US20060241577A1 - Tissue biopsy and treatment apparatus and method - Google Patents

Abstract

A method of treating a tumor includes providing a tissue biopsy and treatment apparatus that includes an elongated delivery device that has a lumen and is maneuverable in tissue. A sensor array having a plurality of resilient members is deployable from the elongated delivery device. At least one of the plurality of resilient members is positionable in the elongated delivery device in a compacted state and deployable with curvature into tissue from the elongated delivery device in a deployed state. At least one of the plurality of resilient members includes at least one of a sensor, a tissue piercing distal end or a lumen. The sensor array has a geometric configuration adapted to volumetrically sample tissue at a tissue site to differentiate or identify tissue at the tissue site. At least one energy delivery device is coupled to one of the sensor array, at least one of the plurality of resilient members or the elongated delivery device. The apparatus is then introduced into a target tissue site. The sensor array is then utilized to distinguish a tissue type. The tissue type information derived from the sensor array is utilized to position the energy delivery device to ablate a tumor volume. Energy is then delivered from the energy delivery device to ablate or necrose at least a portion of the tumor volume. The sensor array is then utilized to determine an amount of tumor volume ablation.

Description

CROSS-RELATED APPLICATIONS
• This application claims the benefit of priority to U.S. Provisional Application Ser. No. 60/193,544 filed Mar. 31, 2000, entitled “Tissue Biopsy, Monitoring and Treatment Apparatus and Method”, which is fully incorporated by reference herein. This application is also related to a co-pending application attorney docket number 13724-844.
FIELD OF THE INVENTION
• This invention relates generally to a method for performing an in vivo tissue biopsy sample using minimally invasive methods. More particularly, the invention to relates to method and apparatus for performing in vivo tissue biopsy using optical methods. Still more particularly, the invention relates to a method and apparatus for performing an in vivo tissue biopsy to discriminate between diseased and healthy tissue and facilitate tissue treatment.
BACKGROUND OF THE INVENTION
• Various ablative procedures can be used to treat diseased and/or abnormal tissue. These methods cause physiological and structural changes intended to cause necrosis of the selected target tissue. During ablative procedures of diseased and other abnormal tissue, clinicians encounter numerous difficulties and challenges, these include (i) locating the target tissue, (ii) the need to perform a biopsy and diagnose diseased tissue versus healthy tissue, (iii) correct device placement, (iv) monitoring ablation progress, (v) assuring a (healthy tissue) margin, and (vi) assessing the completed ablation. Current ablative technologies have failed to recognize and therefore, properly address these requirements.
SUMMARY OF THE INVENTION
• An embodiment of the invention provides a method of treating a tumor that includes providing a tissue biopsy and treatment apparatus that includes an elongated delivery device that has a lumen and is maneuverable in tissue. A sensor array having a plurality of resilient members is deployable from the elongated delivery device. At least one of the plurality of resilient members is positionable in the elongated delivery device in a compacted state and deployable with curvature into tissue from the elongated delivery device in a deployed state. At least one of the plurality of resilient members includes at least one of a sensor, a tissue piercing distal end or a lumen. The sensor array has a geometric configuration adapted to volumetrically sample tissue at a tissue site to differentiate or identify tissue at the tissue site. At least one energy delivery device is coupled to one of the sensor array, at least one of the plurality of resilient members or the elongated delivery device. The apparatus is then introduced into a target tissue site. The sensor array is then utilized to distinguish a tissue type. The tissue type information derived from the sensor array is utilized to position the energy delivery device to ablate a tumor volume. Energy is then delivered from the energy delivery device to ablate or necrose at least a portion of the tumor volume. The sensor array is then utilized to determine an amount of tumor volume ablation.
• An embodiment of the invention provides a tissue biopsy and treatment apparatus that comprises an elongated delivery device that is positionable in tissue and includes a lumen. A sensor array having a plurality of resilient members is deployable from the elongated delivery device. At least one of the plurality of resilient members is positionable in the elongated delivery device in a compacted state and deployable with curvature into tissue from the elongated delivery device in a deployed state. At least one of the plurality of resilient members includes at least one of a sensor, a tissue piercing distal end or a lumen. The sensor array has a geometric configuration adapted to volumetrically sample tissue at a tissue site to differentiate or identify tissue at the target tissue site. At least one energy delivery device is coupled to one of the sensor array, at least one of the plurality of resilient members or the elongated delivery device.
• Yet another embodiment of the invention provides a method for tumor detection, wherein a primary optically labeled marker or antibody is infused into a patient or injected into a target tissue or organ site containing a tumor and specifically binds to a marker produced by or associated with a tumor. The target tissue or organ site is scanned with a biopsy ablation apparatus including a sensor array and the binding sites of the labeled marker antibody are located by detecting elevated levels of optical label signal intensity at such sites with the sensor array. This information can be digitally stored and displayed on a monitor device to accurately position the biopsy ablation apparatus within the tumor s to deliver energy to necrose or ablate the tumor resulting in an ablation volume. A second marker which binds or reacts with necrosed tumor tissue can infused or injected into the tumor site before, during or after the delivery of ablating energy. The sensor array is utilized to detect the signal from the second marker ablation volume and this signal digitally stored and superimposedly display over tumor volume image so as to determine the size of the ablation volume relative to the tumor volume. This embodiment provides two key benefit to the physician: (i) visual confirmation that the tumor has been completely ablated/necrosed, (ii) selective over control the amount of healthy tissue margin that is ablated beyond the tumor volume to improve clinical outcomes of the procedure.
BRIEF DESCRIPTION OF THE FIGURES
• FIG. 1 is a lateral view illustrating the placement of an embodiment of a tissue biopsy and treatment apparatus at a tissue site.
• FIG. 2 is a lateral view illustrating the components of an embodiment of a biopsy and treatment apparatus including the elongated member, sensor array, resilient members and energy delivery device and advancement member.
• FIGS. 3aand3bare cross sectional and perspective views illustrating embodiments of the resilient member having a slot.
• FIG. 3cis a perspective view illustrating an embodiment of the sensing member fixedly positioned to the resilient member.
• FIG. 4 is a perspective view illustrating an embodiment of a biopsy and treatment apparatus having an emitting member and detecting member positionable positionable in the resilient member.
• FIGS.5 is a schematic view illustrating various optical tissue interactions and properties.
• FIG. 6 is a perspective view illustrating an embodiment the sensing members fixedly positioned within the resilient member.
• FIG. 7 is a perspective view illustrating the use of different wavelengths to sample multiple tissue volumes in an embodiment of the invention.
• FIGS. 8a-8dare perspective views illustrating various arrangements of the emitting and detecting members;FIG. 8aillustrates an embodiment having a centrally positioned emitter member surrounded by detector members;FIG. 8billustrates an embodiment having centrally a positioned detector member surrounded by emitter members;FIG. 8cillustrates anembodiment having emitters22meanddetectors22mdlocated in linear arrangements that are substantially perpendicular or have a selectable angle;FIG. 8dillustrates an embodiment having multiple and independently positionable and rotatable sensor arrays.
• FIG. 9 is a perspective view illustrating an embodiment of a biopsy and treatment apparatus having sensors members positionable distally to the energy delivery member.
• FIG. 10 is a perspective view illustrating an embodiment of the invention having a multiple wavelength laser light source.
• FIG. 11 is a perspective view illustrating use of an optical marker compound and binding agent in an embodiment of the invention.
• FIG. 12 is a perspective view illustrating an embodiment of a biopsy and treatment apparatus configured to detect metabolic chromophores.
• FIG. 13 is a perspective view illustrating an embodiment of a biopsy and treatment apparatus configured to generate a 3D map of the tumor.
• FIG. 14ais a perspective view illustrating use of sensor array to monitor a developing ablation volume.
• FIG. 14bis a plot of spectral signal intensity verses time for a sample volume of ablating tissue illustrating quantitative determinants of an ablation endpoint.
• FIG. 15 is a lateral view illustrating a control and display unit used in various embodiments of the invention.
• FIGS. 16a-16care perspective views illustrating use of the sensor array to assure proper placement of the energy delivery members in the tumor mass in an embodiment of a method of the invention.
• FIGS. 17aand17bare perspective views illustrating use of the sensor array to detect an incomplete ablation in embodiments of a method of the invention.
• FIG. 18ais a lateral view illustrating the configuration of the introducer.
• FIGS. 18band18care cross sectional views illustrating cross-sectional profiles of the introducer.
• FIG. 19 is a lateral view illustrating an embodiment of a deflectable introducer along with the components of the introducer.
• FIG. 20 is a lateral view illustrating an embodiment of a tissue biopsy and treatment apparatus with a handpiece and coupled aspiration device, fluid delivery device and fluid reservoir
• FIGS. 21a-21fare lateral views illustrating various configurations of the electrode including ring-like, ball, hemispherical, cylindrical, conical and needle-like.
• FIG. 22 is lateral view illustrating an embodiment of a needle electrode configured to penetrate tissue.
• FIG. 23 is lateral view illustrating an embodiment of an electrode having at least one radii of curvature.
• FIG. 24 is lateral view illustrating an embodiment of the electrode having a radii of curvature, sensors and a coupled advancement device.
• FIG. 25 is a perspective view illustrating an embodiment of the electrode that includes insulation sleeves positioned at exterior surfaces of the electrode(s) so as to define an energy delivery surface.
• FIG. 26 is a perspective view illustrating an embodiment of the electrode that includes multiple insulation sleeves that circumferentially insulate selected sections of the electrode(s).
• FIG. 27 is a perspective view illustrating an embodiment of the electrode with insulation that extends along longitudinal sections of the electrodes to define adjacent longitudinal energy delivery surfaces.
• FIG. 28 is a cross-sectional view of the embodiment ofFIG. 27.
• FIG. 29 is a lateral view illustrating an embodiment of the apparatus with an electrode having a lumen and apertures configured for the delivery of fluid and the use of infused fluid to create an enhanced electrode.
• FIG. 30 is a block diagram illustrating a controller, power source, power circuits and other electronic components used with an embodiment of a control system other embodiments of the invention.
• FIG. 31 is a block diagram illustrating an analog amplifier, multiplexer and microprocessor used with an embodiment of a control system or other embodiments of the invention.
DETAILED DESCRIPTION
• Embodiments of the present invention provide a method and apparatus to optically biopsy a tissue and use the information to diagnose a tumor, accurately position an energy delivery device, visually monitor and confirm complete ablation of the tumor. Further embodiments of the invention include one or more sensing members or sensing arrays that can be deployed independently or simultaneously to enable probing of target tissue by optical or other means. Deployment of each array is controlled such that telemetry can be used with optical, temperature and impedance feedback to both identify tissue and map the topography of tissue types and structures to facilitate proper placement of an energy delivery device to ablate the tumor. These and other embodiments of the invention allow for the control and determination of a clinical endpoint while significantly reducing the risk of incomplete ablation or unwanted damage to critical anatomical structures due to improper device placement.
