[ 0121 ] fig1 is a schematic diagram of a system for conducting vascular catheterisation of a patient . the system includes a personal computer ( pc ) 1 that presents a graphical user interface ( gui ) via a number of monitors 2 . the user interface system is based on a microsoft windows ™ platform . multiple windows may be used to acquire / project data from / to the user . although not shown , the pc can accept user inputs via a keyboard and mouse , or other pointing device , in the usual manner . the pc includes a number of data stores 7 , which may be external , and a cd rom reader / writer device 3 the pc is coupled via a data interface 4 to a thermography catheter 5 , details of which will be described below . in this example , the thermography catheter 5 transmits four channels ( one for each sensor ) which are received by the data interface 4 an analogue temperature data signal on each channel is converted to a digital signal using an a / d converter within the data interface 4 at a user configured sampling rate of up to 2 5 khz . typically , the sampling rate would be set at around 25 to 50 hz to reduce the quantity of data acquired . the data interface 4 includes a multiplexer ( not shown ) that combines the four digital channels into a single time division multiplexed ( tdm ) signal this tdm signal is coupled to the pc over a pci pus . the data from each channel are written into an area of memory within the data store 7 reserved for that channel where they can subsequently be retrieved for data processing along with the corresponding time sequenced data from other channels and image data from other sources . the temperature data from the thermography catheter 5 are introduced to the system software running on the pc using function calls temperature data are input to the software as the actual voltage at the a / d hardware inputs , and therefore they have to be converted to temperature . a sensor data convert function handles this process the system is designed to be used in conjunction with a fluoroscopy x - ray apparatus and therefore includes a video frame capture interface 6 that couples fluoroscopy video data inputs to the pc via a pci bus . similarly , it can be used in conjunction with intravascular ultra - sound ( ivus ) image data fed from the thermography catheter 5 ( when provided with the appropriate hardware ) the system software allocates sufficient memory area to the systems memory for this data , taking into account the current system configuration , for example sampling rate , recording time , and video frame size a memory handle hdib is used to map video data directly through the pci bus from the video frame capture interface 6 to this allocated area in memory . hdib memory is divided into i equal chunks , each of a size equal to the frame capture interface frame - puffer . optionally , hdib [ i ] data can also be mapped to a memory area of a screen - video buffer , giving capability of live preview during recording . each time the software records an x group of four ( or more ) temperature measurements , it prompts for a frame capture at hdib [ x ]. a user configuration file determines the ratio between temperature data fluoroscopy video frame capture whilst in normal circumstances the thermography catheter 5 is inserted manually , it is intended that when performing vascular measurements the thermography catheter 5 is pulled back relative to a predetermined start position using an electro - mechanical pull - back drive 8 coupled to the body of the catheter . the pull - back drive 8 is controlled by the pc via a pull - back drive interface 9 the system software accesses user - defined configuration files to get the necessary information about controlling the systems automatic pull - back interface 9 . data sampling rite , recording duration and pre - selected retraction rate are taken into consideration for adjusting the pull - back speed . the software routines control a d / a converter ( not shown ) that feeds the input of the pull - back interface 9 with an appropriate control voltage . the controlled pull - back process will be described in more detail below . temperature data plotting may be both on - line and / or off - line . in an on - line mode , the monitor presents a temperature / time - distance graph , where temperature is continuously plotted as connected dots . in an off - line mode , temperature data can be loaded from the data store 7 ( or other media ) and plotted on the screen graph . the user can scroll to different time / temperature locations , while several automated functions may be provided , for example auto min - max marking , colour coding of temperature an a bullseye graph colour thermal maps , and 3d temperature coding on a cylinder model in the latter case , an artificial colour 3d cylinder that represents the vessel is divided into splines equal to the temperature channels . the channel temperature is coded on each spline with colours varying from dark - blue ( minimum temperature ) to flashing - red ( maximum temperature ). the user can rotate the cylinder as he wishes in a virtual 3d world . the focus is set to the specific time / distance that corresponds to the mouse position on the screen temperature / time graph 3d position