US 20070293853 A1
Apparatuses and methods for removing solid tissue from beneath a tissue surface are described. The methods rely on positioning an energy conductive element at a target site beneath the tissue surface and energizing the element so that it can vaporize tissue. The element is then moved in a pattern which provides the desired tissue removal geometry, such as spherical, ovoid, or cylindrical. Usually, the shaft is moved, typically rotated or reciprocated, and the energy conductive element is moved relative to the shaft, typically by pivoting a rigid element or bowing a flexible element.
1. A tissue ablation device comprising:
a shaft having a proximal end, a distal end, and a lumen therethrough,
a substantially rigid energy conductive straight cylindrical pin attached to pivot about a fixed point on the shaft near its distal end;
a means for causing the element to pivot relative to the shaft; and
an aspiration connector coupled to the lumen near the proximal end of the shaft.
2. The tissue ablation device of
a power supply connector disposed near the proximal end of the shaft and electrically coupled to the energy conductive element.
3. The tissue ablation device of
4. The tissue ablation device of
5. The tissue ablation device of
a motor attachable to the proximal end of the shaft.
6. The tissue ablation device of
7. The tissue ablation device of
8. The tissue ablation device of
9. The tissue ablation device of
10. The tissue ablation device as in
11. The tissue ablation device of
12. The tissue ablation device of
13. A method for performing tissue ablation comprising:
positioning an energy conductive element situated at a distal end of a shaft at a target tissue site;
operating a drive mechanism coupled to the conductive element to bow the conductive element between a substantially linear profile where the element lies directly over the shaft and a series of arcuate profiles continuously spaced progressively away from the shaft, thereby providing a continuous series of arcuate tissue removal paths;
while operating said drive mechanism, rotating the conductive element about the shaft and applying energy to the conductive element, thereby vaporizing all tissue in the path of the conductive element; and
while vaporizing said tissue, applying an aspiration source to a lumen included within the shaft, said lumen coupled to the distal end of the shaft in a region including the conductive element, and thereby withdrawing vaporized tissue from the target tissue site.
14. The method of
imaging the target tissue site and positioning the conductive element based on the image.
15. The method of
16. The method of
17. The method of
18. The method of
19. The method of
20. The method of
This patent application is continuation of pending U.S. patent application Ser. No. 10/635,691, filed on Aug. 5, 2003, which is a divisional of U.S. patent application Ser. No. 09/930,531, filed on Aug. 14, 2001, and issued as U.S. Pat. No. 6,663,626 on Dec. 16, 2003, which was a divisional of U.S. patent application Ser. No. 09/249,208, filed on Feb. 12, 1999, and issued as U.S. Pat. No. 6,296,639 on Oct. 1, 2001, the entire disclosures of which patent applications are incorporated herein by reference. In addition, U.S. patent application Ser. No. 09/249,208, originally included, but later disclaimed, a priority claim to U.S. Provisional application 60/092,572, filed Jul. 13, 1998, the entire contents of which are hereby incorporated by reference.
The present invention relates generally to medical devices, kits, and methods. More particularly, the present invention relates to apparatuses and methods for removing tissue from tissue regions beneath a tissue surface.
The removal of diseased and other tissues is the basis for many surgical procedures and is accomplished in many different ways. Most commonly, the target tissue is excised using a cutting blade, such as a scalpel, in open surgical procedures. Typically, the cutting blade is advanced into a tissue through an exposed tissue surface, and the target tissue is simply cut out and removed. While very effective for tissue removal at or near an exposed tissue surface, this approach is less effective for tissue removal from sites spaced below the closest exposed tissue surface.
For removal of target tissue below a tissue surface, a surgeon can simply cut down to the level of the target tissue and cut out and remove the tissue at that level. The need to cut down through “non-target” tissue is, however, disadvantageous in several respects. First, surgically cutting through the overlying healthy tissue can create a much bigger incision than is necessary for simply removing the target tissue. Moreover, the need to penetrate through relatively thick layers of overlying tissue can complicate identification of the target region, often requiring that larger volumes of tissue be removed to assure to complete removal. Additionally, the ability to cut down into internal organs during minimally invasive endoscopic procedures is significantly more limited than in open surgical procedures.
