WO2007042819A1 - Dispositif de mesure de température vasculaire - Google Patents

Dispositif de mesure de température vasculaire Download PDF

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Publication number
WO2007042819A1
WO2007042819A1 PCT/GB2006/003798 GB2006003798W WO2007042819A1 WO 2007042819 A1 WO2007042819 A1 WO 2007042819A1 GB 2006003798 W GB2006003798 W GB 2006003798W WO 2007042819 A1 WO2007042819 A1 WO 2007042819A1
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WO
WIPO (PCT)
Prior art keywords
sensor
catheter
temperature
projection
thermistor
Prior art date
Application number
PCT/GB2006/003798
Other languages
English (en)
Inventor
Antony Flint
Stephen Blatcher
Richard Dibling
Original Assignee
Thermocore Medical Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Thermocore Medical Limited filed Critical Thermocore Medical Limited
Publication of WO2007042819A1 publication Critical patent/WO2007042819A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/02007—Evaluating blood vessel condition, e.g. elasticity, compliance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/01—Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/01—Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue
    • A61B5/015—By temperature mapping of body part

Definitions

  • the present invention relates to a medical device for measuring the temperature of vascular tissue.
  • the present invention is particularly related to locating inflamed or unstable atherosclerotic plaque in a blood vessel.
  • Plaque can develop in a patient's cardiovascular system.
  • the plaque can be quite extensive and occlude a substantial length of the vessel.
  • the plaque may be inflamed and unstable, such plaque being subject to rupture, erosion or ulceration which can cause the patient to experience a myocardial infarction, thrombosis or other traumatic and unwanted effects.
  • Such inflamed and unstable plaques are commonly known as vulnerable atherosclerotic plaques. Inflammation, such as that of unstable plaque, is associated with increased temperature.
  • Thermography has been used to determine variations in temperature of a vessel wall using a vascular catheter, termed a thermography catheter, where the distal tip of the catheter incorporates sensors mounted on resiliently biased projections where the projections are attached at the proximal end to a body.
  • the catheter is inserted into a vessel and can be actuated between a deployed configuration and a retracted configuration.
  • a sheath encompasses the projections so that they are constrained against the body of the catheter.
  • the sheath is withdrawn and the resiliently biased projections (which are made from a material such as NiTinol) take up the deployed configuration and contact the vascular wall.
  • the projections are preferably arcuate in shape so can follow the morphology of the vessel wall.
  • Thermistors are used as sensors and are generally made from ceramic materials with metal alloy oxides and may have sharp edges. It is necessary, therefore, to provide a coating over the thermistor (or any other temperature sensor) to provide a smooth biocompatible surface which will not damage the vessel wall.
  • thermography catheters have been successful in detecting small temperature variations along a vessel wall which are indicative of vulnerable plaque.
  • the temperature variation along the vessel due to the vulnerable plaque is typically less than 1 0 C as discussed in our co-pending application US Application No. 10/323,592.
  • the present invention provides catheter apparatus for temperature measurement of vascular tissue, comprising a flexible body, at least one resiliently biased projection depended from the body, a sensor carried by the projection and an electrical carrier for transmitting data from the sensors to a remote device wherein the sensor is encapsulated in a layer of glass.
  • the present invention provides a method of measuring the temperature of vascular tissue, the method comprising; placing a catheter apparatus in a vessel, the catheter apparatus comprising a flexible body having at least one resiliently biased projection depended from the body and a sensor encapsulated in a layer of glass carried by the projection; deploying the projection to contact the vessel wall; and transmitting data from the sensor to a remote device.
  • the benefits include improved physical interactions with the vessel wall and blood when in use and allow for significant improvements in the sensitivity and reliability of the temperature measurements to be achieved leading to a more successful determination of the presence of vulnerable plaque.
  • the glass coating has advantageous physical properties providing a biocompatible surface which is smooth and well suited for contacting the vascular wall.
  • glass is a hydroscopic material (in contrast to most polymers such as those used as heat shrink wrapping which are hydrophobic) and has favourable wetting characteristics, minimising frictional effects with the vasculartissue and giving excellent lubricity.
  • the glass exhibits reduced friction when wet (again, in contrast to most polymers which exhibit increased friction when wet).
  • glass has a relatively good thermal conductivity and can be coated onto the thermistor so that the coating has a substantially uniform thickness at all points around the thermistor. This means that the heat absorbed by contact of one part of the sensor with a vessel wall, is quickly transmitted around the whole sensor to give an accurate result.
  • the uniform coating also means that the results are more reliable than with previous thermography catheters as the reading is not dependent on the orientation of the sensor because the heat absorbed by the sensor through contact at any point with the vessel wall, will quickly be homogenously distributed throughout the sensor.
