fig1 shows the near - infrared imaging endoscope system . infrared light at a wavelength in the range 1550 - 1680 nm is emitted by the ir illumination source ( 1 ) in the form of a laser diode . the light travels down the illumination fibers ( 11 ) where it exits out of a dome - shaped glass structure and passes through the blood filled environment ( 7 ) where it illuminates a target ( 8 ). reflections from the target pass through the blood filled environment ( 7 ), through the hood ( 9 ) into an imaging lens ( 10 ). this light is transmitted down an imaging bundle ( 4 ) until it enters the infrared camera ( 2 ). output from the camera is sent to a video monitor ( 5 ), video output ( 4 ) and liquid crystal display ( 3 ). it is understood that the infrared camera element ( 2 ) may also incorporate various image processing means known in the art . this system can image structures about 0 . 2 - 2 . 5 cm away through flowing blood . the field of view is 40 - 120 degrees . pictures are displayed as black and white images and structures are displayed in real time at a frame rate of 10 frames / sec . ablated tissue appears as a whitening of regions of the image ( as reported by knight , heart rhythm 2004 , abstract 26 ). bubbles and coagulum formation are easily seen if they are in the field of view and within about 2 cm from the infrared endoscope ( as reported by knight , heart rhythm 2004 , abstract 26 ). fig2 shows the distal end of the infrared endoscope ( 12 ). the endoscope is about 7 french in diameter . unlike conventional endoscopes , the infrared endoscope employs a hood ( 9 ) to reduce blood backscatter . the hood may be made of glass , silica , acrylic or various polymeric materials . the hood extends about 2 mm beyond the termination of the optical fibers . the infrared endoscope ( 12 ) is similar in size and distal end shape to a conventional ablation catheter . by applying the radiofrequency electrode to the hood a combination endoscope - ablation catheter is formed . the ablation electrode is longer ; typically it was 4 mm and more recently longer 8 mm electrodes have been introduced . since the hood can be any size beyond about 1 . 5 mm in length , it could be easily extended to the 4 - 8 mm range . the hood ( 9 ) is also the ablation electrode if a metallic coating ( 14 ) is deposited to the surface of the hood . the disclosed embodiments inlcude an infrared imaging means or other imaging modality , although for clarity that means is not separately described . in fig3 , gold is deposited uniformly over the hood at about a 20 - 80 nm thickness . the gold coating is extended and attached to a gold connecting pad ( 13 ). the gold connecting pad is also electrically connected to a nitinol wire ( 15 ), which extends out of the proximal end of the catheter and is plugged into an rf generator for catheter ablation procedures . this configuration allows the physician to view the ablative process in real - time through a transparent ablation electrode . in addition , the use of minute metallic quantities coupled with a gold , titanium or nitinol connecting wire — all non - magnetic materials — make this catheter magnetic resonance ( mr ) imaging compatible . since mr machines utilize powerful magnets , conventional ablation catheters constructed from steel wires and platinum hemispheres are not only moved by the large magnets but can heat tissue from induction by the magnetic fields . with the metal - deposition process , even if a magnetic material is used , the quantity of metal in the catheter is extremely small . for example , a 4 mm long by 2 . 3 mm diameter hemisphere coated with 50 nm of metallic material represents a volume of about 0 . 0001 cubic millimeters of metal . currently used platinum hemispheres are about 0 . 3 - 0 . 4 mm thick corresponding to about 10 cubic millimeters of paramagnetic metal , or about 10 , 000 times more metal by volume . thus , any thin metallic deposition on a non - metallic substrate coupled with connecting wires made out of gold , nitinol or titanium will be mr - compatible . when gold , titanium or nitinol are used as the electrode deposition material , the catheter is completely mr - compatible . in an atrial fibrillation ablation , the physician positions the endoscope - ablation catheter just outside the pulmonary vein and will encircle with ablative lesions each pair of pulmonary veins . viewing the monitor ( 5 ) in fig1 during the ablation permits the physician to accurately place the electrode in a safe position relative to the pulmonary veins as well as view the entire ablation process . the lesion is seen a whitening or discoloration which grows as the rf ablation is applied . near the end point of the ablation process , bubbles and or coagulum may appear on the monitor . these events can lead to complications and signal when the rf