• Specific embodiments are configured to utilize inputs from the sensor to distinguish and identify the distinct spectral profiles that are generated by different tissues. The apparatus is further configured to employ analytical methods to compare these profiles and utilize them to accurately identify and distinguish between tissue types. Such tissue comparison and identification is particularly applicable to the detection of metastases and other types of tumors. This is due to the fact that metastases are growths of tissue from cells originating in a different part of the body from the subsequent tumor site that they cause. As such these different body tissues have different pathological features, the spectral profile comparison can be used to discern a metastatic or other non-native tumor within the target tissue sample.
• FIG. 1 shows an embodiment of a tissue biopsy andtreatment apparatus10 configured to optically biopsy and treat atumor mass5″ in atarget tissue site5′ by volumetrically sampling the tissue mass and delivering energy or other treatment to produce anablation volume5av. Referring now toFIGS. 1 and 2, an embodiment ofbiopsy treatment apparatus10 comprises an elongated member orintroducer12 having alumen13, aproximal portion14, adistal end16, one or moreresilient members18 positionable inlumens13 and one ormore sensing members22mpositionabe inlumens72 disposed withinmembers18.Distal end16 may be sufficiently sharp to penetrate tissue including fibrous and/or encapsulated tumor masses, bone, cartilage and muscle.Lumens13 may extend over all or a portion of the length ofintroducer12.Members18 can comprise aplurality18plofresilient members18 configured to be positionable inlumen13 and advanceable in and out ofdistal end16 by anadvancement device15 oradvancement member34 or other means described herein.Resilient members18 can be deployed with curvature fromintroducer12 to collectively define avolume5avintarget tissue site5′. In an embodiment all, or a portion, of one ormore members18 can be an energy delivery device orenergy delivery member18edescribed herein.Energy delivery device18ecan be coupled to an energy source orpower supply20 and can also include one ormore lumens72.
• In various embodiments,introducer12 can be flexible, articulated and steerable and can contain fiber optics (both illumination and imaging fibers), fluid and gas paths, and sensor and electronic cabling. In anembodiment introducer12 can be configured to both pierce tissue and also be maneuverable within tissue. This can be achieved through the use of flexible portions coupled to a tissue piercingdistal end16 that can be a needle or trocar tip integral or joined tointroducer12.Introducer12 can be sufficiently flexible to move in any desired direction through tissue to a desiredtissue site5′. In related embodiments,introducer12 is sufficiently flexible to reverse its direction of travel and move in direction back upon itself This can be achieved through the use of flexible materials and/or deflecting mechanisms described herein. Also,introducer12 can be coupled at itsproximal end14 to ahandle24 orhandpiece24.Handpiece24 can be detachable and can includeports24′ andactuators24″.
• One ormore sensors22 can be coupled tointroducer12,resilient members18 orenergy delivery device18e. In an embodiment,sensors22 can comprise one ormore sensing members22mthat can be positionable withinlumens72 ofmembers18 and configured to be advanceable in and out ofindividual members18 or can be coupled to an exterior ofresilient member18.Sensing members22mcan comprise a plurality ofmembers22mplpositioned in multipleresilient members18.Sensing members22m, orsensors22 coupled toresilient members18 can be deployed independently or simultaneously to enable probing oftarget tissue5′ in multiple locations. Deployment of sensingmember22morsensors22 can be controlled such that telemetry can be used with optical, temperature and impedance feedback to identify tissue types and map the topography of tissue masses, tumors or tissue structures.
• 33.Sensing members22mcan also be deployed with curvature frommembers18 to collectively define avolume5sv(also calledsample volume5sv) that is volumetrically sampled by sensingmember plurality22mpl. Collectively, theplurality22mpof deployedsensor members22morplurality18plof deployedresilient members18 with coupledsensors22 can comprise a 3 dimensional orvolumetric sensor array22a. By havingsensors22 in multiple locations andplanes sensor array22ais configured to volumetrically sample (e.g. sample in multiple locations) tissue withintarget tissue site5′ includingtumor mass5″.Sensor array22ais further configured to be able to simultaneously sample tissue at multiple locations withinvolume5svortissue site5′ to perform one or more of the following: (i) locate the position of thetumor mass5″, (ii) discern the position or deployment distance of theenergy delivery devices18, (iii) monitor the developing ablation volume, (iv) perform tissue sensing biopsy and identification by comparing signals between two or more site (e.g. known healthy tissue and suspected diseased tissue). In variousembodiments sensor array22aand/ormember plurality18plcan be configured to define a variety of shapes forsample volumes5svincluding, but not limited to, a hemisphere, a sphere, an oval, a cone, pyramidal, a polyhedron or a tetrahedron.
• Referring now toFIGS. 3aand3b, in an alternativeembodiment sensor member22mcan be advanced through aslot72sin or on the surface ofresilient member18.Slot72sserves as track to guide and advancesensor member22m.Slot72 also serves to increase the torsional flexibility ofmember18 and to lesser extent lateral flexibility (the reciprocal of stiffness). The size and shape ofslot72scan also configured to increase the lateral flexibility ofmember18 with a minimal affect on lateral flexibility (e.g. less than 10%). Shapes forslot72scan include but are not limited to substantially semi-ovoid or semi-circular. In various embodiments the torsional flexibility ofmember18 can be increased in the range of 10 to 200% with specific embodiments of 25, 50 and 100% with increases in lateral flexibility being lower in each case. Also in various embodiments, the torsional flexibility ofmember18 can be controllably adjusted via the length ofsensor member22mpositioned withinslot72s. In oneembodiment member18 with aslot72 has a maximum flexibility whenslot72 is empty, as increasing lengths ofsensor member22mare advanced withinslot72member18 flexibility is decreased untilsensor member22mcompletely fillsslot72s. In a related embodiment shown inFIG. 3c, sensingmembers22mcan be fixedly attached to the exterior ofresilient member22 either inslot72sor adhered to the surface ofmember18 using an adhesive known in the art.
• In various embodiments,multiple sensing members22mcan be positioned and deployed from asingle lumen72 ofresilient member18 and/or fromlumen13 ofintroducer12. Referring now toFIGS. 4 and 5, in an embodiment, two sensingmembers22mcan be positioned in alumen72 of one or more resilient members18: alight emitting member22me, configured to emit an incident orprobe beam22ib; and alight detecting member22md, configured to detect returning light22rbresulting from various optical tissue interactions (including scatter, reflectance or absorbance) ofincident beam22ibbytissue5 as is shown inFIG. 5.
• In these andother embodiments members22m,22meand22mdcan be optical fibers including glass fiber known in the art such as those manufactured by the Dow Coming Corporation (Midland, Mich.) or Polymicro Technologies (Phoenix, Ariz.). Thediameter22doffiber22mcan be in the range of 0.001 to 0.010″ with a preferred embodiment of about 0.004″ (without cladding). When light emittingmember22meis a fiber optic, one ormore members22mecan include or be coupled (preferably at itsdistal end22med) to a collimating or focusinglens221 to collimate, and/or increase or decrease the size ofincident beam22ib. Similarly light detectingfiber22mdcan include or be coupled to acollimating lens221 preferably at theproximal end22mdpofmember22 to collimate returning light prior22rbprior to its entry into a optical measurement device described herein.
• In an alternative embodiment shown inFIG. 6, sensingmembers22 including emittingmember22meand detectingmember22md22mecan be fixedly positioned withinresilient member18 such that their distal ends are substantially flush with thedistal end18deofresilient member18 or can fixed in other arrangements such as protruding slightly out ofdistal end18deby several thousandths of inch or more or being recessed by a similar amount withindistal end18de. These embodiments provide the benefit of maintaining the optical relationship between the emitting and detectingmembers22meand22mdconstant, reducing signal variations due to movement of either member. In a related embodiment, sensingmembers22meand22mecan also be fixedly positioned at or near thedistal end16 ofintroducer12.
• Sensing members22 can be arranged in variety of configurations to perform one or more desired functions (e.g. tissue identification). Eachresilient member18 can have one ormore sensing members22. Somemembers18 may haveemitters22meand somedetectors22md, so that selectable portions of tissue betweenmembers18 can be interrogated via different optical paths.Emitters22meanddetectors22mdcan be positioned anywhere within or outside ofmembers18 including at thetips18deofmembers18 where they can be fixedly positioned. Alternative embodiments may compriseemitters22meanddetectors22mdpositioned on passive or otherwise non-energy deliveryresilient members18 so as to position at least some of the emitter and detectors beyond the developing orcomplete ablation volume5sv. Such configurations allow for monitoring outside of tissue outside of the developing ablation volume to simultaneously compareun-ablated tissue5 andablated tissue5avas well as reduce signal noise and artifacts from energy delivery within the ablation volume.
• Referring back toFIGS. 2 and 4, in various embodiments one ormore sensing member22mcan coupled to anoptical switching device29 or otherwise configured such that their function can be dynamically switched from an emitter to a detector mode and vice versa. By changing the optical function of sensingmember22m(e.g. from receiving to emitting) during the process of scanning or interrogating a desiredtissue sample volume5sv, directional biases, signal artifacts and detection errors can be reduced improving detection sensitivity. Further, different emitter detector combinations can be employed to obtain more accurate higher resolution signals and hence more detailed information about the target tissue. When both emittermember22meand detectingmember22mdare located in thesame member18, they can be operated simultaneously for localized tissue sampling and interrogation. Such configurations allow for the comparison of tissue adjacent oneresilient member18′ to that of anotherresilient member18″. In a related embodiment, emitting or detectingsensing members22 on multiple and/or distantresilient members18 can be operated collectively to obtain a more global interrogation of a desiredsample volume5svusing one or more wavelengths.
• In various embodiments separate wavelengths can be used to simultaneously sample different locations withintarget tissue site5′. In an embodiment shown inFIG. 7 a first interrogation wavelength or group ofwavelengths7′ can be used to sample a localfirst volume5sv1 and a second wavelength orgroup wavelengths7″ for asecond volume5sv2 and a third wavelength for larger orglobal sample volume5sv3 defined or circumscribed by multiple sensor tippedmembers18 orsensing members22. Eachsample volume5svprobed with a givenwavelength7 results in a separatespectral profile19s. Thussample volumes5sv1,5sv2 and5sv3 producespectral profiles19s1,19s2 and19s3 respectively.