Surgical instruments for removing tissue beneath a tissue surface have been developed For example, instruments employing specialized cutting blades for chopping or “morcellating” tissue into small pieces and aspirating the resulting debris have been developed. While such instruments are at least theoretically capable of being manipulated to remove a defined volume of tissue beneath a tissue surface, their performance suffers in various ways. Most importantly, tissue morcellation can result in significant bleeding which is difficult to staunch. Thus, these techniques would not be useful in highly vascularized tissues, such as many muscle and organ tissues. Even when combined with electrosurgical coagulation, such tissue morcellation devices are probably not useful for the removal of large tissue volumes beneath a tissue surface where bleeding control is problematic.
For all of these reasons, it would be desirable to provide improved apparatuses and methods for tissue removal beneath tissue surfaces. In particular, the devices and methods should be suitable for use in minimally invasive procedures, such as procedures where the devices are introduced through a port and viewed under endoscopic viewing. The methods and devices should further allow access to a target tissue region with minimum disruption and damage to the overlying “non-target” tissue. Additionally, it would be desirable to provide tissue removal regions with a simplified approach for removing the debris resulting from the tissue removal. It would be particularly desirable to provide such tissue removal methods and devices which result in minimum or easily controlled bleeding at the tissue removal site. Such methods and apparatuses should still further provide for removal of controlled volumes, even relatively large volumes of at least 0.5 cm3, preferably at least 50 cm3, and still more preferably at least 500 cm3, or more. The methods and apparatuses should also be useful on a wide variety of tissue types and for a wide variety of specific procedures. At least some of these objectives will be met by the invention described hereinafter.
A loop electrode for radiofrequency electrosurgical excision of a tissue volume in solid tissue is described in Lorentzen et al. (1996) Min. Invas. Ther. & Allied Tecnol. 5:511-516.
Three-dimensional electrode arrays for deployment in solid tissue followed by the application of radiofrequency energy to necrose tissue volumes are described in U.S. Pat. Nos. 5,827,276; 5,735,847; and 5,728,143.
Atherectomy catheters having radially expansible blade structures intended for rotational stenotic excision in blood vessels are described in U.S. Pat. Nos. 5,556,408; 5,554,163; 5,527,326; 5,318,576; 5,100,423; and 5,030,201. In particular, U.S. Pat. No. 5,554,163, describes a catheter having a flexible “cutting” element that may be radially deployed from the catheter body. U.S. Pat. No. 5,100,423, describes a cutting structure comprising a plurality of helically-shaped cutting wires that can be connected to an electrosurgical power supply to effect cutting of obstructing matter in a blood vessel The following patents describe other electrosurgical instruments: U.S. Pat. Nos. 2,022,065; 4,660,571; 5,217,458; 5,578,007; 5,702,390; 5,715,817; 5,730,704; 5,738,683; and 5,782,828.
The present invention provides improved methods, devices, and kits for removing tissue from internal target sites disposed beneath a tissue surface The present invention can provide a number of advantages when compared to prior tissue removal techniques, including minimizing disruption of the tissue overlying the target site, i.e., between the tissue surface and an outer periphery of the target volume which is to be removed. In the preferred examples described below, access through the overlying tissue can be achieved with a single percutaneous or transcutaneous tissue tract sufficient to accommodate a single shaft of the apparatus. In addition to minimizing disruption of overlying tissue, the present invention can significantly reduce bleeding at the target site after tissue removal. In particular, by employing electrocautery as part of the tissue excision process, bleeding of the surrounding tissues can be substantially staunched.