ablation should be terminated . following the first lesion , if a contiguous line is desired to be produced ( as in atrial fibrillation ablation ) the catheter is moved to a position just adjacent to the first lesion which will appear as whitened circle on the monitor . after applying the second lesion , the physician can view both lesions to assure contiguity . in a similar manner , the physician can make a contiguous line anywhere in the heart referenced to anatomical markers , such as the pulmonary vein . future ability to ablate while moving to create an ablation line is also contemplated . an alternative to constructing a transparent electrode by coating it with a very thin layer of gold , is to form a pattern on the hood which includes enough space between the gold - deposited pattern so it appears nearly transparent on the viewing monitor . fig4 shows such an embodiment . in this embodiment , a series of gold - plated stripes ( 16 ) are fabricated on the surface of the hood . each of these stripes is connected to a gold connecting pad ( 13 ). as shown in fig5 , the connecting pad is connected to a nitinol , titanium or gold wire ( 15 ) for connection to an rf generator . the gold stripe does need not to be transparent since adequate imaging is provided by the spaces between the stripes . the pattern can be a cross - hatched as well as striped . the spacing between metallic lines should be no greater than one millimeter since rf energy ablates tissue about one millimeter from the electrode surface . sub - millimeter spacings will insure a continuous lesion in the spaces between electrode stripes . the raw image produced by the infrared camera will now include the stripes as well as tissue in the intervening spaces . by performing a spoc in the infrared camera , the reflection from the stripes is removed . the stripe pattern would be reduced by the spoc to a neutral contrast , leaving only the tissue as a multi - contrast entity in the monitor image . as in the first embodiment , this catheter is mr compatible if nitinol , titanium or gold connecting wires are employed . a typical application of the invention is with a transvenous catheter , however the invention is not limited to that application . the next embodiment ( fig6 ) depicts a rigid conventional visible - region endoscope ( 18 ) ablating a liver tumor ( 19 ). as in the infrared endoscope , a glass hood ( 9 ) is placed over the proximal end of the endoscope . the hood is coated with a gold coating of about 60 nanometers or less . a nitinol wire connects the gold coating to an rf generator ( 17 ). the endoscope provides visual confirmation of the tumor ablation . the demarcation of the tumor boundary to normal tissue is observable in the endoscope image viewed on the monitor . this permits greater precision in eradicating the tumor with safe margins into healthy tissue to assure non - reoccurrence of the tumor . fig7 is a picture of a thin gold - coated infrared endoscope - ablation catheter incorporating a surface thermocouple . on the glass hood a thin layer of a dissimilar metal is deposited in the shape of a tab ( 21 ). this is accomplished by masking the surface except the tab shape before depositing the metal deposition . this is followed by a dissimilar metal deposition of the entire surface ( 20 ) the portions on the surface where the two dissimilar metals are in contact form a thermocouple . the two metal deposits could be any dissimilar metals . in this embodiment , gold is deposited over the tab and acts as the ablation electrode and the tab is composed of 316 stainless steel . it is connected via a nitinol wire to a radiofrequency generator . it is understood any two metals , which can be deposited can be used to form the thermocouple or the ablation electrode , and any wire type can be used to connect to the radiofrequency generator . as in the first embodiment this embodiment uses the infrared endoscope configuration to ablate cardiac tissue . the endoscope - ablation catheter is positioned against the structure desired while viewed on the monitor . besides viewing the underlying tissue , the position of the thermocouple will also be visible . the catheter can be maneuvered so that the thermocouple is either in contact with blood or tissue . this is accomplished by placing the endoscope - ablation catheter in an outer sheath and rotating the catheter until the thermocouple is in the desired position . the thermocouple could be positioned against tissue to accurately record the tissue temperature during ablation . or conversely , it could be positioned against blood to insure that the critical temperature for blood coagulum formation was not exceeded . also , multiple thermocouples could be applied on the surface to give local temperature values on various positions on the transparent electrode . in addition , a