• Referring now toFIGS. 8a-8d, in various embodiments light emittingmembers22meand light detectingmembers22mdcan be arranged inarrays22ahaving a variety of geometric arrangements and relationships so as to optically sample different volumes oftissue5svusing different optical paths and/or optical tissue interactions. Such embodiments provide the benefit of improved acquisition, accuracy and analysis of thespectral signal19sfrom a givensample volume5svto compensate for signal hysteresis, noise (due to energy delivery etc) directional bias or other error. They also provide the benefit of simultaneous sampling and comparison of two or more tissue volumes to perform tissue identifications. In an embodiment shown inFIG. 8a, an emittingmember22meis positioned at the center oftissue volume5svwith detecting members orsensor22mdpositioned in a surrounding relationship so light passes from the center of the sample volume to the outlying sensors. In another embodiment shown inFIG. 8b, a detectingmember22mdis positioned at the center oftissue volume5svwith emittingmembers22meorsensors22 positioned in a surrounding relationship so as to transmit light inward. In yet another related embodiment shown inFIG. 8c,emitters22meanddetectors22mdcan be located in alinear arrangements22′ that are substantially perpendicular or have anotherselectable angle22″. Alternatively as shownFIG. 8d,emitters22mecan comprise afirst array22a1 (such as perpendicular array) and thedetector22mdlocated on aseparate array22a2.First array22a1 can be rotated to obtain different optical paths todetector array22a2 so as to sample different tissue volumes and/or provide multiple samplings of the same volume (via different optical paths) to improve accuracy and signal to noise ratios.
• In another embodiment shown inFIG. 9, one ormore sensor members22mcan be advanced fromenergy delivery member18eso as to be positioned aselectable distance45 distal to thedistal end18deofenergy delivery member18e(which corresponds to thedeployment distance43 ofenergy delivery member18.).Distance45 onto or even beyond the point thatmember22mis positioned outside of theablation volume5sv.Distance45 can be a greaterlongitudinal distance45′ or alateral distance45″ with respect to a longitudinal axis12a1 ofintroducer12. This can also be achieved by the embodiment shown inFIG. 8dutilizing two ormore arrays22a, with at least one array positioned outside of the ablation volume.
• Referring back toFIG. 4, emittingmember22mecan include an integrallight source17 such as an LED or a diode laser or alternatively can be optically coupled to an externallight source17 which in various embodiments, can be configured to emit light at multiple wavelengths and over a range of wavelengths including, but limited to the range of 300 to 850 nm, a more preferred range of 450 to 850 nm with specific embodiments in the UV and infrared ranges. In anembodiment light source17 can be a monochrometer known in the art. Examples of monchrometers include single crystal, double crystal and surface normal reflection monchrometers as well as models manufactured by Macken Instruments Inc. (Santa Rosa, Calif.). In other embodiments,light source17 can be a white light source, a xenon bulb, an LED or a coherent light source such as a laser configured to emitprobe beam22ib. Examples of lasers include, but are not limited to, YAG lasers, Nd:YAG lasers, CO2 lasers, infrared lasers, argon lasers, tunable dye lasers and copper vapor lasers. Referring now toFIG. 10,laser device17 can include multiple beams at different wavelengths including a first22ib′ and asecond beam22ib″ having a first andsecond wavelength7′ and7″ wavelength. Examples of multiple wavelength emitting lasers include CO₂lasers and argon-pumped tunable dye lasers. The use of multiple and/or a broad spectrum ofwavelengths7 provides the benefit of increased tissue or tissue chromophore specificity and hence increased predictive power (e.g. statistical confidence) of associated tissue identification algorithms described herein. The use oflaser light source17 with multiple beams and wavelengths can also be configured to determine the deployment distance of one ormore members18,18eusing laser range finding methods known in the art.
• Referring back toFIG. 4, in anembodiment detecting member22mdcan be coupled to anoptical measurement device19 such as a spectrophotometer, reflectometry device or CDC device. For ease of discussion, optical measurement device will now be referred to as a spectrophotometer, but all other embodiments are equally applicable.Spectrophotometer device19 is configured to detect and record spectral information including a tissue spectra orspectral profile19sresulting from optically induced tissue interactions such as reflectance, transmittance and scatter resulting from the incident light22ifromemitter22meon tissue withinsample volume5sv.
• In an embodiment,spectrophotometer device19 can includelogic resources19lrsuch as a microprocessor andmemory resources19lrsuch as RAM or DRAM chip configured to analyze, store and display tissuespectral profile19sand/or other optical information derived from sensingmember22mand/orsensing array22a.Spectrophotometer device19 can also be coupled to adisplay device21 so as to display real time or stored spectra, images and other data generated byspectrophotometer device19. Examples ofdisplay devices22 include cathode ray tubes (CRTs), liquid crystal displays, plasma displays, flat panel displays and the like.Display device22 can also be incorporated in anexternal computer24 coupled tospectrophotometer device19.
• Referring now toFIG. 11, in various embodimentslight source17 can also include a wavelength7fconfigured to cause fluorescence of an optical marker compound or molecule9 either naturally occurring or coupled to a tumor specific binding agent9basuch as an antibody, protein or liposome known in the art. Antibody9bais configured to attach to a tumorspecific antigen9a. Binding agent9bacan also be configure to be controllably release marker9 when a specific tissue condition is met such as temperature, release of intracellular fluids/contents or other indications of cell lysis from ablative treatment. Binding agent9bacan include a plurality of binding agents9baincluding a first and a second binding agents9ba1,9ba2 configured to be released a first and a second marker9′ and9″ upon a first tissue condition and a second tissue condition. An example of binding agent that is configured to controllably release a marker includes a liposome. Suitable liposomes include those manufactured by Liposome Technology Inc. (Menlo Park, Calif.). In various embodiments binding agents9ba,9ba1 or9ba2 can be configured to release marker9 in a temperature range from about 40° C. to about 60° C.; and more preferably in the range from about 45° C. to about 55° C. Marker9 can also be configured to enhance the delivery of energy totumor5″ and or increase the necrotic effect of energy on the tumor mass. An example of an energy delivery enhancing marker is an ferro-colloid compound.
• In an embodiment, marker9 and binding agent9bacan be mixed in asolution27 that is fluidically coupled to introducer12 (via a reservoir or fluid delivery device described herein) and delivered totissue site5′ throughlumen13 ofintroducer12 or throughlumen72 ofmember18.
• In related embodiments, markers9 can be configured to degrade upon a given tissue condition such that a decrease in the concentration of marker9 serves as an indicator of that tissue condition, temperature being one example. In various embodiments, marker9 can be configured to degrade or under a change in state or phase (e.g. solidify, liquefy or vaporize) upon a number of conditions or tissue treatments including: temperature or thermal irradiation, electrical current such as an RF current, ultrasound irradiation, UV radiation, ionizing irradiation and the like. These and related embodiments can be configured to be used in conjunction with an analytical method known in the art such as fluorescence spectroscopy described herein.
• Invarious embodiments apparatus10 andarray22aincludingmembers22mcan be configured to perform tissue identification, differentiation, ablation monitoring and mapping of tissue masses and structures. In specific embodiments,apparatus10 is configured to perform a tissue biopsy function using optical or other information derived fromarray22aSuch information is obtained by probing thetarget tissue volume5svwith anincident beam22ibhaving one ormore wavelengths7. As described herein, the optical tissue interactions ofincident beam22ibontarget tissue site5′ result in a distinctspectral profile19sthat serves as a fingerprint of the tissue type. As shown inFIG. 5 the main optical tissue interactions include scatter, reflection and absorption and to a lesser extent fluorescence. Referring back toFIG. 4, these optical tissue interactions are controlled to a large extent bychromophores33 that result in one ormore peaks33pwithinprofile19s.Chromophores33 can includemetabolic chromophores33 that are individually or collectively predictive of a particular tissue type including cancerous tissue. By analyzing and matchingpeaks33pcorresponding to one or more of thesechromophores33,spectral profile19shas predictive value for tissue type and/or a tissue condition such as necrosis or thermal injury. Further, many tissue types will have asignature profile19sthat can be readily identified and matched to a database of profiles using pattern recognition techniques or algorithms known in the art including fuzzy logic methods. Accordingly,apparatus10 includingsensor array22acan be configured to generate and analyze a compositespectral profile19sincluding reflectance, absorption and fluorescence components depending on the tissue type and associated chromophores of interest. Alternatively,apparatus10can sensor array22acan be configured to generate and analyze individualspectral profiles19sfor a particular optical property, again depending on the chromophores of interest.
• Referring still toFIG. 4, in various embodiments,apparatus10 can include electronic algorithms orsoftware modules19mresident inlogic resources19lrofdevice19 or microprocessor339 that are configured to analyzeprofile19sand perform tissue identification and/or tissue differentiation between one or more sampledvolumes5sv.Modules19mcan include pattern recognition algorithms or fuzzy logic. Also in an embodiment,modules19mcan be configured to compareprofile19sto a database ofprofiles19dbstored inmemory resources19mruse curve fitting or other numerical methods known in the art to provide and display a correlation coefficient or statistic indicative of the probability of a match to a particular tissue type.
• Referring now toFIG. 12, invarious embodiments apparatus10 can also be configured to differentiate cancerous or other abnormal tissue vs. healthy tissue based on metabolic abnormalities of cancerous tissue. Accordingly in various embodiment,apparatus10 andarrays22acan also be configured to detect and/or quantifyspecific chromophores33 includingmetabolic chromophores33, also calledmetabolites33 that are predictive or otherwise indicative of cancerous tissue, precancerous tissue, abnormal tissue, necrosed tissue or injured tissue. In an embodiment,apparatus10 can be configured to detect and/or quantify a plurality ofmetabolites33pthat can include a first, second, third and fourth metabolite,33a,33b,33c, and33d. Software module19acan compare detected metabolite concentrations for one or mores of these metabolites to a database of19dpof metabolite concentrations for known cancer types and use curve fitting, fuzzy logic or other numerical methods to establish a match along with an associated confidence metric such as a p-value. In an alternative embodiment,apparatus10 including module19acan be configured to utilize relative differences in concentrations ofmetabolites33 by detecting and measuring concentrations of metabolites in afirst sample volume5sv1 containing healthy tissue can compare those to measurements forcancer metabolites33′ of asecond sample volume5sv2 believed to be a tumor orcancerous tissue volume5″.Module19mcan calculate the differences and compare one or more of them to adatabase19dbof differences for known cancer types and use curve fitting, fuzzy logic other numerical methods to establish a match along with an associated confidence metric.
• In a related embodiment,emitter22mecan also be configured to emit areference beam22refat areference wavelength7rthat does not appreciably interact with thetarget chromophore33 so as to compensate for tissue hysteresis. In another relatedembodiment spectrophotometry device19 can be a dual beam spectrophotometer in which areference beam22refis also used to compensate for any hysteresis in thelight source17.
• In various embodiments,predictive metabolites33 include, but are not limited to, oxyhemoglobin, deoxyhemoglobin DNA and DNA fragments, tissue oxygen or PO₂, lipids, glucose, acids, CO₂, sodium, potassium, calcium and intracellular fluid and the like. This can be achieved by probing the tissue with wavelengths of incident light22ibknown to be absorbed or cause fluorescence of these chromophores. Oxyhemoglobin has strong absorption bands in the visible spectrum with the strongest absorption peak of occurring at 418 nm. Two additional absorption peaks with lower absorption coefficients occur at 542 and 577 nm. Glucose is known to absorb in the near infrared range. Two other cancerpredictive chromophores33′ include NAD(P)H, and flavins that fluoresce in the ultra-violet and near ultra-violet range.
