~309 1 will suggest themselves without departing from the spirit 2 and scope of the invention. The disclosures ana the descriptions herein are purely illustrative and are not 4 intended to be in any sense limiting.
What is claimed is:
Disease deposits which cause reduction of flow of 16 body fluids in internal body channels occur in various 17 body sites including the arteries, the ureters an~ the 18 bile ducts. Conventional surgical techniques which are 19 used to remove the obstructive material include operative procedures and minimally invasive procedures. In an 21 operative proceduret skin incision directly exposes the 22 disease site to facilitate removal of disease. In a 23 minimally invasive procedure, a surgical instrument is 24 inserted percutaneously (through the skin) into a body channel or cavity and advanced to the disease site. The 26 instrument may use various means (e.g. mechanical, 27 chemical, photophysical) to re~ove the diseased area and 28 restore normal flow~
I~ various techniques heretofore conceived for 31 using laser energy as a means to re~ove diseased areas 2 within body channels~ the laser energy enters the 33 proximal end of a radiation transfer conduit (e.g. an 34 optical fiber), travels through the fiber and exits from a more distal operative end within the body channel to reach 6 the treatment ~ite. A ma~or difficulty with these prior 37 techniques was in providing adequate means for 3~
- 2 - l 3 1 ~ 3 09 1 non-trauma~ically guiding the operative end of the 2 radiation transfer conduit to the treatment area and then 3 providing a sufficiently efficient mean~ for removing all 4 or a large portion of a diseased obstruction. Body channels may tortuously curve and branch and the radiation 6 transfer conduit must therefore be flexible and yet 7 maneuverable and controllable. Since manipulation of 8 the transfer conduit must be controlled at one end g thereof, the conduit must be capable of responding to both torsional and pushing forces applied to its proximal end.
~1 Furthermore, during the obstruction removal process, the 12 radiation transf2r conduit must often pass through an 13 area of obstruction to treat more distal areas within and 14 beyond a lesion. In some situations, the obstruction may be quite large compared with the size of the beam of la~er 16 energy being applied. Therefore, in order to dissolve or 17 reduce such obstructions the beam must be moved or 18 additional treatment means must be utilized to reduce the 19 obstructions after an initial or new channel has been made through the obstruction. Moreover, when any radiation 21 transfer conduit is moved within the body channel, it i5 22 eSsential that its laser energy not be directed at 23 non-contiguous sites within the obstructive deposits, and 24 thereby avoid creating a hazard of embolic events. In addition, the newly created channel must be sufFiciently 26 wide to permit adequate re-establishment of the flow of 27 body fluid despite the requirement of using a low profile 28 radiation transfer conduit. Finally, the aforesaid 29 problems were further complicated by specific site factors 3~ that often occur at different types of disease areas 31 le-9- atherosclerosis, ureteral stones, gallstones).
32 In U.S Patent No. 4,641,6~0 a method is disclosed 33 for destroying atheromatous plaque within an artery of a 34 patient using a catheter system including ~iberoptical cable means which includes optical diagnostic means and a 36 treatment fiber optical array means. The diagnostic means _ 3 - 131~3~9 1 is used to sense the presence and location of the plaque 2 in the artery so tha~ the treatment means can be directed 3 on the plaque and avoid damaging healthy tissue. However, desp;te the improvements in treatment results afforded by the aforesaid sensing system, there existed a need for a 6 more effective system for removing body channel 7 obstructions, and moreover one that was compa~ible with 8 and could encorporate ~he sensing system.
g Accordingly, a general object of the invention is to provide an improved method of delivering laser energy 11 for the treatment of an area within a body channel or 12 cavity.
13 Another object of the invention is to teach an 14 improved method and to provide an instrument usable in said method capable of tunneling through a body channel or 16 cavity and of also providing guidance and positioning 17 capabilities that will provide an improved treatment 18 modality in terms of safety and efficacy.
19 Another object of the invention is to teach an improved method and provide an instrument for enlarging 21 an opening within a body channel or cavity by providing a 22 means to deliver laser energy to a contiguous area of 23 disease and thus diminish the chance of embolic events.
24 Yet another, more specific object of the invention is to provide an improved instrument of 26 radiation transfer which can be inserted into a body 27 channel having an obstruction and then be controlled to 28 create or enlarge a first opening ~brough the obstructive 29 body channel such that said instrument can advance further 3~ through this first channel and thereafter serve as a 1 directional guide for another component of the instrument 32 capable of providing subsequent treatment when 33 operationally interfacea with the diseased site.