transparent thermocouple is achieved if the tab coating is in the sub - 100 nm range . if transparency was achieved by the pattern - method in the second embodiment , the thermocouple material could be applied under any of the metallic lines . fig8 is a diagram of how two separate half - hemisphere electrodes , each with its own thermocouple is constructed . a masking band ( 22 ) is first applied over the hood . following this , two tabs ( 20 ) are deposited to each hemisphere with a dissimilar metal from the ablation electrode metal . finally , the ablation metal is deposited over the entire hood . the masking band is removed and replaced with an insulating opaque material to create two half hemispheres ( 21 ) which are clearly demarcated on the monitor ( fig1 , item 5 ). each half - hemisphere ( 21 ) is connected to a separate wire routed to the distal end of the catheter , and so each half - hemisphere serves as a separate electrode . as this electrode is placed against tissue , the half - hemisphere that contacts tissue is connected to the radiofrequency generator insuring that the energy is used to ablate tissue . the half - hemisphere contacting blood would not be activated , thereby reducing the coagulum formation during the ablation . both thermocouple wires are connected to a temperature acquisition unit , thus providing two temperature measurement places during the ablation . in this embodiment , the temperature recorded by the two thermocouples is displayed as a color superimposed over the two thermocouples . this is accomplished in the following manner . referring to fig1 , the position of the imaging bundle ( 6 ) relative to the infrared camera ( 2 ) is known because the connection is keyed to only allow insertion in one orientation . consequently , the position of the thermocouples on the monitor ( 5 ) is also known . over the pixels in the monitor ( 5 ) corresponding to the position of the thermocouples , a color corresponding to the temperature of the thermocouples will be displayed . as the ablation occurs , the physician now only needs to watch the monitor to fully assess the ablation and the temperature of the two thermocouples . as shown in fig9 , the thermocouples ( 21 ) will gradually change from green to yellow to red as the temperature increases . bright red would correspond to a surface temperature of 100 deg c . by observing the color superimposed over the thermocouples as well as bubble and coagulum formation , the physician can quickly terminate the ablation , reducing clot formation . fast - response active control means to adjust the ablation energy can rapidly respond to the temperature changes known to be at the tissue surface and dynamically adjust the energy applied to achieve a desired temperature set point . such fast - response means can also be used to determine out of range conditions at blood or tissue interface points and reduce energy application to prevent steam pops and coagulum formation events . rather than using thermocouples to measure temperature , the use of an endoscope allows other temperature measuring means as well . the following techniques could be used as well . 1 . the endoscope could incorporate a filter or beam splitter to send the component of the signal exceeding about 2000 nm to an infrared camera operating somewhere in the 2000 - 10000 nm range which is sensitive to heat . different temperatures would appear as different colors . this image could be superimposed over the image of the tissue to show both tissue and temperature changes 2 . the ablation electrode or substrate underneath could be coated with a chemical , which turns different colors depending on the temperature . in both of these cases , a temperature map of the entire electrode surface would be obtained . this would be much more useful than just one or a few discrete temperature determinations . hot spots could be recognized on the electrode surface and positional adjustments of the catheter could be made to provide more uniform heating . an alternate ablation configuration shown in fig8 is to connect the two electrodes in a bipolar radiofrequency mode . unipolar ablation systems generally have a single electrode surface as the active ablating contact element , and utilize a large area return electrode to complete the current circuit . the return electrode is generally placed on the patient &# 39 ; s skin . effective operation of such systems relies on the fact that current density becomes high , and ablation occurs , only in a small region close to where the active electrode contacts tissue . bipolar systems , on the other hand , employ two closely spaced electrodes of opposite polarity to define the current paths through tissue . the current is high because the electrodes are near to each other , and both electrodes are of comparable size , so the high current