• Differences in the concentration ofmetabolites33 for healthy tissue verses metabolites forcancerous tissue33′ result from the metabolic differences of cancerous tissue. A discussion will now be presented of those differences. Since many cancer or tumors are over vascularized relative to normal tissue a higher total amount of oxyhemoglobin in a given sample volume of tissue can indicate cancer. At the same time, since cancer cells are more rapidly dividing and have higher metabolic rate than normal tissue the tumor will typically be slightly hypoxic and thus have lower PO₂levels and or oxyhemoglobin concentrations (or higher deoxyghemoglobin concentrations) relative to normal tissue. Also, owing to higher metabolic rates, tumors will frequently have lower interstitial glucose concentrations and higher PCO₂levels as well as lower pH whichsensor array22acan be configured to detect. Further, as described herein, tumors will have different (usually higher) rates of DNA synthesis as well as abnormal DNA one or both of which can be detected bysensor array22ausing DNA probe methods.
• In one embodiment of an optical biopsy method, fluorescence spectroscopy can be employed for optical biopsy including tissue identification and ablation monitoring. In this method, thewavelength7 of theincident beam22ibis altered by interaction with the target tissue resulting in an emitted or returning light22rbat a different wavelength known as the emitted wavelength7e. Sampling and analysis of the emitted light bydetection member22mdand coupled spectrometer device17 (which in this embodiment is a UV spectrometer) results in the generation of afluorescence emission spectrum19s. This is a plot of the intensity of emitted fluorescent light as a function of emission wavelength produced when the target tissue is illuminated at a particular wavelength7f.Spectra19sis then compared matched to and todatabase19dbof UV spectra for known cancer types or cancerpredictive metabolites33′.
• Inother embodiments apparatus10 andsensor array22acan be configured to detect and quantify metabolic chromophores ormetabolites33cnindicative of cell necrosis, injury or ablation. These metabolites result from various cellular functions occurring during cell necrosis. More specifically, when cells are heated by ablation treatment such as RF energy they heat to the point where their proteins are denatured, cell walls rupture and their contents released which includes a number ofnecrotic indicating metabolites33cn. Suchnecrotic indicating metabolites33cncan include but are not limited to collagen, denatured collagen, fatty acids, lipids, cell membrane lipids, billirubin, and vapor bubbles and carbonized tissue. In a related embodiment,sensor array22acan also be configured to monitor for decreases inmetabolic chromophores33 resulting from thermal or other ablative treatment. For example, decreases in hemoglobin due its thermal breakdown result in a tissue color e.g. from red to white which can be readily detected bysensor array22afor portions or an entiretarget tissue site5′. Besides hemoglobin, other decreasingchromophore33 concentrations that can be monitored as indicators for cell necrosis include myoglobin, collagen and melanin.
• In alternative embodiments,sensor array22aincludingmembers22m,22meand22mdcan be configured to detect and distinguish betweennormal cells6 andabnormal cells6′ including abnormal cell shapes, sizes and morphology as a means of identifying cancerous, precancerous or other abnormal tissue. This can be accomplished using a variety of optical cell sorting and optical particle sizing techniques known in the art including fluorescence tagging methods.Cancer cells6′ will frequently be drastically different from anormal cell6 including being larger, having a larger more dense nucleus and being irregularly shaped.Array22acan be configured to detect one or more of these abnormalities and input them tologic resources19. Theremodules19mcan be configured to compare these abnormalities to adatabase19dbof known abnormalities and make a tissue identification based on pattern recognition or fuzzy logic algorithms which can be similar to those used for finger print identification.
• Invarious embodiments apparatus10 andsensor array22acan be configured to optically probetissue site5′ and generate an image or map of the tumor volume and other structures within thetarget tissue site5′. In an embodiment shown inFIG. 13,apparatus10 and sensor array20aare configured to probe/scan thetissue volume5″ simultaneously in3 dimensions (e.g. volumetrically sample) to determine theborder5″boftumor mass5″ so as to locate and map thetumor mass5″ in 3 dimensions. The process can be facilitated by having one or moreknown reference points5ronmembers18 that are determined via apositional sensor22pondeployment device24″ that is configured to determinedeployment distance43 of a selectedmember18e. (reference point5rcan also be aradiopaque marker11 positioned at set distance alongmember18e). The mapping process can also be facilitated by rotatingarray22aabout introducer axis12a1 or advancing and retracting one ormore sensing members22mfrommembers18 or a combination of both. Signals22ifromsensor array22aas well those fromposition sensor22pcan then be input tologic resources19lrwheremodule19mgenerates a 3dimensional map4″ of the tumor volume using one or more image processing algorithms known in the art including, but not limited to, edge detection (to definetumor boundary5″B), filtering, volume imaging, contrast enhancement and fuzzy image processing algorithms and the like.Module19mcan then be configured to displaymap4″ on a coupled display device21 (using volume image display algorithms such as numeric projection). The generation of3D map4″ allows the user to accurately positionenergy delivery members18ewithintumor mass5″ while establishing the position of and avoiding nearby criticalanatomical structures5cs. Further, the volumetric sampling and 3D mapping capability of embodiments of the invention solves the shortcomings of 2D intra-operative imaging methods including poor resolution of the tumor mass, difficulty in visualization of the tumor volume including misjudgment of the size, shape and location of the tumor volume. Inrelated embodiments detectors22mecan be configured to monitor in the near infrared range to produce an infrared/thermal image4irofsample volume5svthat can includetumor mass5″ orablation volume5av.
• In addition to identifying tissue types,apparatus10 andsensor arrays22acan also be employed to monitor the progression of an ablative procedure including the progression of anablation volume5avresulting from the delivery of energy to targettissue volume5. Referring now toFIGS. 14aand14b,emitters22aanddetectors22mdcan be configured to monitor the moving boundary layer ofcell necrosis55 and/orthermal fronts55tof a developingablation volume5av. This can be achieved by monitoring for the presence ofmetabolic chomophores33 or markers9 indicative of cell necrosis or ablation described herein. Thespectral signal intensity19s(at one or more wave lengths7) for a volume of tissue between one ormore emitters22meanddetector22mdcan be monitored over time. An endpoint for ablation can be determined based on either aselectable threshold value19tsofsignal19sor an inflection point or change inslope19ds(e.g. a derivative) ofcurve19sor a combination of both. In anembodiment signal19scan comprise the subtraction of a baseline (or reference)spectral measurement19sb1 of a nearby, but non-ablated tissue volume, from areal time measurement19srtof the target tissue volume during the time course of ablation. This compensates for any signal or tissue hysteresis over time. Signal/curve19scan include both spectral, thermal and impedance measurements. Values for19tsand19scan be input and stored inlogic resource19lrcoupled tospectrophotometer19 or incorporated into an electronic algorithm controlling the delivery of energy which can be stored in a controller orprocessor338 coupled topower supply20.
• In related embodiments,sensor array22acan be configured to monitor for any number of indicators of cell necrosis that can be utilized to qualitatively or quantitatively assess the progress of an ablation and determine a meaningful clinical endpoint. Such indicators and associated monitoring and endpoint methods include, but are not limited to, the following: monitoring interstitial moisture or hydration levels (these would expect to go as cell lyse and then go down as fluid is boiled or evaporated) and utilizing a decrease below a lower threshold as an endpoint; monitoring interstitial electrolyte concentrations (which increase with cell lysis); monitoring for interstitial fatty acid and amino acid concentrations (which would increase with cell lysis and then decrease due thermal degradation); monitoring for the increase or decrease of marker compounds9; monitoring impedance; monitoring tissue temperature changes using near-infrared or thermocouple measurements; monitoring tissue color changes (e.g. red to white), monitoring for protein or collagen denaturization; monitoring for the release of DNA, gene fragments, DNA fragments or degraded DNA; monitoring for the release of RNA, RNA fragments or RNA fragments; monitoring for changes in tissue oxygenation in the form of PO₂or oxyhemoglobin; monitoring for changes in PCO₂; monitoring for decrease or cessation of blood flow rates (an indication of tissue coagulation) using optical (e.g. laser Doppler) or acoustical (e.g. doppler ultrasound) sensors and monitoring for the presence of vapor bubbles and rate of vapor bubble formation. In a specific embodiment, sensor array is configured to monitor the rate of vapor bubble formation (using either optical and/or acoustic/ultrasound sensors22) and as an indicator of both rate of ablation and also a treatment endpoint. A treatment control and endpoint algorithm in module19aemploying this method would initially look for an increase in bubble rate formation and then a decrease below a set threshold as the endpoint. Other related embodiments can be configured to monitor for various cellular functions indicative of injury or necrosis.
• Thetarget tissue site5″ can also be probed and interrogated bysensor array22aafter the completion of ablation to confirm that ablation is complete for the entire desired volume ablation volume. By probing the ablated region withsensor array22, the 3 dimensional volume of the ablation can be assessed and themargin5mof ablated healthy tissue beyond thetumor mass5″ can also be measured.
• Referring now toFIG. 15, in anembodiment power supply20,display device21,controller329 and/orlight source17 and/oroptical device19 can be incorporated or integrated into a single control and display device orunit20cd.Device20cscan configured to include display one or more of the following:spectral profile19s,tissue site image4′,tumor volume image4″,ablation volume image4av, time temperature profiles, tissue identification information, and ablation setting information (e.g. power setting, delivery time etc.).Device20cdcan also be configured to superimposeablation volume image4avontotumor volume image4″ ortissue site image4′ as well as superimposevisual cues4con the placement (including proper and improper placement) ofapparatus10 includingenergy delivery devices18ewithin thetumor volume5″ ortissue site5″.Device20cdcan also include controls knobs20ckfor manipulating any of the images (4′,4″ or4av) in one or more axis.
• Referring now toFIGS. 16a-16c, in an embodiment of a method of theinvention sensor array22acan be utilized to ensure proper placement ofenergy delivery member18eto achieve the desiredablation volume5avas well as detect various improper placements. Referring toFIG. 16a, asenergy delivery members18eare advanced out ofintroducer12sensors22 positioned atdistal tip18deorsensor members22/array22acan be utilized to locate and maptumor mass5″, sense the position ofenergy delivery members18erelative to the tumor mass and determine anablation volume5avbased on the current position ofmembers18e. As shown inFIG. 16a,sensors22 ormembers22 can be used to determine and alert the user when one or more energy delivery members are positioned outside oftumor mass5″ and/or when the resultingablation volume5avwould not encompass theentire tumor mass5″.Device20cdor other coupled monitoring device can then be configured to alert the use of the necessity of repositioning one or moreenergy delivery members18eproviding visual cues as to which member to move and by how much distance. Referring now toFIG. 16b, asmembers18econtinue to be advanced into the tumorvolume mass sensors22 ormembers22 can also determine ifmembers18enot positioned properly to produce anablation volume5avthat has an adequatehealthy tissue margin5mwith respect totumor mass5″. Again, the user could be alerted of the need to reposition one ormore member18e. Referring nowFIG. 16c, asmembers18econtinue to beadvanced sensors22 ormember22 can be configured to determine whenmembers18 are properly positioned to produce the desiredablation volume5av, the user being subsequently alerted bydevice20cd.
