as previously described in this specification , the rf field generated by an mri machine will heat the wires of a typical catheter . preferably , the temperature rise of the exterior of an mri compatible catheter during a typical 15 minute scan time will preferably not exceed 4 ° c ., and more preferably 2 ° c . the heat generated by the wire is defined by the strength of the magnet and the length of the wire . longer wires get hotter than shorter wires . the preferred embodiments of the present invention allow a temperature - sensing catheter to be exposed to the field of an mr machine . since catheter length and therefore the length of the sensor wires can vary considerably from one catheter to another , different preferred embodiments may be appropriate with different catheter designs . generally , the first two preferred embodiments provide an insulator between the wire and the catheter . the third preferred embodiment removes the heat generated by passing a cooling fluid by the wire during the scan . the fourth preferred embodiment removes the wire from the catheter during an mri scan . note that the catheters in which a temperature sensor is placed may have more than one lumen for other medical purposes and procedures . for simplicity , the drawings omit extra lumens . also , note that the term wire will be used to describe the two wires of a temperature sensor . while the probe of the present invention is specifically referred to as a temperature probe , it should be understood that the present invention is particularly applicable to any sensor type that includes conducting wires ( e . g ., an oxygen probe ). thus , the probe as described in the specification may be any probe / sensor that uses electrically conductive wires . referring to fig1 , a catheter 10 with a wire lumen 12 is formed by a wall 14 that encircles the lumen . a sensor wire 18 is positioned within an insulating tube 16 that insulates the wire 18 from the lumen wall 14 . preferably , the insulating tube 16 is flexible enough not to overly stiffen the catheter 10 , can withstand the temperature of the wire and includes a low coefficient of heat transfer . one example insulating material is polyimide , which is ductile , has a particularly low coefficient of heat transfer and is available for use in thin - wall tubes . the thermocouple and thermistor wires are preferably 0 . 005 ″ in diameter and form a twisted wire set including electrical insulation of about 0 . 014 ″ in diameter . the diameter of the insulating tube 16 , affects the overall catheter diameter . preferably , the tube 16 has an id of 0 . 020 ″ and an od of 0 . 026 ″ which balances the size of the lumen 12 and the efficacy of the insulation . if the catheter lumen wall is 0 . 004 ″, the tube 16 of these dimensions provides a wall thickness of 0 . 007 ″. if used in a ventricular catheter , the example insulating tube 16 will reduce the heat transferred from the wire 18 to the catheter 10 by over two thirds . the basis of the heat reduction of the previous example is as follows . present silicone catheters typically have a wall thickness about 0 . 02 ″. the conductivity of polyimide is ⅙ that of silicone . the 0 . 007 ″ wall of tube 16 therefore has about the same insulating quality as a 0 . 042 ″ silicone tube wall . when the insulating value of the silicone wall is added to that of the polyimide wall of the tube 16 , the insulating effect is equal that of a silicone wall 0 . 062 ″ thick or about 3 times that of a silicone tube alone . over time , the temperature of the wire 18 will increase due to the reduction in heat transfer from wire 18 to the wall of the catheter 10 . the higher temperature of the wire 18 will reduce the net effect of the insulating tube 16 , so improvement may be less than a ⅓ reduction . the lumen diameter required to receive the 0 . 026 ″ od insulating tube 16 is about 0 . 03 ″. such a lumen is about twice as large as a lumen required to string a wire set without a thermal insulation sleeve or tube 16 . fig2 illustrates another preferred embodiment of an insulating arrangement according to the present invention in which short insulating tubes , segments or beads 20 are placed along the wire 18 . preferably , the beads 20 are longitudinally spaced along the wire at intervals that keep the catheter wall 12 from contacting the bare wire 18 if the catheter 10 is bent to the extent that it forms a 0 . 25 ″ radius . in one specific example , beads 20 have a length of 0 . 05 ″, are composed of polyimide and are fixed on the wire 18 at intervals of 0 . 150 ″. the air gap between the beads has a lower k factor than polyimide and thus reduces overall heat transfer . in cal /( cm )( sec )(° c . ), the conductivity of air is 6 . 9 × 10 − 7 vs . 3 . 