  • the present invention is also advantageous in terms of construction as the glass coating provides a smooth and biocompatible coating obviating the need for a polymer wrapping around the sensor (although one may be provided on other parts of the projections).
  • the present invention is concerned with optimizing the heat capture to ensure that as much as possible of the heat generated by the inflamed plaque is detected and makes use of a glass coating.
  • the sensor is encapsulated in a layer of glass which is less than 100 ⁇ m thick.
  • a thin layer of glass means that the glass has a low thermal mass leading to improved accuracy and responsiveness of the sensor.
  • having such a thin layer of glass ensures that the thermistor is not more than 100 ⁇ m away from the vascular wall.
  • it also ensures that at least some of the thermistor is in the plume of heated blood, thereby improving heat capture.
  • non- leaded glass is used having a good thermal conductivity.
  • the senor is a thermistor having a diameter of less than 500 ⁇ m. This is significantly smaller than conventional thermistors used in thermography catheters. In order to give an accurate temperature reading, the thermistor must absorb heat from its surroundings which takes time and inevitably changes the temperature of the surroundings. Using a smaller thermistor and a thinner coating reduces the thermal mass of the sensor leading to improved sensitivity and accuracy.
  • Glass encapsulated sensors in accordance with the present invention are especially suitable, although not exclusively, for use with the types of thermography catheters described in our co-pending applications US Application Nos. 10/169523,
  • the method of the present invention and catheter for use in such a method are concerned with measuring the temperature of vascular tissue.
  • the aim of the invention is to provide an improved way of identifying variations in the temperature of the vessel wall which may be indicative of inflamed or unstable atherosclerotic plaque. Once the plaque has been identified, appropriate treatment can be administered.
  • the catheter is placed in the vessel of interest which is most commonly a cardiac vessel. This is done using conventional techniques.
  • the flexible body of the catheter can be of any conventional design and preferably comprises a plurality of co-axial lumen and an external covering hereinafter referred to as a sheath.
  • the body may be formed from the standard catheter lumen materials, for example, nylon, FEP, polyurethane, polyethylene and nitinol and mixtures thereof.
  • the distal end of the body usually comprises a guide member.
  • the catheter comprises at least one resiliently biased projection depended from the body.
  • a first end of the projection is attached to the body while a second end carries one or more sensors.
  • the second end is adapted to be radially movable away from the body on deployment.
  • the projection preferably comprises a superelastic material, preferably exhibiting features such as biocompatibility, kink resistance, constancy of stress, physiological compatibility, shape-memory deployment, and fatigue resistance.
  • Ni-Ti-based alloys (with between 50 and 60 atomic percent nickel) are well suited for use in the present invention.
  • the apparatus may be actuated between a deployed configuration and a retracted configuration.
  • the sheath In the retracted configuration, the sheath encompasses the projections 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 is withdrawn away from the distal tip to expose the projections.
  • the resiliency biased projections take up the deployed configuration.
  • the projections are designed to be resiliently biased against the vascular wall in use, thus initiating contact between the sensor and the wall. This achieves an adequate thermal contact with the vascular wall, without substantially compromising blood flow.
  • the projection in the deployed configuration, preferably adopts an arcuate shape along at least part of its length, preferably wherein the gradient of the arcuate portion of the projection, with respect to the longitudinal axis of the catheter, increases as a function of distance along the projection from the end attached to the catheter body.
  • the projection in a deployed configuration, adopts an arcuate shape along a major portion of its length under its own resilient bias.
  • the free end of the projection bends away from the catheter body.
  • This particular embodiment allows the sensor-bearing end of the projections to more accurately and consistently follow the morphology of the vascular tissue.
  • each sensor is mounted on a separate projection.
  • four projections, each having a single sensor mounted thereon, are provided.
  • the sensors are preferably located on an outer face near the distal end or on the distal end of the projection so that they contact the vascular tissue in use.
  • thermocouple any type of temperature sensor, for example a thermistor, thermocouple or infrared sensor can be used where the sensor is encapsulated in a layer of glass.
  • the senor is a thermistor.
  • the layer of glass should be as thin as possible to permit efficient heat transfer to the sensor and is preferably less than 100 ⁇ m thick, in particular between 1 and 80 ⁇ m, ideally between 10 and 50 ⁇ m.
  • encapsulated we mean that the exposed surfaces of the sensor (those surfaces which are not connected to the body and which would otherwise be in contact with the atmosphere) are coated in glass.
  • the sensor should be as small is possible while maintaining reasonably accurate results but, in view of manufacturing and handling requirements, usually has a diameter of at least 10 ⁇ m.
  • the sensor can be, but is not necessarily cylindrical.
  • the diameter is the largest dimension of the distal surface of the sensor (which is the surface that comes into close proximity with the vessel in use).
  • the diameter of the sensor is between 50 and 400 ⁇ m, more preferably less than 300 ⁇ m or even less than 200 or 100 ⁇ m.