• Referring now toFIGS. 17aand17b, in other method embodiments of theinvention sensors20 orsensor array22acan be utilized to detect incomplete ablation volumes. In the embodiment shown inFIG. 17a, one ormore members18ewith coupledsensors22 orsensor members22mcan be rotated about theintroducer axis12 to move thearray members22mfrom afirst array position22a′ defining afirst sample volume5sv1 to asecond array position22a″ defining asecond sample volume5sv2 so as to detect areas of incomplete ablation that are outside of the plane defined by two or moreenergy delivery members18e. By rotatingintroducer12 ormembers18,array22acan be rotated about axis12a1 in any desired amount from 1 to 360° to sample any desired tissue volume and ascertain that theentire tumor volume5″ has been ablated along with the desire amount ofhealthy tissue margin5m. In another embodiment shown inFIG. 17b, incomplete ablation can be determined by advancingsensor members22morpassive members18 with coupledsensors22 outside of the immediate area orvolume5evdefined byenergy delivery members18eand interrogating a desired tissue volume withsensors22 ormember22mto determine if it has been sufficiently ablated. This procedure can be repeated withsensor members22mormember18 being further advanced with subsequent tissue interrogations untilsensors members22morsensors22 are positioned at theborder5av′ of the desiredablation volume5avand a determination has been made that all sampled tissue has been adequately ablated.
• Turning now to a further discussion ofintroducer12, in various embodiments,introducer12 can be a trocar, catheter, multi-lumen catheter, or a wire-reinforced or metal-braided polymer shaft, a port device, a subcutaneous port device or other medical introducing device known to those skilled in the art. In various embodiments,introducer12 as well asresilient member18 can be configured to have varying mechanical properties along their respective lengths including, but not limited to variable stiffness, torquability, bendability, flexural modulus, pushability, trackability and other mechanical performance parameters known in the catheter arts. Referring toFIG. 18a, this can be achieved through the use ofstiff shafts sections12′″ disposed within portions ofintroducer12 along itslength12″. It can also be accomplished through the use of braids, varying/tapered diameters and different materials (e.g. stiffer materials joined to flexible materials) positioned over portions ofintroducer12.Sections12′″ made from different materials can be joined using introducer bonding methods known in the art such as hot melt junctions (with and without capture tubes/collates), adhesive joints, but joints and the like. The joining method can be controlled/selected so as to control themechanical transition12mtbetween two sections to a desired gradient (e.g. smooth vs. abrupt). In related embodiments,introducer12 and/ormember18 can be configured to have stiffer proximal portions and more flexible distal portions so as to facilitate one or more of the following (i) introducer steerability and positioning ofdistal tip16 at a selectabletarget tissue site5′, (ii) reduced risk of perforation, abrasion and other trauma during the positioning the introducer to the tissue site. In various embodiments, the transition from the stiffer to the more flexible portion can be configured to be either (i) gradual with a linear or curve-linear transition, (ii) a step or abrupt transition, and (iii) combinations thereof.
• Referring toFIGS. 18band18c,introducer12 can have a substantially circular, semicircular, oval or crescent shaped crosssectional profile12cs, as well as combinations thereof along its length. Similarly,lumens13 can have a circular, semicircular, oval or crescent shaped cross section for all or a portion of the12′ length ofintroducer12.
• Suitable materials forintroducer12 andresilient member18 include, but are not limited to, stainless steel, shape memory alloys such as nickel titanium alloys, polyesters, polyethylenes, polyurethanes, Pebax®, polyimides, nylons, copolymers thereof and other medical plastics known to those skilled in the art. All or portions ofintroducer12 can be coated with a lubricious coating orfilm12′ which reduces the friction (and hence trauma) ofintroducer12 with hepatic, pulmonary, bone and other tissue. Such coatings can include but are not limited to silicones, PTFE (including Teflon®) and other coatings known in the art. In arelated embodiment introducer12 andmember18 can have anoptical coating37 on their exterior surface or withinlumens13 or72 that is configured to reduce reflection or glare from their respective surfaces that may cause false optical signals or otherwise interfere with the optical sampling process by sensingmembers22.Optical coating37 can be any non-reflective, glare resistant coating known in the art or can be a surface treatment such as anodization.
• Also, all or portions ofapparatus10 includingintroducer12 andmembers18 can be constructed of materials known in the art that are optimized and/or compatible with radiation sterilizations (e.g. Gamma or E-beam). In related embodiments, all or portions ofapparatus10 can be configured (e.g. lumen diameter to length ratio, etc) to be sterilized by plasma (e.g. H₂O₂) sterilization by systems.
• Referring now toFIG. 20, in other embodiments all or portions ofintroducer12 orresilient members18 can be configured to be deflectable and/or steerable usingdeflection mechanisms25 which can include pullwires15, ratchets, cams, latch and lock mechanisms, piezoelectric materials and other deflection means known in the art. The amount of deflection ofintroducer12 is selectable and can be configured to allow the maneuvering ofintroducer12 through tortuous vasculator and other anatomy. In specific embodiments, the distal portions ofintroducer12 can be configured to deflect 0-180° or more in up to three axes to allow the tip ofintroducer12 to have retrograde positioning capability.Deflection mechanism25 can be coupled to or integral with a moveable orslidable actuator24″,25′ onhandpiece24.Mechanism25 and coupledactuator25′ are configured to allow the physician to selectively control the amount ofdeflection25 ofdistal tip16 or other portion ofintroducer12.Actuator25′ can be configured to both rotate and deflectdistal tip16 by a combination of rotation and longitudinal movement of the actuator.
• Referring now toFIGS. 20, in various embodiments introducer12 can be coupled at itsproximal end14 to ahandle24 orhandpiece24.Handpiece24 can be detachable and can includeports24′ andactuators24″.Ports24′ can be coupled to one or more lumens13 (and in turn lumens72) and can include fluid and gas ports/connectors and electrical, optical connectors. In various embodiments,ports24′ can be configured for aspiration (including the aspiration of tissue), and the delivery of cooling, electrolytic, irrigation, polymer and other fluids (both liquid and gas) described herein.Ports24′ can include but are not limited to luer fittings, valves (one-way, two-way), toughy-bourst connectors, swage fittings and other adaptors and medical fittings known in the art.Ports24′ can also include lemo-connectors, computer connectors (serial, parallel, DIN, etc) micro connectors and other electrical varieties well known to those skilled in the art. Further,ports24′ can include opto-electronic connections which allow optical and electronic coupling of optical fibers and/or viewing scopes to illuminating sources, eye pieces, video monitors and the like.Actuators24″ can include rocker switches, pivot bars, buttons, knobs, ratchets, levers, slides and other mechanical actuators known in the art, all or portion of which can be indexed. These actuators can be configured to be mechanically, electro-mechanically, or optically coupled to pull wires, deflection mechanisms and the like allowing selective control and steering ofintroducer12.Handpiece24 can be coupled to tissue aspiration/collection devices26, fluid delivery devices28 (e.g. infusion pumps) fluid reservoirs (cooling, electrolytic, irrigation etc)30 orpower source20 through the use ofports24′. Tissue aspiration/collection devices26 can include syringes, vacuum sources coupled to a filter or collection chamber/bag.Fluid delivery device28 can include medical infusion pumps, Harvard pumps, syringes and the like. In specific embodiments,aspiration device26 can be configured for performing thoracentesis which is a procedure for removing pleural fluid percutaneously.
• Turning now to a discussion ofresilient members18, these members can be of different sizes, shapes and configurations with various mechanical properties selected for the particular tissue site. In one embodiment,members18 can be needles, with sizes in the range of 28 to 12 gauge with specific embodiments of 14, 16 and 18 gauges.Resilient members18 are configured to be in non-deployed positions while retained inintroducer12. In the non-deployed positions,resilient members18 may be in a compacted state, spring loaded, generally confined or substantially straight if made of a suitable memory metal such as nitinol. Asresilient members18 are advanced out ofintroducer12 they become distended to a deployed state, which collectively defines anablative volume5av, from which tissue is ablated as illustrated more fully inFIGS. 1, 2,19 and16a-16c. The selectable deployment ofresilient members18 can be achieved through one or more of the following approaches (i) the amount of advancement ofresilient members18 fromintroducer12; (ii) independent advancement ofresilient members18 fromintroducer12; (iii) the lengths and/or sizes of energy delivery surfaces ofelectrodes18 and18′; (iv) variation in materials used forelectrode18; and (v) variation of the geometric configuration ofelectrode18 in their deployed states.
• As described herein, in various embodiments all or a portion ofresilient member18 can be an energy delivery device ormember18e. Turning to a discussion of energy delivery device and power sources, the specific energy delivery devices18eand power sources20 that can be employed in one or more embodiments of the invention include but are not limited to, the following: (i) a microwave power source coupled to a microwave antenna providing microwave energy in the frequency range from about 915 MHz to about 2.45 GHz (ii) a radio-frequency (RF) power source coupled to an RF electrode, (iii) a coherent light source coupled to an optical fiber or light pipe, (iv) an incoherent light source coupled to an optical fiber, (v) a heated fluid coupled to a catheter with a closed or at least partially open lumen configured to receive the heated fluid, (vi) a cooled fluid coupled to a catheter with a closed or at least partially open lumen configured to receive the cooled fluid (viii) a cryogenic fluid, (ix) a resistive heating source coupled to a conductive wire, (x) an ultrasound power source coupled to an ultrasound emitter, wherein the ultrasound power source produces ultrasound energy in the range of about 300 KHZ to about 3 GHz, (xi) and combinations thereof For ease of discussion for the remainder of this application, the energy delivery device18eis one or more RF electrodes18eand the power source utilized is an RF power supply. For these and related embodiments,RF power20 supply can be configured to deliver 5 to 200 watts, preferably 5 to 100, and still more preferably 5 to 50 watts of electromagnetic energy is to the electrodes ofenergy delivery device18 without impeding out. Theelectrodes18eare electromagnetically coupled toenergy source20. The coupling can be direct fromenergy source20 to eachelectrode18erespectively, or indirect by using a collet, sleeve and the like which couples one or more electrodes toenergy source20.
• In various embodiments,electrodes18ecan have a variety of shapes and geometries. Referring now toFIGS. 21a-21f, example shapes and geometries can include, but are not limited to, ring-like, ball hemispherical, cylindrical, conical, needle-like and combinations thereof.
• Referring toFIG. 22, in anembodiment electrode18ecan be a needle with sufficient sharpness to penetrate tissue including fibrous tissue including, encapsulated tumors cartilage and bone. Thedistal end18deofelectrode18ecan have acut angle68 that ranges from 1 to 60°, with preferred ranges of at least 25° or, at least 30° and specific embodiment of 25° and 30°. The surface ofelectrode18ecan be smooth or textured and concave or convex.Electrode18ecan havedifferent lengths38 that are advanced fromdistal end16′ ofintroducer12. The lengths can be determined by the actual physical length of electrode(s)18e, thelength38′ of anenergy delivery surface18edsofelectrode18eand the length,38″ ofelectrode18ethat is covered by aninsulator36.Suitable lengths38 include but are not limited to a range from 1-30 cms with specific embodiments of 0.5, 1, 3, 5, 10, 15 and 25.0 cm. Theconductive surface area18edsofelectrode18ecan range from 0.05 mm2 to 100 cm2. The actual lengths ofelectrode18edepend on the location oftissue site5′ to be ablated, its distance from the site, its accessibility as well as whether or not the physician performs an endoscopic or surgical procedure. While theconductive surface area18edsdepends on the desiredablation volume5avto be created.