7 × 10 − 4 for polyimide , a three orders of magnitude difference . this construction can be used in an mri with a stronger magnet and / or a catheter with a longer wire than the preferred embodiment of fig1 . in another preferred embodiment , a cooling fluid or gas ( e . g ., water or air ) is passed over or adjacent the wire . fig3 a illustrates a two - lumen construction in which an inflow lumen 22 delivers ( e . g . via a pump ) a cooling fluid through a crossover 24 to an outflow lumen 26 and ultimately to an exit in a transition tube 36 . the wire 18 is located in the outflow lumen 26 and is thereby cooled by the cooling fluid . the wire 18 is fixed to a transition tube 36 by an adhesive 35 . both the lumens are closed where needed by a plug 28 . the inlet lumen has a luer connector 34 on its proximal end that mates with a similar connector on a fluid source line . a transition tube 36 carries the wire out of the catheter to a connector , not shown . the cooling fluid exits out of a transition tube . the transition tube has a luer connector 34 that can mate with a take - away line , not shown . thus , the cooling fluid can be delivered over the wire 18 during an mri procedure and thereby maintain the temperature of the catheter . fig3 b illustrates a single fluid lumen embodiment that uses a fluid delivery tube 38 that extends the length of the wire lumen and delivers fluid to the bottom of the lumen . the fluid cools the wire 18 as it flows out the lumen . a transition tube 36 has a y 40 that separates the wire 18 from the outflow fluid . the cooling fluid exits the lumen through an outflow line 42 that has a luer fitting 30 . the wire 18 exits the upper leg 41 of the y where the wire 18 is bonded to an interior of the lumen of the catheter by an adhesive 34 . fig4 illustrates a preferred embodiment of a removable temperature probe 1 . preferably , the temperature probe 1 can be removed prior to an mri procedure , thereby eliminating any temperature increase of the wires 18 . alternately , any of the previously described insulation or cooling embodiments ( such as those seen in fig1 - 3 b ) can be used with the wire 18 of probe 1 , allowing the user to choose an appropriate probe 1 for a specific mri machine . the removable temperature probe 1 allows the device to be used in any strength mri machine if the other components of the catheter 10 ( e . g ., the catheter of fig5 ) are non - magnetic . the wire 18 of the probe 1 is located in a probe housing 44 . the distal end of the housing is a closed hemisphere . the wire 18 passes through a probe connector 30 ( e . g ., a luer fitting ) and is held in place by an adhesive . fig5 illustrates a catheter 10 with a lumen and transition tube 36 designed to receive the temperature probe 1 . both of the lumen ends are closed with a plug 28 . the transition tube 36 has a transition tube connector 34 that mates with the probe connector 30 on the temperature probe 1 . a guide tube 46 is preferably attached to the proximal end of the transition tube 36 . the curvature of the guide tube 46 and its low friction properties enable the temperature probe 1 to be inserted into the lumen of the catheter 10 . inserting the probe into a 0 . 025 ″ diameter lumen without the attributes of the guide tube may be problematic as the bend radius required to enter a 0 . 025 ″ lumen is quite small . when the probe is fully inserted in the catheter , the guide tube connector 34 and the probe connector 30 are joined . preferably , the probe housing 44 is composed of polyimide , as it is available in very thin wall tubes and has a low coefficient of friction . in one example , the polyimide probe housing 44 is 0 . 01 ″ id × 0 . 015 ″ od . the lumen diameter of the catheter is 0 . 03 ″. a guide tube 46 is integrated into the provided port . it serves two functions . the entry of the probe 1 into the catheter 10 requires that the probe make a very sharp turn into a very small lumen of the catheter 10 . the curved section of the guide tube 46 causes the probe 1 to curve as it makes the transition from the guide tube to the catheter lumen . the guide tube 46 also provides a surface with a low coefficient of friction . catheter materials are somewhat grabby and can make the insertion of the probe into a small diameter lumen difficult . in operation , the catheter 10 is implanted within a patient and the removable probe 1 is placed within the catheter 10 , coupling the transition tube connector 34 and the probe connector 30 . prior to an mri procedure , the transition tube connector 34 and the probe connector 30 are uncoupled and the probe 1 is removed . once the mri procedure has been performed , the probe 1 can be reintroduced into the catheter 10 and the transition tube connector 34 and the probe connector 30 can be coupled once more . fig6 a through 7c illustrate a preferred embodiment similar to the previously described preferred embodiment , further including a manifold 52 that snaps into or couples to a bolt 54 via biased locking tabs 59 . the bolt 54 includes a portion implantable within a patient ( e . g ., a patient &# 39 ; s skull ) and a passage therethrough . the manifold 