control is performed using multi cubic - bezier lines , where the curvation control points change in relation to the cylinders position in the virtual world . a separate window shows numeric details for the particular time / distance position . video frame data from simultaneous fluoroscopy / ivus are plotted as image frames in a separate window . by moving to a specific time / temperature position , the corresponding video frame is automatically projected . in this way , temperature and video frames are accurately synchronised . the system software is designed to provide basic and advanced image processing functions for the captured fluoroscopy / ivus video frames , such as filtering and on - screen measurement functions . the user can filter the captured frame to discard unwanted information while focusing on the desired one there are several auto - filter options as well as manual adjustment of the image curve in addition , the user can calibrate the system and proceed in performing on - screen measurements of both distances and / or areas . automatic routines perform quantification of the measurements giving significant information on lesion characteristics the temperature can also be colour coded on the fluoroscopy frame , providing unique information about the correlation between temperature and morphology . by using temperature data and video frame data , the system software uses advanced algorithms based on interpolation and fractal theory to plot a 3d reconstruction of the vessel under measurement with colour coding of temperature . the user can freely move the virtual camera inside the reconstructed vessel in 360 °, and / or - fly - through the vessel . 2d reconstructions are also provided . temperature data can be processed on the basis of mean temperature , or on a channel - by - channel basis . [ 0131 ] fig2 and 3 show an example of the distal tip of a thermography catheter incorporating sensors 10 mounted circumferentially about a central lumen 14 . in this example , four sensors 10 are mounted on resiliently biased projections 11 circumferentially about the central lumen at 90 ° intervals , although only one sensor is shown here for the sake of clarity . the projections 11 are made of nitinol the figures clearly show the deployed configuration projection adopting an arcuate shape along its length , with the gradient of the projection , with respect to the longitudinal axis of the catheter , increasing as a function of distance along the projection from the end attached to the catheter body . the sensors 10 are ntc thermistors . such thermistors prove extremely reliable regarding the relation between the temperature changes and resistance changes . an ntc thermistor having a 30 kω impedance at 25 ° c . typically maintains linearity between 35 ° c . and 45 ° c ., at a resolution of 0 . 01 ° c .- 0 . 1 ° c . the construction of the thermistors 10 are that of two rectangular plates with a metal alloy oxide in the centre the thermistor has dimensions in the range of 0 . 25 mm - 5 mm , and a caliper less than 1 mm . each thermistor 10 is attached to the end of each projection 11 by bonding with an thermally conducting epoxy glue 12 . each thermistor 10 is connected to an insulated bifilar wire 13 . the wire 13 has a low impedence and is constructed from nickel and / or copper . this wire provides an electrical connection with the proximal end of the device ( not shown ). as shown in the figures the wire 13 is coiled around the length of the projection 11 this feature has the effect of substantially eliminating strain when the projection 11 flexes . the pitch of the coil is typically arranged to be such that there are 5 to 10 turns over a length of 10 mm . as will be described below , a neat shrink wrapping 15 is applied over the projection 11 to prevent damage to the wire 13 during retraction and replacement of an outer sheath 16 . the neat shrink wrapping also provides an additional degree of electrical isolation . to assemble a projection , a nitinol arm is first pretreated by placing it in a bending tool and heating to around 700 ° c . to impart a bend in the arm the nitinol arm is then held straight in a chuck and a thermistor / bifilar wire assembly is attached to a free end of the arm using a uv cure adhesive . the wire 13 is then spun around the length of the nitinol arm . finally , the neat shrink wrapping 15 is placed over the length of the nitinol arm to a point just beyond that of the thermistor . in tis example , the heat shrink wrapping is supplied as a polyester tube that is cut to length an epoxy resin is then injected into the end of the tube the assembly is subsequently heat treated to shrink the tube and set the epoxy resin . the heat shrink wrapping is then trimmed back to expose at least part of the epoxy resin coated thermistor , while maintaining electrical isolation of the bifilar wires . after neat treatment , te heat shrink has a wall thickness of around 10 μm . as shown in the figures , the thermography catheter is mounted on an angioplasty guide wire ( not shown ) which runs through the central lumen 14 and a guide member 17 which defines the tip of the thermography catheter . in use , the apparatus may be actuated between a non - wall - temperature