  • the catheter of the present invention comprises an electrical carrier for transmitting data from the sensors to a remote device.
  • the electrical carrier is typically coiled around the body of the projection to reduce the strain.
  • the pitch of the coil is arranged such that there are 5 to 10 turns per cm.
  • Any conventional electrical carrier can be used, preferably an insulated bifilar wire.
  • the wire and optionally also the thermistor can be covered with an electrically insulating coating such as parylene (which is the polymer of para-xylene).
  • parylene which is the polymer of para-xylene.
  • the parylene may be substituted, for example with chlorine. Parylene is applied by deposition. Parylene is particularly suitable for this purpose as it is biocompatible and infra-red transparent.
  • Figure 1 shows a schematic diagram of a system for conducting vascular catheterisation of a patient
  • Figure 2 shows an enlarged partial section of an example of the distal tip of a thermography in accordance with the present invention in a deployed configuration
  • Figure 3 is a flow diagram illustrating the steps involved with conducting intravascular catheterisation of a patient and the associated data capture and image processing
  • Figure 4 shows an angiogram frame overlaid with a temperature profile.
  • FIG. 1 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.
  • GUI graphical user interface
  • the user interface system is based on a Microsoft WindowsTM platform. Multiple windows may be used to acquire/project data from/to the user.
  • the PC can accept user inputs via a keyboard and mouse, by touching a touch-sensitive screen or in another conventional 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.
  • 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.
  • TDM time division multiplexed
  • This TDM signal is coupled to the PC over a PCI bus.
  • 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.
  • thermography catheter 5 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-buffer.
  • hDib [i] data can also be mapped to a memory area of a screen-video buffer, giving capability of live preview during recording.
  • 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.
  • 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 rate, 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.
  • the monitor presents a temperature/time-distance graph, where temperature is continuously plotted as connected dots.
  • 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 thermal maps, and 3D temperature coding on a cylinder model.
  • 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.
  • 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.
  • 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.
  • Figure 2 shows an example of the distal tip of a thermography catheter incorporating sensors 10 mounted circumferentially about a central lumen 14.
  • sensors 10 mounted circumferentially about a central lumen 14.
  • 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 sensors 10 are NTC thermistors which are 178 ⁇ m thick, 190 ⁇ m wide and 370 ⁇ m long. Each thermistor 10 is covered by a layer of glass 12 which has a thickness in the order of tens of microns. The proximal end of the glass coated thermistor is attached to a plastic tube 18.
  • a wrapping of heat shrink material which is in the order or 10 ⁇ m thick and which is indicated as 19 on Figure 2, is applied around the plastic tube 18 to help to secure the tube to the arm 15 and to ensure the projection has a smooth profile.
  • the wrapping extends about 0.5mm beyond the distal end of the arm 15 but does not extend over the thermistor 10.
  • 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 Figure 2, away from the distal end, 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.
  • a NiTinol arm 15 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 15 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 15.
  • parylene C chlorine substituted parylene
  • the coating is about 10 ⁇ m thick.
  • 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.
  • 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 Figure 2.
  • 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.
  • the sheath 16 and the guide member 17 present a smooth profile when adjacent to one another in the retracted 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.
  • 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.
  • r has a value in the range of 2-4 mm.
  • 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.
  • the projections for a large blood vessel 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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 fluoroscopic techniques, as is the guiding catheter.
  • 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.
  • thermography catheter As the thermography catheter is withdrawn inside the artery, the projections automatically adjust their angle following the wall'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.
  • 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.
  • Figure 4 shows an angiogram image overlaid with a temperature profile from the thermography catheter.
  • an angiogram of the region is taken.
  • the user studies the angiographic image and determines which area is of interest and should be investigated further using the thermography catheter.
  • the thermography catheter is then inserted into the vessel and positioned in a start position which is distal to the area of interest.
  • An angiogram is taken with the catheter in the start position and this position is marked as B on the image.
  • the user determines the distance over which the thermography readings should be taken, depending on the length of the area of interest, and programs the pullback device to pullback the catheter a certain distance accordingly.
  • a second angiogram is taken after the pullback and the position of the catheter is marked on the image as E, the end position.
  • 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.