34 Still another object of the present invention is to provide a catheter assembly for removing obstructions 36 from a body channel wherein a first movable guidewire 3~
_ 4 1 ~ 1 ~309 1 element with radiation capabilities is movable within a 2 second larger catheter body having at least one radiation 3 transfer conduit, so that the first element can be 4 positioned to form an initial opening in the body channel obstruction being treated and then can serve as a guide 6 means to advance the second large~ catheter body so that 7 its radiation transfer conduit can be positioned near the 8 channel obstruction to further dissolve diseased tissue and greatly enlarge the opening through the obstruction.
11 Summary of the Invention 12 In accordance with one aspect of the inventionf 13 there is contemplated a method of removing atheromatous 14 plaque to create a new channel within an artery of a patient comprising the steps of introducing a first 16 fiberoptical, light transmitting conduit into the artery 17 and advancing its distal end so that it is operatively 1~ opposite the plaque site. At the appropriate time laser l9 energy is introduced into the proximal end of this first fiberoptical conduit which is emitted from its distal 21 end to remove disease deposits and thereby allow the 22 fiberoptical conduit to form a new channel and advance 23 further in the artery. The first conduit is movable 24 Within a larger catheter body which also has a second fiberoptical conduit fixed therein~ After the first, 26 movable conduit has formed a new channel in an 27 obstruction, the catheter body is guided by and tracks 28 along the first fiberoptical conduit to become 29 operatively interfaced with any remaining atherosclerotic obstruction. With the second ~iberoptical conduit so 31 positioned, laser energy is introduced into its proximal 32 end to exit its distal end and remove additional disease deposits contiguous to the new channel, thereby producing 34 a wider channel along the axis of ~he f irst ~iberoptic conduit. In addition to or in lieu of the use of laser 36 energy through the second conduit the catheter body may _ 5 _ 131~309 l also utilize other treatment means at the disease site 2 (e.g. dilatation balloon, slicing device, ultrasonic 3 energy), to widen further the new channel along the axis 4 of the first fiberoptical conduit.
To implement the method o~ the invention~ it is 6 contemplated that the first conduit comprise a single 7 strand or bundle of light transmitting fibers at least 8 the distal end of which is situated within a relatively 9 flexible coiled wire sheath capable of serving as a guide means within the body channel being treated. This first ll conduit means is movable within ~he catheter assembly 12 having the second fiberoptic conduit. ~sing linear and 13 torsional control of the first fiber conduit instrument 14 with its coiled wire sheath, the physician operator can then manipulate and position its distal end within the 16 artery even during the emission of light radiation from 17 the operative end. Thus, the first fiber conduit can first 18 create an enlarged channel and then advance through it.
19 The catheter assembly with its fixed fiber conduit can then track over the first fiber conduit, encounter the 21 disease areas contiguous to the new channel, and operate 22 to widen the channel, either with the application of more 23 laser energy or by performing a conventional dilatation 24 balloon angioplasty.
In accordance with the invention when used to 26 remove atherosclerotic plaque from an artery, the first 27 fiber conduit with its coiled wire exterior serves as a 28 guidewire as it is advanced across an area of 29 constriction in the body channel. ~hereafter, the catheter body having ~ingle or muItiple lumens and single or 31 multiple fiber conduits can be moved forwardly aIong the 32 fir5t fiber conduit which rests within the lumen of said 33 catheter assembly~ After the first conduit has provided 34 partial reduction of the artery plaque, additional laser energy can be directed into the proximal end of the fiber 36 or fibers of the catheter body to remove more diseased 3~
- 6 - 1 31 ~30q 1 tissues when encountered and thus widen the channel in the 2 contiguous area of disease adjacent to the guidewire like 3 fiber conduit.
~ Other objects, advantages, features of the invention will be appare~t from the following detailed 6 description of preferred embodiments thereof, presented 7 in conjunction with the accompanying drawings~
; 8 g BRIEF DESCRIPTION OF DRAWINGS
Fig. 1 is a partially schematic and fragmentary 11 view in elevation of a catheter assembly embody;ng 12 principles of the present invention.
13 Fig. 2 is an enlarged view in section taken at 14 line 2-2 of Fig. 1.
Fig. 3 is enlarged view in section taken at line 16 2-2 of Fig. 1 showing a balloon section of the assembly, 17 with the inflated balloon shown in dotted lines.
18 Fig~ 4 is a further enlarged distal end view of 19 the catheter assembly of Fig. 1, taken at line 4-4 thereof.
21 Fig. 5 is an enlarged distal end view of a 22 modified form of catheter assembly according to the 23 invention.
24 Fig. 6 is an enlarged distal end view of another modified form of catheter assembly according ~o the 26 invention.
27 Fig. 7 is an enlarged distal end view of another 28 modified form of cathe~er assembly according to the 29 invention.
Fig. 8 is a fragmentary view in elevation and in 31 section showing the movable guidewire/fiber means for the 32 catheter assembly of Fig. 1.