sensing configuration and a temperature sensing configuration . the non - temperature sensing configuration is hereinafter referred to as the retracted configuration . the temperature sensing configuration is hereinafter referred to as the deployed configuration . an example of the deployed configuration is shown in fig2 . an example of the retracted configuration is shown in fig3 in the retracted configuration , the sheath 16 encompasses the projections 11 so that they are constrained to lie parallel to the longitudinal axis of the catheter and therefore cannot take up a deployed position . the sheath 16 extends as far as the rear end of the guide member 17 but does not overlap the guide member . this minimises any protrusions from the thermography catheter which could lead to damage of the vascular wall . this is particularly important where a vessel is angulated or there is bifurcation of the vessel . such features lead to bending of the thermography catheter and would emphasise any protrusions . hence , in this example the sheath 16 and the guide member 17 present a smooth profile when adjacent to one another in the retracted configuration . to adopt the deployed configuration , the sheath 16 is withdrawn away from the extreme distal tip i . e ., away from the guide member 17 , towards the proximal section , to expose the projections 11 . when the sheath 16 is withdrawn to the extent shown in fig2 the resiliently biased projections 11 take up the deployed configuration . it should be noted that the sheath is controlled from the proximal end of the apparatus and is not shown in its entirety in the figures . the projections 11 individually extend a certain distance ( r ) away from the longitudinal axis of the catheter . in the deployed configuration , r has a value in the range of 2 - 4 mm . however , r is not fixed and varies with the diameter of the vascular tissue being measured due to the flexibility of the projections 11 . different diameter catheters may be used for different diameters of vascular tissue . however , as it is desirable to minimize the diameter of catheters in all interventional vascular treatments , it is desirable to adapt the length of the projections and / or the angle to which the projections may extend away from the central lumen depending on the dimensions of the vascular tissue being measured rather than increasing catheter body dimensions thus , the projections for a large blood vessel , for example 8 mm diameter , will generally require a length of projection in the range of 5 mm to 10 mm . smaller diameter vascular tissue , for example 2 . 5 mm diameter , will generally require a length of projection in the range of 2 mm to 6 mm . typically , the ratio of the area of the cross - sectional profiles of the apparatus in the deployed to retracted configurations is up to 4 : 1 . the thermography catheter includes a valve system ( not shown ) allowing the annular gap between the sheath and the intermediate lumen to be flushed in an adequate way , thus minimising the possibility of air bubbles or debris within the sheath such a valve is constructed to enable engagement by a 2 mm , 5 mm , or 10 mm , 6 ° luer syringe . the thermography catheter may be flushed with a suitable fluid such as saline . when flushing the catheter , fluid should exit via the distal tip of the catheter , indicating proper flushing of the sheath in addition , the catheter includes a female luer fitting ( not shown ) attached to the proximal end of the central lumen , to enable the central lumen to be flushed in a similar way to the sheath . with reference to fig4 in use , the sequence of events begins with the insertion of a guiding catheter into the area of general interest ( step 100 ), for example the cardiac region . where , for example , the coronary arteries are to be examined , the guiding catheter is inserted so that it is in or adjacent to the opening of the coronary arteries . an angioplasty guide wire is then inserted into the coronary artery , past the point of specific interest ( step 110 ). the guide wire is usually inserted with the aid of standard fluroscopic techniques , as is the guiding catheter . once the guiding catheter and guide wire are in position , the thermography catheter of the present invention is maneuvered over the guide wire to a position beyond the specific area of interest in the coronary artery ( step 120 ) with the aid of fluoroscopy . an angiogram is taken ( step 130 ) to assess the position of the thermography catheter in the vascular tissue . this image is saved and the position of the thermography catheter is marked on the image so as to define a starting point for the controlled pull - back step . the guiding catheter is then locked in position and both the sheath and the lumen housed in the sheath are locked to mounts on the pull - back device . the sheath is then retracted to allow the projections to adopt the deployed configuration . controlled pull - back of the thermography catheter then takes place ( step 140 ). the pull - back takes place at a constant speed and is controllable by the user . pull - back typically takes place at speeds of 0 . 1 to 2 mm in divisions of 0 . 