• Referring now toFIGS. 23 and 24,electrode18ecan also be configured to be flexible and or deflectable having one or more radii ofcurvature70 which can exceed 180° of curvature. In use,electrode18ecan be positioned to heat, necrose or ablate any selectedtarget tissue volume5′. Aradiopaque marker11 can be coated onelectrodes18efor visualization purposes.Electrode18ecan be coupled tointroducer12 and or an advancement member ordevice15 or and advancement-retraction member34 using soldering, brazing, welding, crimping, adhesive bonding and other joining methods known in the medical device arts. Also,electrode18ecan include one or more coupledsensors22 to measure temperature and impedance (both of the electrode and surrounding tissue), voltage and current other physical properties of the electrode and adjacent tissue.Sensors22 can be at exterior surfaces ofelectrodes18eat their distal ends or intermediate sections.
• Electrode18ecan be made of a variety of conductive materials, both metallic and non-metallic. Suitable materials forelectrode18einclude, steel such as 304 stainless steel of hypodermic quality, platinum, gold, silver and alloys and combinations thereof. Also,electrode18ecan be made of conductive solid or hollow straight wires of various shapes such as round, flat, triangular, rectangular, hexagonal, elliptical and the like. In a specific embodiment all or portions ofelectrodes18eor asecond electrode18e′ can be made of a shaped memory metal, such as NiTi, commercially available from Raychem Corporation, Menlo Park Calif.
• Referring now toFIGS. 25 through 28 in various embodiments one ormore electrodes18ecan be covered by aninsulative layer36 so as to have an exterior surface that is wholly or partially insulated and provide a non-insulated area which is anenergy delivery surface18eds. In an embodiment shown inFIG. 25,insulative layer36 can comprise a sleeve that can be fixed or slidably positioned along the length ofelectrode18eto vary and control thelength36′ of energy delivery surface18eds. Suitable material forinsulative layer36 include polyimide and flouro-carbon polymers such as TEFLON.
• In the embodiment shown inFIG. 26,insulation36 is formed at the exterior ofelectrodes18ein circumferential patterns, leaving a plurality of energy delivery surfaces18eds. In an embodiment shown inFIGS. 27 and 28,insulation36 extends along a longitudinal exterior surface ofelectrodes18e.Insulation36 can extend along a selected distance along a longitudinal length ofelectrodes18eand around a selectable portion of a circumference ofelectrodes18e. In various embodiments, sections ofelectrodes18ecan haveinsulation36 along selected longitudinal lengths ofelectrodes18eas well as completely surround one or more circumferential sections ofelectrodes18e.Insulation36 positioned at the exterior ofelectrodes18ecan be varied to define any desired shape, size and geometry ofenergy delivery surface18eds
• Referring now toFIG. 29, in various embodiments electrode18ecan include one or more lumens72 (which can be contiguous with or the same as lumen13) coupled to a plurality of fluid distribution ports23 (which can be apertures23) from which a variety offluids27 can be introduced, including conductivity enhancing fluids, electrolytic solutions, saline solutions, cooling fluids, cryogenic fluids, gases, chemotherapeutic agents, medicaments, gene therapy agents, photo-therapeutic agents, contrast agents, infusion media and combinations thereof This is accomplished by having ports orapertures23 that are fluidically coupled to one ormore lumens72 coupled tolumens13 in turn coupled tofluid reservoir30 and/orfluid delivery device28.
• In an embodiment shown inFIG. 29, aconductivity enhancing solution27 can be infused intotarget tissue site5′ includingtissue mass5″. The conductivity enhancing solution can be infused before during or after the delivery of energy to the tissue site by the energy delivery device. The infusion of aconductivity enhancing solution27 into thetarget tissue5′ creates an infused tissue area5ithat has an increased electrical conductivity (verses un-infused tissue) so as to act as anenhanced electrode40. During RF energy delivery, the current densities inenhanced electrode40 are greatly lowered allowing the delivery of greater amounts of RF power intoelectrode40 andtarget tissue5′ without impedance failures. In use, the infusion of the target tissue site with conductivity enhancing solution provides two important benefits: (i) faster ablation times; and (ii) the creation of larger lesions; both without impedance-related shut downs of the RF power supply. This is due to the fact that the conductivity enhancing solution reduces current densities and prevents desiccation of tissue adjacent the electrode that would otherwise result in increases in tissue impedance. A preferred example of a conductivity enhancing solution is a hypertonic saline solution. Other examples include halide salt solutions, and colloidal-ferro solutions and colloidal-silver solutions. The conductivity of enhancedelectrode40 can be increased by control of the rate and amount of infusion and the use of solutions with greater concentrations of electrolytes (e.g. saline) and hence greater conductivity. In various embodiments, the use ofconductivity enhancing solution27 allows the delivery of up to 2000 watts of power into the tissue site impedance shut down, with specific embodiments of 50, 100, 150, 250, 500, 1000 and 1500 watts achieved by varying the flow, amount and concentration ofinfusion solution27. The infusion ofsolution27 can be continuous, pulsed or combinations thereof and can be controlled by a feedback control system described herein. In a specific embodiment, a bolus ofinfusion solution27 is delivered prior to energy delivery followed by a continuous delivery initiated before or during energy delivery withenergy delivery device18eor other means.
• Turning to a discussion of sensors, the use of one ormore sensors22 coupled to the introducer, energy delivery devices, deployable member and biopsy needles and permits accurate measurement of temperature attissue site5′ in order to determine, (i) the extent of cell necrosis, (ii) the amount of cell necrosis, (iii) whether or not further cell necrosis is needed and (iv) the boundary or periphery of the ablated tissue mass. Further,sensor22 reduces non-targeted tissue from being injured, destroyed or ablated. Referring toFIG. 24, multiple sensors can be coupled toelectrodes18.
• Sensor22 can be selected to measure temperature, tissue impedance or other tissue property described herein to permit real time monitoring of energy delivery. This reduces damage to tissue surrounding the targeted mass to be ablated. By monitoring the temperature at various points within and outside of the interior oftissue site5′, a determination of the selected tissue mass periphery can be made, as well as a determination of when cell necrosis is complete. If at anytime sensor22 determines that a desired cell necrosis temperature is exceeded, then an appropriate feedback signal is received at anenergy source20 coupled toenergy delivery device18 which then regulates the amount of electromagnetic energy delivered toelectrodes18 and18′.
• Turning now to a discussion of sensors,sensor22 can be of conventional design, including but not limited to thermal sensors, acoutiscal sensors, optical sensors, pH sensors, gas sensors, flow sensors positional sensors and pressure/force sensors. Thermal sensors can include thermistors, thermocouples, resistive wires, optical sensors and the like. A suitablethermal sensor22 includes a T type thermocouple with copper constantene, J type, E type, K type, fiber optics, resistive wires, thermocouple IR detectors, and the like. Acoustical sensors can include ultrasound sensors including piezoelectric sensors which can be configured in an array. Pressure and force sensors can include strain gauge sensors including silicon-based strain gauges. Optical sensors can include photomultipliers, optical diodes, fiber optics, and micro-machined optical fibers. Gas sensors can include O2 sensors such as Clark electrodes, CO2 sensors and other electrochemical based sensors known in the art. Flow/velocity sensors can include ultrasound sensors, electromagnetic sensors and aneometric sensors which can be configured to detect both liquid and gaseous flows. Positional sensors can include LVDT's, and Hall effect sensors. Other sensors which can be employed in various embodiments of the invention, include impedance sensors, antibody-based sensors, electrochemical biosensors, (e.g. glucose), gene chips, silicon-based gene chips, oglionucleotide-based gene chip sensors, and chemical sensors. In various embodiments, one sensor can be configured to detect multiple parameters or one or more sensors can be coupled together to deliver input on multiple parameters which can be multiplexed to an input device to a controller or microprocessor. Pressure sensors can be selected and/or configured to detect pressure differentials less than 1 mmHg and even less than 0.1 mmHg. In specific embodiments,pressure sensor22 can be a micro- machined fiber optic sensor, a PSP-1 pressure sensors made Gaymar Industries Inc., (Orchard Park, N.Y.) or a Monolithic Integrated Pressure sensor made by the Fraunhofer-Institut (Duisburg, Germany). Also, ultrasound sensor or transducers can be a Model 21362 imaging probe by the Hewlett Packard Company, Palo Alto, Calif.
• In various embodiments, analytical genetic methods including DNA probe methods and techniques can be utilized to monitor rates of DNA synthesis fortarget tissue5′ and a comparison can be made between rates of synthesis to determine cancerous versus healthy tissue. In an embodiment,sensor array22acan be configured to detect such rates of DNA synthesis andlogic resources19lrorcontrol system329 can configured with algorithms to measure and determine threshold ratios of DNA synthesis as an predictor of cancerous tissue. The ratio can vary for different types of tissue (e.g. hepatic, gastro-mucosal, prostate, mucosal, submucosal etc.) and different types of cancer. Specific DNA synthesis ratios (healthy vs. target tissue) indicative of cancer can include, but are not limited to: 1:1.1, 1:1.3, 1:1.5, 1:2. 1:3, 1:5, 1:10, 1:20, 1:50 and 1:100.
• An alternative embodiment of an in vivo tumor biopsy method utilizes a radiolabel marker compound bound to a tumor specific primary antibody that is detected by a radiation detection device (not shown) coupled to sensingmember22 and/orresilient member18 and also coupled tooptical detection device19. Given the target tissue organ, prior diagnostic imaging diagnosis the physician could select among several antibodies that are likely matches to the suspected tumor. Or alternatively, he or she could start off with an antibody to many common tumors and then utilizes ones with increasing specificity as means to narrow down the tumor type. Also, a secondary label can be used as a subtraction agent to enhance sensitivity. The radiation detection device can be configured to detect alpha, gamma, beta, positron or other radioactive particle. Preferably, the label used is positron and/or has an extremely short half life (e.g. hours). The detector device can be configured to discriminate between different energies of incident radiation, e.g., between gamma radiation in different ranges within the broad 50-500 KeV range which is normally used for gamma scintillation counters and/or between alpha, gamma and beta radiation emitted by labels on the specific and a second or different antibody. Further, the detector can be configured to distinguish between the radiation emitted by the primary antibody label and that emitted by a subtraction agent, in those cases where dual antibody correction is used to enhance sensitivity. This can be achieved by embodiments having two different detector devices or by using a single detector configured to record counts of different energies in different channels, or to distinguish by other electronic means between radiation of different types or energies. In another embodiment this can be achieved by configuring coupledoptical measurement device17 with photomultiplier and comparator circuitry that detects differences in brightness of a scintillation crystal response that correlate to differences in photon energy of incident gamma radiation. The circuit can be configured to respond only to energy levels above a selected level corresponding to the desired gamma energy band for one of the two radioisotopes.
• In an embodiment, the radiation detector can be a scintillation crystal optically mounted on the end of a fiberoptic sensing member22, that is configured to transmit the optical response of the crystal to incident gamma radiation to a photomultiplier and associated detection circuitry which comprise are integral or otherwise compriseoptical measurement device19. This configuration reduces the size of the detector to be compatible with a percutaneous introducing device, such as a catheter or trocar. The introducing device can be shielded to serve as a collimator, where necessary, and/or fitted with a window at a known distance from its terminus, with the scintillation crystal internally housed.