33 Fig. g is a view in section of the guidewire/fiber means taken at line 9-9 of Fig. 8.
Fig. 9A is a distal end view of the 3G guidewire/iber means taken at line 9A-9A thereof.
_ 7 _ 1 31 ~30q 1 Fig. 10 is a schematic view in elevation of the 2 guidewire/fiber means of Fig. 8 showing different sections 3 along its length.
4 Fig's. 11-16 are a series of schematic views showing one mode of an operation for the removal of 6 atheromatous plaque from an artery in accordance with the 7 principles of the present inventionO
g DETAILED l:)ESCRIPTIl:)N OF EMBODIMENTS
With reference to the drawing, Fig. 1 shows a 11 catheter instrument 20 for removing diseased obstructions 12 from body channels, such as atheromatous plaque fro~ an 13 artery, in accordance with principles of the present 14 invention. In broad terms, the instrument comprises a multi-lumen thin-walled flexible body 22 having a tapered 16 distal end 24 that is adapted for initial insertion into 17 an artery or vein. This flexible body 22 is preferably 1~ made from a suitable plastic material such as polyethylene 19 or polyurethane, although other flexible materials could also be used. Near its proximal end 26, the device is 21 coupled, by a suitable conduit coupling 27, to a plurality 22 of branch conduits connected from certain controllable 23 appliances to lumens within the body 22, as will be 24 described below. Within one lumen 28, as shown in Fig. 2, is a movable, first radiation transmission conduit 30 26 which also serves as a guidewire and has a surrounding 27 coiled wire sheath 32. Separated by a septum 34 from the 2~ first lumen 28 in the body 22 is a second lumen 36 within 29 which is a second laser transmission conduit 38 that is fixed in place ~nd is thus non-movable therein.
31 As shown in Fig. 2, a pair of addi~ional lumens 3~ 40 and 42 are provided at spaced apart locations extending 33 along the length of the body 22. Both of these lumens are 3~ smaller in diameter than the lumens 28 and 36. One lumen 40 is connected to a flexible tube 44 at the proximal end 36 of the catheter body 22 and has an opening 46 in the wall - 8 - l 31 ~309 1' of the body near its distal end. The tube 44 is adapted 2 for connection to a source of a pre-selected liquid such 3 as a sui~able radio opaque dye substance that may be used 4 during a treatment procedure with the instrument 20. The proximal end of the lumen 42 is connected to a flexible 6 tube 48 that is connectable to a $ource of air pressure 7 through a suitable coupling and valve (not shown).
8 As shown in Fig. 3, an opening 50 from the distal g end of the lumen 42 is provided in the wall of the catheter body 22. This opening is located between the ends 11 of an elastomeric tubular sleeve 52 that extends around 1~ the body 22 and is retained by suitable annular sealant 13 ,members 54 at its opposite ends~ When compressed air is 14 supplied to the lumen 42, it exits the opening 50 and inflates the sleeve 52 which forms a toroidal balloon 16 around the catheter body, as indicated by the dotted lines 17 in Fig. 3. During use of the instrument 20, this balloon 18 52 may be used to stabilize the instrument within a body 19 channel and also block the flow of blood during a treatment operation. Attached to the outer surface of the 21 catheter body 22 under the balloon 52 is marker band 63 of 22 a suitable radiation opaque material such as a nickel 23 platinum alloy which enables the exact location of the 24 balloon to be monitored during an operation. Similar marker bands may be attached to the catheter body such as 26 near its tapered tip.
27 At the proximal end 26 of the catheter body 22, 28 the lumen 28 for the movable laser transmitting guide wire 29 conduit 30 is connected via a short conduit 55 ~o a "y~
fitting 56 having a pair of branch members 58 and 60. One 1 branch member 58~contains an extension 62 o~ the fixed or ~2 second fiber conduit 38 that terminates with a coupling ~ hich, facilitates its connection to a laser generator 34 indicated schematically by the box 64. The other branch member 60 is tubular and has a shutoff valve 65 with an 1 3 1 ~309 g 1 end itting 67 that facilitates its connection to a 2 selected source of liquid such as a saline solution that 3 may be used in a typical body channel tr~eatment procedure.
~ The movable laser transmission conduit 30 that is slidable and rotatable within the lumen 28 will be 6 described in detail with reference to Figs. 8-10.