1 mm or so the pull - back takes place over a distance of the vascular tissue being measured . temperature readings may be taken intermittently or substantially continuously . the data transmitted by the sensors from the vascular wall is captured for data and image processing ( step 150 ) together with a fluoroscopy / ivus image frame . as the thermography catheter is withdrawn inside the artery , the projections automatically adjust their angle following the wall &# 39 ; s morphology without losing the desired thermal contact . the result is that the thermal contact between the sensors and the wall is continuously maintained , even when the catheter is crossing very irregular plaque formations . once the pull - back has been completed relative movement between the sheath and the intermediate lumen places the sensors in the retracted configuration . this restores the original smooth profile of the thermography catheter . as mentioned above , the system software has the capability to capture image - frames that come from standard fluoroscopy or ivus devices simultaneously with temperature spatial data that come from fluoroscopy / ivus are combined by the software with temperature data . this is done as follows : before the thermography procedure starts , and while the thermography catheter is still out of the target vessel , the user records the fluoroscopy - tube / bed position and records a video frame during injection of contrast media . the vessel is opacified , and the image is stored and projected on one of the system monitors . the user calibrates the pixel / mm relation by using the guiding catheter as a known reference so that distances in mm can subsequently be estimated accurately on the monitor . as shown in fig5 the user then marks the beginning and ending of the area of interest ( points b and e ) by clicking on them using the mouse : in return , the software marks these points on the monitor by arrows or lines . the user then positions the thermography catheter in the target vessel by pushing it forward on the guide wire until the fluoroscopic marker on the thermography catheter passes point e over a few mm ; while watching the system &# 39 ; s monitor , the thermal sensors are then deployed and the user manually pulls the thermography catheter back gently until the fluoroscopic marker overlaps exactly on point e . the software then instructs the automatic pull - back device to pull back the thermography catheter over the length of the be curve within the vessel . the software then performs auto - border detection on the be area of the fluoroscopy video frame using a photoluminescence technique , and temperature is subsequently coded in the atherosclerotic plaque outline as rgb color degradation from dark - blue ( 0 , 0 , 255 ) corresponding to the minimum detected temperature , to flashing red ( 255 , 0 , 0 ) corresponding to the maximum detected temperature . a reference color map may be provided , and by moving the mouse cursor inside the be area , temperature values may also automatically be provided in a numeric format . [ 0154 ] fig6 shows the same image processing as applied to a single ivus image frame for a section of the target vessel . fig7 shows a 3d section of a target vessel constructed using a series of ivus images ( without temperature mapping ) as shown in fig8 a number of ivus images can be processed to provide a 3pd representation of the temperature profile / morphology over a length of the target vessel . this is a actual image of the artery of a patient having an unstable coronary syndrome [ 0155 ] fig9 and 10 show temperature profiles obtained in a normal artery having substantially no inflamed plaque and an artery known to contain inflamed plaque , respectively , obtained by continuous sampling of temperatures using a thermography catheter having 4 sensors . the values obtained for the 4 different sensors are shown in the figures the zero value is the mean value for the normal artery . the examples below show the results of obtaining a series of individual temperature measurements in the blood vessels of a series of patients . measurements were carried out using a thermography catheter as described above in fig2 and 3 table 1 below shows the heterogeneity measured in the blood vessel , namely the difference between the lowest individual temperature value ( reference temperature value ) and the highest individual temperature value ( first temperature value ). these values are measured as deviation from the temperature at non - atherosclerotic (“ normal ”) vessel wall . all values are in degrees centigrade (° c .). it is believed that the results from patients 1 to 15 are all indicative of the likely presence of inflamed plaque , particular patients 8 an 12 further results are shown in table 2 below .
the invention is based on the realisation that inflamed plaques in blood vessel walls , which are potentially vulnerable to rupture , can be detected at elevated temperatures which are lower than previously realised . in particular , the low temperatures at which inflamed plaque can be detected are often associated with systems in which blood flow is generally close to normal in particular temperature differences above zero but not more than 0 39 ° c . have been found to be indicative of the presence of inflamed plaque .