• In preferred embodiments, the radionuclide label used for tumor detection is an isotope with a gamma radiation emission peak in the range of 50-500 Kev. Suitable radionuclides include but are not limited to e.g., Iodine-131, Iodine-123, Iodine-126, Iodine-133, Bromine-77, Indium-111, Indium-113 m, Copper-67, Gallium-67, Gallium-68, Ruthenium-95, Ruthenium-97, Ruthenium-103, Ruthenium-105, Mercury-197, Mercury-203, Rhodium-99 m, Rhodium-101, Rhodium-105, Tellurium-121 m, Tellurium-122 m, Tellurium-125 m, Thulium-165, Thulium-167, Thulium-168, Rhenium-186, Technetium-99 m Fluorine-18. In embodiments utilizing multiple isotopes for method utilizing dual isotope correction, the two labels selected can be of sufficiently different energies to be separately detectable with the same radiation probe. Suitable such pairs of radioisotopes include, e.g., Iodine-131/Iodine 123, Gallium-67/Indium-111, Iodine-131/Technetium-99 m and the like. Preferably, the paired radionuclides used for subtraction do not both have significant scatter into the channels where the emission of the other nuclide is being detected. One-way scatter can readily be corrected for by filtering algorithms known in the art.
• Referring now toFIGS. 30 and 31, afeedback control system329 can be connected toenergy source320,sensors324 andenergy delivery devices314 and316.Feedback control system329 receives temperature or impedance data fromsensors324 and the amount of electromagnetic energy received byenergy delivery devices314 and316 is modified from an initial setting of ablation energy output, ablation time, temperature, and current density (the “Four Parameters”).Feedback control system329 can automatically change any of the Four Parameters.Feedback control system329 can detect impedance or temperature and change any of the Four Parameters.Feedback control system329 can include a multiplexer (digital or analog) to multiplex different electrodes, sensors, sensor arrays and a temperature detection circuit that provides a control signal representative of temperature or impedance detected at one ormore sensors324. A microprocessor can be connected to the temperature control circuit.
• The following discussion pertains particularly to the use of an RF energy source with an opticalbiopsy treatment apparatus10. For purposes of this discussion,energy delivery devices314 and316 will now be referred to as RF electrodes/antennas314 and316 andenergy source320 will now be an RF energy source. However it will be appreciated that all other energy delivery devices and sources discussed herein are equally applicable and devices similar to those associated withbiopsy treatment apparatus10 can be utilized with laser optical fibers, microwave devices and the like. The temperature of the tissue, or ofRF electrodes314 and316 is monitored, and the output power ofenergy source320 adjusted accordingly. The physician can, if desired, override the closed or open loop system.
• The user ofapparatus10 can input an impedance value that corresponds to a setting position located atapparatus10. Based on this value, along with measured impedance values,feedback control system329 determines an optimal power and time needed in the delivery of RF energy. Temperature is also sensed for monitoring and feedback purposes. Temperature can be maintained to a certain level by havingfeedback control system329 adjust the power output automatically to maintain that level.
• In another embodiment,feedback control system329 determines an optimal power and time for a baseline setting. Ablation volumes or lesions are formed at the baseline first. Larger lesions can be obtained by extending the time of ablation after a center core is formed at the baseline. The completion of lesion creation can be checked by advancingenergy delivery device316 fromdistal end16′ ofintroducer12 to a position corresponding to a desired lesion size and monitoring the temperature at the periphery of the lesion such that a temperature sufficient to produce a lesion is attained.
• Theclosed loop system329 can also utilize acontroller338 to monitor the temperature, adjust the RF power, analyze the result, refeed the result, and then modulate the power. More specifically,controller338 governs the power levels, cycles, and duration that the RF energy is distributed toelectrodes314 and316 to achieve and maintain power levels appropriate to achieve the desired treatment objectives and clinical endpoints.Controller338 can also in tandem analyzespectral profile19sand perform tissue biopsy identification and ablation monitoring functions including endpoint determination. Further,controller338 can in tandem govern the delivery of electrolytic, cooling fluid and, the removal of aspirated tissue.Controller338 can be integral to or otherwise coupled topower source320. In this and related embodiments,controller338 can be coupled tolight source317 and can be configured to synchronize the delivery of pulsed power to tissue site to allow for sensing by sensors orsensor array322aduring off power off intervals to prevent or minimize signal interference, artifacts or Unwanted tissue effects during sampling bysensors324 orsensor array322a. Thecontroller338 can also be coupled to an input/output (I/O) device such as a keyboard, touchpad, PDA, microphone (coupled to speech recognition software resident incontroller338 or other computer) and the like.
• Referring now toFIG. 30, all or portions offeedback control system329 are illustrated. Current delivered throughRF electrodes314 and316 (also called primary and secondary RF electrodes/antennas314 and316) is measured by acurrent sensor330. Voltage is measured byvoltage sensor332. Impedance and power are then calculated at power andimpedance calculation device334. These values can then be displayed at a user interface anddisplay336. Signals representative of power and impedance values are received bycontroller338 which can be amicroprocessor338.
• A control signal is generated bycontroller338 that is proportional to the difference between an actual measured value, and a desired value. The control signal is used bypower circuits340 to adjust the power output in an appropriate amount in order to maintain the desired power delivered at the respective primary and/orsecondary antennas314 and316. In a similar manner, temperatures detected atsensors324 provide feedback for maintaining a selected power. The actual temperatures are measured attemperature measurement device342, and the temperatures are displayed at user interface anddisplay336. A control signal is generated bycontroller338 that is proportional to the difference between an actual measured temperature, and a desired temperature. The control signal is used bypower circuits340 to adjust the power output in an appropriate amount in order to maintain the desired temperature delivered at therespective sensor324. Amultiplexer346 can be included to measure current, voltage and temperature, at thenumerous sensors324 as well as deliver and distribute energy betweenprimary electrodes314 andsecondary electrodes316.
• Controller338 can be a digital or analog controller, or a computer with embedded, resident or otherwise coupled software. In anembodiment controller338 can be a Pentium® family microprocessor manufacture by the Intel® Corporation (Santa Clara, Calif.). Whencontroller338 is a computer it can include a CPU coupled through a system bus. On this system can be a keyboard, a disk drive, or other non-volatile memory systems, a display, and other peripherals, as are known in the art. Also coupled to the bus are a program memory and a data memory. Invarious embodiments controller338 can be coupled to imaging systems, including but not limited to ultrasound, CT scanners (including fast CT scanners such as those manufacture by the Imatron Corporation (South San Francisco, Calif.), X-ray, MRI, mammographic X-ray and the like. Further, direct visualization and tactile imaging can be utilized.
• User interface and display336 can include operator controls and a display. In anembodiment user interface336 can be a PDA device known in the art such as a Palm® family computer manufactured by Palm® Computing (Santa Clara, Calif.).Interface336 can be configured to allow the user to input control and processing variables, to enable the controller to generate appropriate command signals.Interface336 can also receives real time processing feedback information from one ormore sensors324 for processing bycontroller338, to govern the delivery and distribution of energy, fluid etc.
• The output ofcurrent sensor330 andvoltage sensor332 is used bycontroller338 to maintain a selected power level at primary andsecondary antennas314 and316. The amount of RF energy delivered controls the amount of power. A profile of power delivered can be incorporated incontroller338, and a preset amount of energy to be delivered can also be profiled.
• Circuitry, software and feedback tocontroller338 results in process control, and the maintenance of the selected power, and are used to change, (i) the selected power, including RF, microwave, laser and the like, (ii) the duty cycle (on-off and wattage), (iii) bipolar or monopolar energy delivery and (iv) infusion medium delivery, including flow rate and pressure. These process variables are controlled and varied, while maintaining the desired delivery of power independent of changes in voltage or current, based on temperatures monitored atsensors324. Acontroller338 can be incorporated intofeedback control system329 to switch power on and off, as well as modulate the power. Also, with the use ofsensor324 andfeedback control system329, tissue adjacent toRF electrodes314 and316 can be maintained at a desired temperature for a selected period of time without causing a shut down of the power circuit to electrode314 due to the development of excessive electrical impedance atelectrode314 or adjacent tissue.
• Referring now toFIG. 31,current sensor330 andvoltage sensor332 are connected to the input of ananalog amplifier344.Analog amplifier344 can be a conventional differential amplifier circuit for use withsensors324. The output ofanalog amplifier344 is sequentially connected by ananalog multiplexer346 to the input of A/D converter348. The output ofanalog amplifier344 is a voltage which represents the respective sensed temperatures. Digitized amplifier output voltages are supplied by A/D converter348 to amicroprocessor350.Microprocessor350 may be a Power PC® chip available from Motorola or an Intel® Pentium® Series chip. However, it will be appreciated that any suitable microprocessor or general purpose digital or analog computer can be used to calculate impedance or temperature or perform image processing and tissue identification functions.
• Microprocessor350 sequentially receives and stores digital representations of impedance and temperature. Each digital value received bymicroprocessor350 corresponds to different temperatures and impedances. Calculated power and impedance values can be indicated on user interface anddisplay336. Alternatively, or in addition to the numerical indication of power or impedance, calculated impedance and power values can be compared bymicroprocessor350 with power and impedance limits. When the values exceed predetermined power or impedance values, a warning can be given on user interface anddisplay336, and additionally, the delivery of RF energy can be reduced, modified or interrupted. A control signal frommicroprocessor350 can modify the power level supplied byenergy source320 toRF electrodes314 and316. In a similar manner, temperatures detected atsensors324 provide feedback for determining the extent and rate of (i) tissue hyperthermia (ii) cell necrosis; and (iii) when a boundary of desired cell necrosis has reached the physical location ofsensors324.
• Conclusion:
• It will be appreciated that the applicants have provided a novel and useful apparatus and method for the biopsy and treatment of tumors using minimally invasive methods. The foregoing description of a preferred embodiment of the invention has been presented for purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise forms disclosed. Embodiments of the invention can be configured for the biopsy and treatment of tumor and tissue masses in a number of organs including but no limited to the liver, breast, bone and lung. However, embodiments of the invention are applicable to other organs and tissue as well. Obviously, many modifications and variations will be apparent to practitioners skilled in this art. Further, elements from one embodiment can be readily recombined with elements from one or more other embodiments. Such combinations can form a number of embodiments within the scope of the invention. It is intended that the scope of the invention be defined by the following claims and their equivalents.