7 Throughout its length the conduit 30 has a core 66 of ~ uniform cross-section formed of either a single glass g fiber strand or a bundle of glass fibers, as shown, capable of transmitting laser energy. Surrounding the 11 glass fiber core 66 ~or most of the length of the conduit 12 30 is the coiled wire sheath 32. This wire is preferably 13 rectangular in cross-section and is made of a resilient, 1~ non-corrosive metal such as stainless steel. The sheath 32 is spaced radially outwardly from the core by a series of 16 insulative annular spacers 68 which are preferably made 17 of a radiation opaque material such as a nickel platinum 18 alloy so that, like the markers 63, they serve as 19 internal markers for a physician during a fluoroscopic 2~ treatment procedure. As ~hown in Fig. 8, at the distal end 21 of the movable member 30 is a short tip portion 70 22 having a modified "J" shape that forms a small angle (e.g.
~3 2-5) with the longitudinal axis of the member 30. An 2~ annular spacer 68 is provided within this tip portion to secure the front end of the fiber core to the surrounding 26 wire coil 32 and to mark its extreme distal end during 27 use. The distal end of the wire coil on the tip portion 70 28 is preferably tapered to a smaller diameter.
29 Spaced longitudinally inwardly from the tip portion 70 is another spacer-marker 68A. As shown in 31 Fig. 8, a front section of the wire coil sheath 32 32 extends longitudinally to a termination point 72 where it 33 surrounds a third annular spacer 68B and abuts against a 3~ shorter section 74 of a plastic material such as polyethylene or polyurethane and having the same outer 6 diameter but completely surrounding the glass iber core lo 1 3 1 ~309 1 66. Since this plastic section i~ essentially bonded or 2 fixed to the fiber core, it provides a means for applying 3 a torsional or twisting force to the entire movable 4 conduit 30.
S As shown in Fig. 10, a complete movable conduit 6 30 preferably has at least two pl~stic sections 74 and 7 74Ao Thus, in the embodiment shown, the conduit 30 is 8 comprised of the front or first wire coil section 32 9 having a length of around 125cms,o the second section 74, which is plastic having a length of 20cms; a third wire 11 coil section 32A having a length of 80cms; a fourth 12 section 74A which is plastic, having a length of 50cm;
13 and a fifth section 32B of coiled wire having a length of 14 115cm. The latter wire section has a suitable end coupler for the surrounded core which is connectable to a 16 laser generator 76 (Fig. 1). The aforesaid length 17 dimensions are presented as being typical for a particular 18 application of the device 20, but they may vary for 19 different operational procedures.
The two plastic sections 74 and 74A afford 21 alternative locations where torsional force can be applied 22 to turn the conduit 30 about its longitudinal axis and 23 thus change the direction of the laser energy emitted from 24 its distal tip portion 70. The coil wire sheath 32 around the laser transmitting core affords the conduit 30 with a 26 degree of flexibility that enables it to bend when 27 necessary and to be controllable by torsional and pushing 28 forces at its proximal end. Yet it also has a sufficient 29 degree of stiffness that enables the conduit to function as a guide wire for the main catheter body 22, to help 31 move it through a body channel after the conduit 30 has 32 initially moved beyond the distal end of the body 22.
33 Thus, as the conduit 30 emits laser energy from its distal 34 end to destroy diseased tissue, it may be moved longitudinally (as well as be rotated) within the 36 catheter body 22 until it extends a substantial distance - 11 131~309 ~ beyond the end of the catheter body. Now, as the catheter 2 body is also moved forwardly in the body channel to 3 further remove blocking plaque or tissue, the member 30 4 is sufficiently strong to serve as a guide means for the catheter body.
In the embodiment of the invention shown in Figs.
7 2 and 4, the lumens 28 and 36 containing the first movable 8 radiation transmjssion element 30 and the fixed radiation g transmission conduit 38 are both cylindrical with their centerlines spaced apart from the centerline of the 11 catheter body 22. Also, the l~men 36 for the fixed glass 12 fiber conduit 38 has a sli~htly smaller diameter than the 13 lumen 28 for the movable element 30. With this embodiment, 14 the entire catheter body 22 would be rotated in use so that the fixed laser transmission conduit 38 can move 16 in an arc to direct laser energy against blocking tissue 17 in the body channel being treated.
18 In a modified arrangement for a instrument 20A, 19 shown in Fig. 5, the centerline of the lumen 28 for the ~0 movable radiation conduit 30 is coincident with the ~1 centerline of the catheter body 22. Circumferentially 22 spaced around the lumen 28 are a series of three arcuately 23 shaped lumens 78 in the catheter body 22. Each of these 2~ arcuate lumens contains a plurality of glass fibers 80, each thereby forming a separate laser transmission 26 conduit. With these circumferentially spaced apart arcuate 27 shaped conduits, rotational movement of the catheter 28 body 22 can be minimized and laser energy can be supplied 29 through any of the selected fiberoptic conduits 80 in use, as will be explained more fully below.