region spans the tissue volume lying between the electrodes . bipolar electrodes may be expected to form better - defined ablation lesions , since current will not vary unexpectedly as movement of the active electrode results in changing impedance pathways to the return electrode . alternate electrode configurations are shown in fig1 . configuration 10 a and b shows the electrode from a side and top view . this configuration has one ablation segment ( 24 ) which can be rotated to position the electrode against tissue . the advantage of this approach is that the electrode is not in contact with blood and a thinner ablation line is produced . configuration 10 c and d shows two electrodes with one electrode ( 25 ) of smaller surface area and another electrode ( 26 ) of larger surface area . the strategy is to place the smaller electrode against tissue and apply radiofrequency energy in a bipolar fashion . the smaller electrode will ablate preferentially over the larger electrode since it has smaller surface area . configuration 10 e and f shows a tripolar configuration ( 26 , 27 , 28 ). whichever electrode is lying against tissue is connected to the radiofrequency generator operating in the unipolar mode . alternatively , this configuration could be used in a bipolar fashion . the electrode touching tissue could be one pole , and the other two could be connected as the return or ground electrode . in all of these configurations , a thermocouple could be applied to each electrode . any number of segments could be used , such a four for a quadrant configuration described previously , or more if desired . in summary ( and without limitation ), this invention teaches the following methods and means : 1 . a transparent ablation electrode whereby the underling tissue can be viewed by an endoscope during the ablation using metallic film deposition technology applied to transparent non - metallic substrate . this is accomplished by coating a transparent non - metallic substrate ( such as glass or silica ) with a metal deposition thin enough to see through or by applying a pattern with sufficient open spaces to see the underlying tissue . 2 . forming a thermocouple on the electrode surface using the electrode surface as one of the thermocouple metals . constructing thermocouples in this manner improves the accuracy and provides fast time response to the tissue / blood temperature . it also provides an easy means to create multiple thermocouples on the electrode surface . 3 . displaying temperature information in a user - friendly format . temperature is displayed as color changes on the endoscope monitor . this permits all crucial information during the ablation to be displayed on one monitor 4 . alternate temperature measurements apart from thermocouples in conjunction with an endoscope . one alternate method is to view the emitted light in the 2000 - 10 , 000 nm region . another is to coat the electrode or substrate with chemical whose color changes with temperature . 5 . constructing complex electrode patterns on the ablation electrode surface to create alternate ablation patterns in conjunction with an endoscope . selection of electrode segments seen to be lying against tissue are taught in the embodiments . 6 . using the bipolar mode of radiofrequency application with one electrode segment being one pole while one or more segments forms the other pole . 7 . constructing a magnetic resonance imaging compatible ablation catheter using thin metallic depositions on a non - metallic substrate connected to a gold , titanium or nitinol wire routed to the catheter distal end . 8 . using fast response dynamic control of energy applied to take advantage of the fast time response to temperature of the ultra - low thermal mass electrodes and thermocouples or infrared light measured temperature in order to control to a predetermined tissue temperature set point . 9 . using fast response means to reduce energy applied to prevent steam pops or coagulum formation events at tissue and / or blood contact surfaces .
a novel transparent electrode that uses a conductive coating to allow delivery of current to the heart as well as outward imaging through the electrode is described . the embodiments disclose a catheter incorporating an endoscope , whose imaging tip is coated with a conductive coating that is transparent in the endoscopic image . however , a transparent electrode may be fashioned for any imaging modality , such as intracardiac echocardiography , that finds the electrode to be transparent to the energy used . this electrode coating may be a thin , optically transparent or translucent coating of platinum or gold or may be a pattern with enough open spaces to see the underlying tissue , such as looking through a screen . a wire is connected to the conductive coating and routed to a radiofrequency generator .