Other advantages provided by the present invention include the ability to remove relatively large tissue volumes, typically, at least 0.5 cm3, often at least 50 cm3, and sometimes as large as 500 cm3, or larger. While the present invention is particularly suited for removing large volumes. The tissue removal can be effected in many tissue types, including those specifically set forth below, and tissue debris remaining after removal can be transported from the site, typically through the single access tract described above, usually by aspirating vapors and cellular debris which are produced as the tissue excision and vaporization stages occur. In addition or as an alternative to vapor aspiration, the tissue void which is being created may optionally be flushed with a suitable liquid or gas, preferably an electrically non-conductive liquid, such as sorbitol. Further optionally, the flushing medium may carry medications or other biologically active substances, such as antibiotics, pain killers, hemostatic agents, and the like. Such flushing may occur concurrently with the cutting, during brief periods when cutting is ceased, and/or after all cutting has been completed.
The present invention is suitable for removing defined volumes of tissue from a variety of different tissue types, including breast tissue, liver tissue, kidney tissue, prostate tissue, lung, uterine, and the like. Thus, the tissue surface may be on the patient's skin, e.g., in the case of breast tissue removal, or the tissue surface may be located subcutaneously, e.g., in the case of internal body organs. In the former case, access to the target site may be achieved transcutaneously or subcutaneously, where the removal device penetrates directly through the skin. In the latter case, a secondary procedure is needed to access the tissue surface of the internal body organ. The secondary procedure may be an open surgical procedure where the overlying skin and body structures are surgically opened. Alternatively, the secondary procedure may itself be minimally invasive where small incisions or ports are used to introduce the devices of the present invention together with any necessary or useful auxiliary devices for performing the tissue removal. Typically, such minimally invasive surgeries will be performed under endoscopic visualization where the treating physician views the procedure on a video screen. As a still further alternative, access to internal body organs may be achieved intraluminally, preferably endoscopically. Typically, such intraluminal, endoscopic access will be obtained through body lumens having natural orifices, such as the esophagus, colon, uterus, fallopian tubes, sinuses, uterus, ureter, and urethra. Such access will typically be achieved using a flexible catheter which can provide a platform for advancing the energy conductive elements, as described in more detail below.
The depth of the target site will depend on the nature of the tissue and the nature of the disease or other condition being treated. Typically, the closest periphery of the target site will be located between the adjacent or available tissue surface by distance in the range from 0.5 cm to 15 cm, usually from 5 cm to 7 cm. The volume of tissue to be removed will typically be in the range from 0.5 cm3 to 500 cm3, typically being from 5 cm3 to 300 cm3. As described in more detail below, the geometry or shape of the removal volume, i.e., the void left in tissue following tissue removal, will generally be spherical, ovoid, cylindrical, or other shape characterized by at least one axis of symmetry. The axis of symmetry will usually arise because of the manner in which the tissue removal devices are used, as described in more detail below.
In a first aspect, methods according to the present invention comprise positioning an energy conductive element at a target site in tissue beneath a tissue surface. The energy conductive element is energized and moved through successive tissue layers, where the element is energized with sufficient energy to vaporize tissue in said successive layers. Such sequential removal of successive layers of tissues will produce a desired removal volume, typically having the geometries and sizes set forth above.
In a second aspect, methods according to the present invention comprise providing an instrument having a shaft and a repositionable energy conductive element on the shaft. The element is advanced through the tissue surface to a target site in solid tissue, where the element is in a low profile configuration (e.g., radially collapsed into the shaft) and the proximal end of the shaft remains outside of the solid tissue to permit manipulation. The shaft is moved relative to the tissue surface and the element repositioned relative to the shaft while the element is being energized with sufficient energy to remove tissue. The combined movements of the shaft and the element relative to the shaft cause the element to pass through successive tissue layers at or near the target site and to vaporize said layers to produce the desired removal volume.