31 A further modified form of the invention is shown 32 in Fig. 6 which is ~ front end view of an instrument 33 catheter assembly 20B. Here, the lumen 28 for the movable 34 radiation conduit 30 has a centerline that is spaced from the main catheter centerline. Spaced to one side of the 6 lumen 28 is a second lumen 82 having a generally arcuate - 12 - 1 3 1 ~30q 1 or nV-like" shape within which are fixed a plurality of 2 glass fibers 84 for transmitting laser energy. This 3 latter lumen, which is fully packed with glass fibers, 4 covers a large percentage of the frontal cross-sectional area of the catheter body 22 so that the laser energy 6 emitted therefrom can be directed toward a substantial 7 area of ohstructive material within a body channel with 8 li~tle or no rotational movement of the catheter body g during treatment.
In another embodiment of the invention, a 11 catheter assembly 20C is shown in Fig~ 7 with the lumen 12 28 for the movable radiation conduit 30 being centrally 13 located within the catheter body 22 so that its 1~ centerline is coincident with the body centerline. Here, near the end of the distal end of the catheter body, an 16 inflatable balloon 86 is provided in lieu of a l~men 17 having fixed fiber optic strands for transmitting laser 18 energy. An opening 88 to the inside of this balloon is 19 provided at the distal end of another lumen provided within the catheter body 22 for supplying compressed air 21 to inflate the balloon 86.
22 A typical operation of the instrument 2Q in 23 accordance with principles of the present invention will 24 be described with reference to Figs. 11-16 utilizing the example of the removal of an atheromatous plaque from an 26 artery 89 as shown in Fig. 11. Before treatment 2i commences~ the distal end of the movable radiation conduit 28 30 is inserted into the lumen 28 of the catheter body 29 22, and the proximal end of this movable element is connected to the laser generator system, as shown in Fig.
31 1. The distal end of catheter body 22 i5 inserted into 32 the patient's artery and is moved to near the treatment 33 site, i.e. the arterial blockage 90. A guiding catheter 3~ (not shown~ of the type well know in the art, may be used to initially place the instrument 20 within the patient's 36 artery or body channel. As shown in Fig. 12, the toroidal ~: ( - 13 - 131 ~ 3 09 1 balloon ~2 on the catheter body 22 can be inflated to 2 block the artery and stabili~e the body 22. The distal end 3 of the movable radiation conduit 30 is then advanced 4 beyond the distal end of catheter body 2~ until it is operatively opposite the treatment site 90. The glass 6 fiber core within the conduit 30 can now trans~it and 7 receive lisht radiation from the treatment site. At ~his 8 point, the conduit 30 can be used to sense the direction g and proximity of diseased blocking tissue in accordance with the principles of V.S Patent No. 4,641,650. At the 11 appropria~e time, the laser generator 76 is activated to 12 transmit laser energy into the proximal end of the iber 13 conduit 30 which is emitted from its aistal end, thereby 14 illuminating a portion of the treatment site 90. The impinged portion of atherosclerosis is vaporized and the 16 movable conduit 30 is advanced into the resultant crater 17 which ultimately becomes a larger opening through the 18 diseased tissue. This process is repeated until the distal 19 end of the movable conduit has advanced completely through the lesion as shown in Fig. 13. This advancement 21 may require torsional as well as linear manipulation of 22 the movable conduit 30 applied by the physician on its 23 proximal end (which remains external to the body 22) in 24 order to negotiate curves in the artery.
In a related embodiment of the invention, the 26 movable fiber optic conduit 30 is inserted into the lumen 27 28 of the catheter body 22 and in a similar fashion the 28 entire catheter assembly 20 is inserted into an artery to 29 be treated. The movable fiber conduit 30 is moved to the 3~ blockage lesion where it utili~es laser energy with its 31 9uidance and positioning functions to create a new 32 channel in the treatment site. Once the movable fiber 33 element is distal to the lesion or treatment site, the 4 catheter body 22 is advanced along its axis until the distal end of the fixed optical fiber conduit 38 in the 36 catheter body is operatively opposite the remaining 1 atherosclerotic areas, as shown in Fig. 14. With the fixed 2 glass fiber condui~ 38 so positioned, the second laser 3 generator means 64 is activated to transmit light 4 radiation or laser energy into the proximal end of the fixed optical fiber conduit 62. Energy from this fixed 6 conduit 38 illuminates the portion of the atherosclerotic 7 lesion contiguous to the movable fiber conduit 30, more 8 plaque is removed and the new channel is widened. During g activation of the f;xed fiber conduit, the entire catheter body 22 may be rotated to some degree to sweep an 11 add;tional cross sectional area of the blockage lesion.