Abstract

La présente invention concerne un appareil de cathéter pour la mesure de température de tissu vasculaire, comprenant un corps flexible, au moins une saillie polarisée de façon résiliente et dépendant du corps, un capteur porté par la saillie et un porteur électrique destiné à transmettre des données des capteurs à un dispositif distant, le capteur étant encapsulé dans une couche de verre.
PCT/GB2006/003798 2005-10-12 2006-10-12 Dispositif de mesure de température vasculaire WO2007042819A1 (fr)

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US72596405P 2005-10-12 2005-10-12
US60/725,964 2005-10-12

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Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5124682A (en) * 1989-06-27 1992-06-23 Ngk Insulators, Ltd. Detecting element
EP1281350A1 (fr) * 2001-08-01 2003-02-05 NV Thermocore Medical Systems SA Dispositif de mesure de la température vasculaire
US20040068311A1 (en) * 1998-03-24 2004-04-08 Dobak John D. Selective organ cooling catheter with guidewire apparatus and temperature-monitoring device
US20040260197A1 (en) 2001-08-01 2004-12-23 Fox Stewart M. Biased vascular temperature measuring device

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5124682A (en) * 1989-06-27 1992-06-23 Ngk Insulators, Ltd. Detecting element
US20040068311A1 (en) * 1998-03-24 2004-04-08 Dobak John D. Selective organ cooling catheter with guidewire apparatus and temperature-monitoring device
EP1281350A1 (fr) * 2001-08-01 2003-02-05 NV Thermocore Medical Systems SA Dispositif de mesure de la température vasculaire
US20040260197A1 (en) 2001-08-01 2004-12-23 Fox Stewart M. Biased vascular temperature measuring device

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
ANONYMOUS: "Miniature Axial Glass (GA) & Radial Glass (GR) Thermistors", BETATHERM SENSORS TEMPERATURE SOLUTIONS, 12 June 2004 (2004-06-12), XP002385221, Retrieved from the Internet <URL:http://web.archive.org/web/20040612235749/www.betatherm.com/datasheets/PC351.php?pc_num=PC351&p_id=115&override=true> [retrieved on 20060614] *

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