Usually, the methods for removing tissue as described above will further comprise imaging the solid tissue and positioning the energy conductive element based on the image. The imaging may be any type of conventional, two-dimensional or three-dimensional medical imaging, including fluoroscopic imaging, ultrasonic imaging, magnetic resonance imaging, computer-assisted tomographic imaging, optical imaging, and the like. Positioning of the energy conductive device may be entirely manual, where the user may view the image of the target site either in real time, as a pre-operative image only, or a combination of real time and pre-operative images. Alternatively, the energy conductive device may be automatically positioned based directly or indirectly on the image using robotic or other automatic positioning equipment. Optionally, such automatic positioning equipment can be programmed based on a pre-operative or real time image of the target region.
The methods of the present invention will preferably further comprise collecting vapors and cellular debris produced by the tissue vaporization and removing those vapors through the overlying tissue and the tissue surface. Usually, vapor removal will comprise aspirating the vapors from the site or volume of tissue removal as the vapors are being produced. Usually, the vapors will be aspirated through a tissue tract between the tissue surface and the target site, more typically being through a lumen in the shaft of the device used for removing the tissue.
The energy conductive element is moved through a pattern of successive tissue layers which, in the aggregate, will form the desired tissue removal volume. The energy conductive element may be moved in any manner, typically being moved by manipulation of the shaft upon which it is mounted. For example, the energy conductive element may be moved relative to the shaft while the shaft itself is moved so that the combined motions of the element and the shaft define the desired removal geometry. Alternatively, the energy conductive element could be moved on the shaft while the shaft remains stationary. In the latter case, a servo or other drive mechanism could be provided within the shaft to move the energy conductive element through its desired pattern.
The shaft will usually be rotated and/or axially reciprocated in order move the energy conductive element through tissue along or about one axis. In turn, the energy conductive element may be pivoted, bowed, or otherwise moved or deflected relative to the shaft to provide further axes or dimensions of the removal volume. In a first exemplary removal method, a shaft having a rigid energy conductive member is introduced to an internal tissue target site with the element lying coaxial to the shaft. The shaft is then rotated and the element pivoted to provide a spherical or partial spherical tissue removal geometry. In a second exemplary embodiment, the energy conductive element comprises one or more flexible elements which may be bowed to form a series of arcuate tissue removal paths as the shaft is rotated. Other approaches include disposing a lateral energy conductive element beneath tissue and simultaneously rotating and reciprocating the support shaft so that a cylindrical removal volume is formed, with the length of the cylinder determined by the length of reciprocation. Other combinations of motion between the shaft and energy conductive element may also be utilized.
The type of energy transmitted or provided through the energy conductive element will preferably provide for heating of the tissue. For example, high frequency energy, such as radiofrequency or microwave energy, may be delivered in a monopolar or bipolar manner to vaporize the tissue. Typically, the radiofrequency energy will be applied with a cutting waveform at a frequency in the range from 100 kHz to 2 MHz, and a current in the range from 1 mA to 50 A, 0.5 mA to 10 A, depending on surface contact area and tissue type. Alternatively, energizing can comprise directly heating the element, typically to a temperature in the range from 100° C. to 300° C., usually 600° C. to 2000° C. Heating is preferably achieved using optical energy, e.g., laser energy, delivered through a fiberoptic element within the energy conductive element. Alternatively, heating can be achieved using an electrical resistance heater which comprises or is disposed within the energy conductive element.
The present invention further provides apparatus for removing tissue. In a first instance, a tissue ablation device comprises a shaft having a proximal end, a distal end, and a lumen therethrough. At least one flexible energy conductive element is disposed near the distal end of the shaft, and a means for bowing the element between a substantially linear profile (where the element lies directly over the shaft) and a series of arcuate profiles spaced progressively further from the shaft is provided. The bowing means will typically include a mechanism for axially advancing a proximal end of the flexible energy conductive element. By preventing or limiting axial movement of a distal end of the flexible energy conductive element, the element will be caused to bow radially outwardly in the desired arcuate configuration. Alternatively, a proximal end of the flexible energy conductive element may be fixed or limited relative to the shaft and a rod or other device for proximally retracting a distal end of the energy conductive element provided. It would further be possible to simultaneously draw both ends of the element together. Other mechanisms, such as expandable cages, parallel linkages, shape heat memory drivers, or the like, may also be provided for bowing the element radially outwardly. The tissue ablation device will further comprise an aspiration connector coupled to the lumen for aspirating vapors produced at the distal end. A power supply connector is further provided to permit electrical coupling of the energy conductive element to a desired power supply.