12 The process of tissue removal by laser energy may continue 13 until the lesion is reduced in size and a clinically 1~ successful result is achieved, as shown in Figs. 15 and 16. At this point, with the channel through the blocking 16 lesion 90 substantially increased, the entire catheter 17 instrument 20 can be advanced, and the movable conduit 30 18 can be pushed further into the artery 89 ahead of the 19 body 22.
Once the conduit 30 is distal to the lesion 90, 21 the catheter body 22 may be advanced ~urther along the 22 axis of the movable conduit 30 which at this point serves 23 as a guide wire for the catheter body. When the catheter 24 body 22 reaches the lesion area, dilatation balloon 53 similar to the balloon 52 or the frontal balloon 86 of 26 Fig. 7 may be positioned across the remaining 27 atherosclerotic plaque area as shown in Fig. 15.
28 conventional balloon angioplasty can be then performed if 29 desired to further widen the body channel at this point.
Using the embodiment of Fig. 4, the catheter body 31 22 may be rotated a~ least partially as the fixed fiber 32 CQnduit 38 is transmitting laser energy, so that a greater area of lesion being trea~ed can be swept and thus removed. With the embodiment of Fig. 5 this can be accomplished by selective activation of the fixed plural 36 fiber conduits 80. If the embodiment of Fig. 6 i9 - 15 - l 3 1 ~ 3 09 l utilized, an increased cross sectional area of blockage 2 tissue can be contacted and vaporized with little or no 3 rotational movement of the catheter body 22 when laser 4 energy is transmitted through the "V-shaped" fiber conduit 84. With both embodiments, the movable conduit 30 is 6 utilized to accomplish the initial enlarclement of the body 7 channel being treated and thereafter, the fixed conduits 8 80 or 84 are energized (with some partial rotation of the 9 catheter body 22, when necessary) to remove additional diseased tissue or plaque and ~urther enlarge the channel.
11 While only the treatment of plaque has been 12 described herein, the present invention may be used for 13 the treatment of other diseases which include but are not 1~ limited to blood clots, foreign bodies in non-vascular channels, tumors, stones in the urinary tract and gall 16 bladder as well as prostate obstructions. The movable 17 radiation transfer conduit 30 can be but is not limited to 18 a fiberoptic conduit which can be a single fiber or ~9 multiple fibers. The fiberoptic cable can be coupled with other catheter designs which include, but are not limited 21 to, such features as endoscopy, balloon devices, steerable 22 guiding systems, multiple lumens for infusion and suctioning, ultrasonic guidance, monitoring devices, 24 ablation devices such as mechanical rotors, slicers or ultrasonic pulverizers, magnetic resonance imaging means, 26 pressure, flow or temperature monitoring and catheter 27 devices. The operative end of the radiation transfer 2~ conduits can include but are not limited to be at the 29 distal tip of the fiber~ coils or catheters, can be directed a~ angles, ~ocus or expand the laser beam, 1 protected by tran~parent windows circumferential or 3~ through balloon materials located other than at the distal 33 tip-34 To those skilled in the art to which this invention relates, many changes in construction and widely differing embodiments and applications of the invention - 16 - 1 31 ~309 1 will suggest themselves without departing from the spirit 2 and scope of the invention. The disclosures ana the descriptions herein are purely illustrative and are not 4 intended to be in any sense limiting.
What is claimed is:
Claims
(1) An instrument for removing an obstruction in an internal body channel comprising:
an elongated catheter body adapted for insertion into a body channel having a first lumen throughout its length, said catheter body having a proximal end and an opposing distal end;
an elongated movable guide and laser transmission conduit means extending through said lumen of said catheter body and having a distal end that is extendable beyond the distal end of said catheter body and a proximal end, said proximal end of said conduit means adapted to be connected to a controlled source of laser enery; and trreatment means at the distal end of said catheter body for further reducing said obstruction following preliminary penetration thereof by said elongated movable guide and laser transmission means, wherein said treatment means comprises a laser transmission means fixed within a lumen of said catheter body and terminating at its distal end.
(2) The instrument as described in claim 1 including an inflatable means affixed to the outer surface of said catheter body near its distal end for sealingly engaging the interior walls of the body channel.
(3) The instrument as described in claim 1 wherein said treatment means comprises a plurality of glass fibers in a closely packed conduit having generally a circular cross-section, whose centreline is offset from the centreline of said catheter body.
(4) The instrument as described in claim 1 wherein said treatment means comprises a plularity of glass fibers in a closely packed conduit having generally a crescent shape that partially surrounds said elongated movable guide and laser transmission conduit means.
(5) The instrument as described in claim 1 wherein said treatment means comprises a plurality of fixed laser transmission conduit means spaced radially from and circumferentially spaced around said lumen of said catheter body.