Claims (12)

1. A method of treating a tumor comprising:

positioning a tissue biopsy and treatment apparatus for detecting and treating a tumor at a selected tissue site,

deploying a sensor array from the appratus, the sensor array including at least one emitting member and at least one detecting member;

deploying a plurality of resilient members from the elongated delivery device, at least one of the plurality of resilient members being positionable in the elongated delivery device in a compacted state and deployable with curvature into tissue from the elongated delivery device in a deployed state, at least one of the plurality of resilient members including at least one sensor,

distinguishing a tissue type utilizing the sensor array to measure a spectral profile of at least one portion of the tissue site to determine a tumor volume;

delivering energy to said resilient members to ablate or necrose at least a portion of the tumor volume; and

determining an amount of tumor volume ablation utilizing the sensor array.

2-104. (canceled)

105. A tissue biopsy and treatment apparatus for detecting and treating tumors, the apparatus comprising:

an elongated delivery device including a lumen, the elongated delivery device being maneuverable in tissue;

at least one sensor array configured to measure a spectral profile of at least a portion of a tissue site, the array comprising at least one emitting member and at least one detecting member;

a plurality of resilient members each having a tissue piercing distal portion, at least one of the plurality of resilient members being positionable in the elongated delivery device in a compacted state and deployable with curvature into tissue from the elongated delivery device in a deployed state, said resilient members being operatively connected to a source of energy for ablating tissue when energy is supplied to the resilient members.

106. The apparatus ofclaim 105, further comprising:

an optical switching device coupled to the sensor array to switch a mode of at least one of the emitting members or the detecting members.

107. The apparatus ofclaim 105, wherein the sensor array is deployable from the elongated delivery device.

108. The apparatus ofclaim 105, wherein at least one of the sensor arrays is positioned in one of the resilient members.

109. The apparatus ofclaim 108, wherein the sensor array is fixedly positioned in the resilient member.

110. The apparatus ofclaim 108, wherein the sensor array is deployable from the resilient member.

111. The apparatus ofclaim 105, further comprising:

an optical measurement device operatively connected to the at least one sensor array.

112. The apparatus ofclaim 105, further comprising:

a light source operatively connected to the at least one sensor array.

113. The apparatus ofclaim 105, further comprising:

at least one advancement device operatively connected to at least one of the sensor array and the plurality of resilient members.

114. The apparatus ofclaim 105, further comprising:

at least one thermal sensor positioned on at least one of (i) the sensor array, (ii) the plurality of resilient members, and (iii) the elongated delivery device.

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