The shaft of such devices may be substantially rigid, typically having a diameter in the range from 0.5 mm to 20 mm, typically 2 mm to 7 mm, and a length in the range from 2 cm to 50 cm, usually 5 cm to 25 cm. The devices will also typically have a handle secured at or near the proximal end of the shaft, and at least one of the aspiration and power supply connectors will usually be disposed on the handle. Optionally, a motor may be provided in the handle or separate from the handle to help drive the device. For example, the motor could be connected to rotate and/or reciprocate the shaft relative to the handle in order to drive the device in a desired manner. Alternatively or additionally, the motor could be connected to bow the flexible energy conductive element in a controlled manner. In the exemplary embodiments, however, all motions of both the shaft and the energy conductive element will be manual.
The shaft of such devices may also be flexible, typically in the form of a catheter having a diameter in the range from 0.5 mm to 10 mm, and a length in the range from 25 cm to 250 cm. Usually, when used for access to natural body lumens, such as the colon, uterus, esophagus, fallopian tubes, sinuses, uterus, ureter, and the urethra, the shafts will be introduced through or as part of an endoscope. The cutting elements for performing the tissue removal will then be deployed from or near the distal end of the catheter. Typically, the cutting elements will be deployed laterally from the catheter and a stylet or other introducer will be utilized to permit subcutaneous introduction as required by the present invention. In other cases, the devices may be introduced intravascularly, typically through the femoral or other veins, to target organs, such as liver, kidney, prostate, lung, and uterus. The cutting elements can then be deployed from the catheters through the blood vessel wall into the target organ.
The energy conductive elements maybe configured to provide for any of the energy delivery modes set forth above. In particular, energy conductive elements may comprise electrodes suitable for the delivery of high frequency electrical energy, typically radiofrequency energy having the particular frequencies and other characteristics set forth above. Alternatively, the energy conductive elements may be configured to provide for direct heating of the elements themselves, usually comprising either an optical fiber for delivering light energy or comprising an electrical resistance heater together with the necessary wiring to connect the resistance heater to a suitable power source.
The flexible energy conductive elements may take a wide variety of forms. A first exemplary form will be a simple elastic or super elastic metal wire, typically having a diameter in the range from 0.1 mm to 5 mm, preferably from 0.5 mm to 2 mm. The wire may be formed from any suitable material, including stainless steel, nickel titanium alloy, tungsten, or the like. The wire may be composed of single material or may be a composite material, e.g., where a portion of the wire is selected for high electrical conductivity while another portion of the wire selected for elastic or other properties. The electrically conductive elements may also be in the form of ribbons, i.e., having a width substantially greater than its thickness. Such ribbon structures will have greater mechanical rigidity when they are radially expanded through their narrow dimension. Often times, different types of energy conductive elements may be combined in a single device. In an exemplary device, a pair of wire elements are disposed on opposite sides of the shaft with a pair of ribbon elements offset by 90°. Each of the four elements is coupled to the other so that they open and close (be “bowed” and relaxed) synchronously. Usually, such structures will be formed for bipolar operation, where the ribbon elements will have a much greater surface area than the wire elements so that the ribbons connect as a dispersible electrode, i.e., an electrode where minimum cutting takes place. In such cases, the ribbon electrode can also serve to act as a surface coagulation electrode to help control bleeding. In some instances, it will be desired that the wire cutting electrodes be advanced slightly radially ahead of the ribbon electrodes. Such a design allows the ribbons to open under a spring force to “automatically” expand as the wire electrodes remove successive layers of tissue.