(6) The instrument as described in claim 5 wherein said plurality of fixed laser transmission conduit means comprises three spaced apart groups of closely packed glass fibers, all terminating at the distal end of said catheter body, each said group being connectable to a laser power source.
(7) The instrument as described in claim 1 wherein said treatment means in said catheter body further comprises an inflatable means at its distal end which can be utilized to perform an angioplasty function on a diseased area of body channel following initial penetration thereof by said elongated movable guide and laser transmission conduit means.
(8) The instrument as described in claim 1 wherein elongated movable guide and laser transmission conduit means comprises an elongated member comprised of an outer coil of wire surrounding an inner core of fiberoptic material.
(9) The instrument as described in claim 1 wherein said catheter body is made of a flexible plastic material having a plurality of lumens along its length.
(10) The instrument as described in claim 1 wherein said catheter body is less flexible than said elongated movable guide and laser transmission conduit means.
(11) The instrument as described in claim 1 wherein said elongated movable guide and laser transmission conduit means is substantially longer than said catheter body and is comprised of at least one major section of length having an outer sheath formed from a wire coil surrounding a core of fiberoptic material, said coil being formed from wire having a rectangular cross section with coils being arranged close together, whereby said conduit means provides a guidewire function for advancing said catheter body in the body channel after it has utilized laser energy to remove the obstruction therein.
(12) An instrument for removing an obstruction in an internal body channel comprising:
(a) an elongated catheter body having a proximal end and a distal end, the distal end of which is adapted for insertion into a body channel, and having a first lumen including a proximal end and a distal end corresponding to the proximal and distal ends of said catheter body;
(b) a movable, elongated, combination guiding and laser transmission device positioned within said first lumen and adapted for transmitting laser energy to an arteriosclerotic site in a blood vessel, the combination guiding and laser transmission device including a flexible sheathing surrounding said transmission device for at least a substantial portion of its length said sheathing having a proximal end and a distal end corresponding to the proximal and distal ends of said catheter body, and having sufficient stiffness so that said device can be pushed through a body channel and turned therein by force applied near its proximal end and can also serve as a tracking means for said catheter body; and (c) treatment means at the distal end of said catheter body for reducing the obstruction, wherein said treatment means comprises a fixed laser transmission means contained within a second lumen of said catheter body.
(13) The device as described in claim 12 wherein said sheating is a coiled metal wire.
(14) The device as described in claim 13 wherein said coiled wire has a rectangular cross section and the coils are close together.
(15) The device as described in claim 13 wherein said metal sheathing has a modified "J" shaped tip at its distal end for ease of reaching arteriosclerotic sites within a blood vessel.
(16) The device as described in claim 12, wherein said combination guiding and laser transmission device comprises a bundle of glass fibers.
(17) The device as described in claim 12, wherein at least one opaque marker is provided at said distal end of said elongated catheter body, so that accurate positioning of the catheter body within a body channel can be controlled under fluoroscopy when in use.
(18) The device as described in claim 17, wherein a plurality of opaque markers are provided at spaced intervals between said distal and proximal ends of said elongated catheter body.
(19) The device as described in claim 17, wherein at least one intermediate portion of said combination guiding and laser transmission device is covered with an annular section of plastic material which enables a torsional force to be applied for turning the transmission device within said catheter body and within a body channel being treated.
an elongated catheter body adapted for insertion into a body channel having a first lumen throughout its length, said catheter body having a proximal end and an opposing distal end;
an elongated movable guide and laser transmission conduit means extending through said lumen of said catheter body and having a distal end that is extendable beyond the distal end of said catheter body and a proximal end, said proximal end of said conduit means adapted to be connected to a controlled source of laser enery; and trreatment means at the distal end of said catheter body for further reducing said obstruction following preliminary penetration thereof by said elongated movable guide and laser transmission means, wherein said treatment means comprises a laser transmission means fixed within a lumen of said catheter body and terminating at its distal end.
(2) The instrument as described in claim 1 including an inflatable means affixed to the outer surface of said catheter body near its distal end for sealingly engaging the interior walls of the body channel.
(3) The instrument as described in claim 1 wherein said treatment means comprises a plurality of glass fibers in a closely packed conduit having generally a circular cross-section, whose centreline is offset from the centreline of said catheter body.
(4) The instrument as described in claim 1 wherein said treatment means comprises a plularity of glass fibers in a closely packed conduit having generally a crescent shape that partially surrounds said elongated movable guide and laser transmission conduit means.
(5) The instrument as described in claim 1 wherein said treatment means comprises a plurality of fixed laser transmission conduit means spaced radially from and circumferentially spaced around said lumen of said catheter body.