52 includes multiple passages on its proximal end that feed into a multi - lumen extension 53 connected on its distal end . in other words , the manifold 52 “ funnels ” or directs different probes , tubes or other devices into the multi - lumen extension 53 via individual passages . preferably , the manifold 52 also includes a catheter passage that allows a catheter to pass through the manifold 52 , and ultimately into the patient , but not into the multi - lumen extension 53 . in this respect , a probe 1 can be advanced into a patient without being sterilized since the multi - lumen extension 53 provides a barrier between the patient and the probe 1 . the multi - lumen extension 53 is an elongated tubular member that may be a separate extension that couples directly to a distal side of the manifold 52 or optionally is unitary with the manifold 52 . alternately the multi - lumen extension 53 may be a distal part of a catheter 10 ( i . e ., similar to the catheter shown in fig5 ). preferably , a touhy - borst fitting holds a catheter 10 ( e . g ., a ventricular catheter shown in fig6 a and 6b ) to the manifold 52 and therefore to bolt 54 , allowing the catheter 10 to pass into the patient . the manifold 52 preferably includes several pigtails ( e . g ., flexible tubes , one of which is shown as pigtail 58 ) that each connect to a passage on the proximal end of the manifold 52 . the temperature probe 1 can be inserted into the brain through one pigtail and other sensors , such as an oxygen sensor can be inserted into other pigtails . for the sake of clarity , only pigtail 58 is shown in fig6 a - 7c . this pigtail 58 includes a probe connector 30 ( e . g ., a luer connection ) on its proximal end . alternately , the probe 1 may be passed directly into the manifold 52 without the use of a pigtail 58 . the temperature probe 1 is inserted into a pigtail 58 and is secured by the probe connector 30 . the distal end of the probe 1 passes through a passage of the manifold 52 and into a lumen 55 of the multi - lumen extension 53 . when fully inserted , the temperature sensor of the probe 1 resides in the patient ( e . g ., a patient &# 39 ; s brain ) but is separated from actual contact with the patient by the closed multi - lumen extension 53 . the temperature probe can be inserted and removed as needed . preferably , the lumen 55 is closed at a distal end ( i . e ., the end inserted into the patient ), however the lumen 55 may also be open within the multi - lumen extension 53 . since the pigtail 58 is connected to the manifold 52 , any pushing , pulling or other force exerted on the pigtail 58 or probe 1 will be transferred to the manifold 52 and the bolt 54 , instead of to the catheter 10 , as may occur in the preferred embodiment of fig4 and 5 . in operation , the bolt 54 is implanted within the patient ( e . g ., into patient &# 39 ; s skull 60 in fig6 a ). next , the catheter 10 is inserted through the touhy - borst of the manifold 52 , through the bolt 54 and into the patient ( e . g ., the brain ). the manifold 52 is then connected to the bolt 54 . the probe 1 is inserted into the pigtail 58 , through the manifold 52 and into the lumen 55 of the multi - lumen extension 53 . the probe connector 30 is coupled to the probe 1 to maintain the position of the probe 1 . prior to an mri procedure , the probe connector 30 is uncoupled from the probe 1 and the probe 1 is removed from the catheter 10 . once the mri procedure is complete , the probe 1 can be reintroduced into the pigtail 58 as previously described . alternately , the pigtail 58 , the manifold 52 and the multi - lumen extension 53 are composed of an insulating material as previously described in this specification ( e . g ., polyimide ). in this respect , the probe 1 can be left within the patient during an mri procedure . the first two embodiments of fig1 and 2 are convenient in that they require no involvement from the mri staff . the third and fourth embodiments may require that the staff prepare the catheter prior to the mri but may be less expensive than the first two embodiments . although the invention has been described in terms of particular embodiments and applications , one of ordinary skill in the art , in light of this teaching , can generate additional embodiments and modifications without departing from the spirit of or exceeding the scope of the claimed invention . accordingly , it is to be understood that the drawings and descriptions herein are proffered by way of example to facilitate comprehension of the invention and should not be construed to limit the scope thereof .
a preferred embodiment includes an mri compatible catheter that maintains a desired temperature during an mri procedure . specifically , the catheter includes a lumen containing sensor wire that is surrounded by an insulating material . this material limits the transfer of heat to the outside of the catheter as the sensor wire heats during an mri procedure .