A second exemplary tissue ablation device comprises a shaft having a proximal end, a distal end, and lumen therethrough. A substantially rigid energy conductive element is pivotally attached to the shaft near its distal end. The device further includes a means for causing the element to pivot, such as a push wire, pull wire, rack and pinion driver, gear driver, or the like. The device will further include aspiration and power supply connectors, both as generally described above.
The nature of the shaft and the types of energy conductive elements which may be deployed are all similar to corresponding aspects of the first embodiment of the tissue ablation device described above. The nature of the pivotally connected energy conductive element will, however, differ. The pivotally attached energy conductive element will usually be straight, typically being in the form of a cylindrical pin having a length in the range from 1 mm to 75 mm, and a width or diameter in the range from 0.5 mm to 5 mm. A preferred geometry includes a circular or flat cross-section. The rigid element may be pivotally attached near its middle, near one end thereof, or anywhere else along its length. In an illustration example, the element is pivotally attached near its middle in order to effect a spherical tissue removal volume as the device is rotated and the pin pivoted through 90° or more, as described in detail below.
The present invention still further provides kits comprising a device having an energy conductive element which is connectable to a power supply and which provides energy sufficient to vaporize successive layers of tissue as the element is moved therethrough. The device may have any of the configurations described above. The kit will further comprise instructions for use setting forth a method as in any of the methods described above. Typically, at least the device will be present in a sterile package, and the instructions for use may printed on a portion of the package or may be on a separate instruction sheet accompanying the package. Suitable packages include pouches, trays, boxes, tubes, or the like. Suitable sterilization techniques include gamma radiation, ethylene oxide treatment, or the like.
Referring now to
Referring now to
After the device 10 is initially positioned, as shown in
The use of radio or other high frequency electrical energy is preferred for forming the tissue void as just described. The radiofrequency energy will not only vaporize tissue, permitting the resulting vapors to be withdrawn through the lumen of the shaft 12 (typically by connecting aspiration port 24 to a suitable vacuum source), but also cauterize the inner surface of the void as it is being formed. Such cauterization, in turn, limits or controls bleeding as the tissue is being removed. After the removal is complete, it may be desirable to introduce collagen, gelatin, autologous tissue, or other biologically compatible tissue fillers into the void region to inhibit tissue collapse, further control bleeding, deliver drugs (which may be incorporated into such matrices), or the like.
Alternatively, after a tissue void has been created, the void can simply be collapsed in order to “debulk” a tissue region. For example, for the treatment of benign prostate hyperplasia, it may desirable to remove a small volume of tissue and thereafter collapse the tissue to release pressure on the urethra. Optionally, a tissue glue, sealant, or other material, may be introduced after the tissue void has been collapsed in order to maintain the collapsed configuration.
Referring now to
Referring now to
An energy conductive element 50 provided in device 40, however, differs from that described with respect to device 10. In particular, a flexible energy conductive device 50, typically in the form of an elastic wire, is provided so that it can emerge radially outwardly from a slot 52 formed near the distal end 44 of the shaft 42. The wire 50 may be bowed outwardly by advancing a proximal portion of the wire 50 in a distal direction, as shown by arrow 56. It will be appreciated that the wire will assume an arcuate configuration, and that the degree to which the arc extends radially outward from the shaft will depend on how far the proximal end has been distally advanced. The wire 50 will be coupled to a suitable energy source through power supply connector 52, typically to a radiofrequency power supply.
Use of the device 40 is illustrated in
Referring now to
Ribbon electrodes can also be used by themselves, either singularly or in multiplies, in the devices and methods of the present application. In particular, a ribbon electrode having the cross-sectional configuration shown in
A further embodiment of an energy conductive element array 100 constructed in accordance with the principles of the present invention is illustrated in
While the above is a complete description of the preferred embodiments of the invention, various alternatives, modifications, and equivalents may be used. Therefore, the above description should not be taken as limiting the scope of the invention which is defined by the appended claims.