(6) The instrument as described in claim 5 wherein said plurality of fixed laser transmission conduit means comprises three spaced apart groups of closely packed glass fibers, all terminating at the distal end of said catheter body, each said group being connectable to a laser power source.
(7) The instrument as described in claim 1 wherein said treatment means in said catheter body further comprises an inflatable means at its distal end which can be utilized to perform an angioplasty function on a diseased area of body channel following initial penetration thereof by said elongated movable guide and laser transmission conduit means.
(8) The instrument as described in claim 1 wherein elongated movable guide and laser transmission conduit means comprises an elongated member comprised of an outer coil of wire surrounding an inner core of fiberoptic material.
(9) The instrument as described in claim 1 wherein said catheter body is made of a flexible plastic material having a plurality of lumens along its length.
(10) The instrument as described in claim 1 wherein said catheter body is less flexible than said elongated movable guide and laser transmission conduit means.
(11) The instrument as described in claim 1 wherein said elongated movable guide and laser transmission conduit means is substantially longer than said catheter body and is comprised of at least one major section of length having an outer sheath formed from a wire coil surrounding a core of fiberoptic material, said coil being formed from wire having a rectangular cross section with coils being arranged close together, whereby said conduit means provides a guidewire function for advancing said catheter body in the body channel after it has utilized laser energy to remove the obstruction therein.
(12) An instrument for removing an obstruction in an internal body channel comprising:
(a) an elongated catheter body having a proximal end and a distal end, the distal end of which is adapted for insertion into a body channel, and having a first lumen including a proximal end and a distal end corresponding to the proximal and distal ends of said catheter body;
(b) a movable, elongated, combination guiding and laser transmission device positioned within said first lumen and adapted for transmitting laser energy to an arteriosclerotic site in a blood vessel, the combination guiding and laser transmission device including a flexible sheathing surrounding said transmission device for at least a substantial portion of its length said sheathing having a proximal end and a distal end corresponding to the proximal and distal ends of said catheter body, and having sufficient stiffness so that said device can be pushed through a body channel and turned therein by force applied near its proximal end and can also serve as a tracking means for said catheter body; and (c) treatment means at the distal end of said catheter body for reducing the obstruction, wherein said treatment means comprises a fixed laser transmission means contained within a second lumen of said catheter body.
(13) The device as described in claim 12 wherein said sheating is a coiled metal wire.
(14) The device as described in claim 13 wherein said coiled wire has a rectangular cross section and the coils are close together.
(15) The device as described in claim 13 wherein said metal sheathing has a modified "J" shaped tip at its distal end for ease of reaching arteriosclerotic sites within a blood vessel.
(16) The device as described in claim 12, wherein said combination guiding and laser transmission device comprises a bundle of glass fibers.
(17) The device as described in claim 12, wherein at least one opaque marker is provided at said distal end of said elongated catheter body, so that accurate positioning of the catheter body within a body channel can be controlled under fluoroscopy when in use.
(18) The device as described in claim 17, wherein a plurality of opaque markers are provided at spaced intervals between said distal and proximal ends of said elongated catheter body.
(19) The device as described in claim 17, wherein at least one intermediate portion of said combination guiding and laser transmission device is covered with an annular section of plastic material which enables a torsional force to be applied for turning the transmission device within said catheter body and within a body channel being treated.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/057,791 US4832023A (en) | 1987-06-03 | 1987-06-03 | Method and apparatus for reducing blockage in body channels |
| US057,791 | 1987-06-03 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1314309C true CA1314309C (en) | 1993-03-09 |
Family
ID=22012789
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000555432A Expired - Fee Related CA1314309C (en) | 1987-06-03 | 1987-12-24 | Method and apparatus for reducing blockage in body channels |
Country Status (7)
| Country | Link |
|---|---|
| US (1) | US4832023A (en) |
| EP (1) | EP0297190B1 (en) |
| JP (1) | JP2648324B2 (en) |
| AT (1) | ATE93701T1 (en) |
| CA (1) | CA1314309C (en) |
| DE (1) | DE3787278T2 (en) |
| ES (1) | ES2043672T3 (en) |
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Also Published As
| Publication number | Publication date |
|---|---|
| JP2648324B2 (en) | 1997-08-27 |
| DE3787278T2 (en) | 1993-12-16 |
| DE3787278D1 (en) | 1993-10-07 |
| JPH02140155A (en) | 1990-05-29 |
| US4832023A (en) | 1989-05-23 |
| EP0297190B1 (en) | 1993-09-01 |
| ES2043672T3 (en) | 1994-01-01 |
| ATE93701T1 (en) | 1993-09-15 |
| EP0297190A1 (en) | 1989-01-04 |
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