US20110066047A1 - Eccentric pressure catheter with guidewire compatibility - Google Patents
Eccentric pressure catheter with guidewire compatibility Download PDFInfo
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- US20110066047A1 US20110066047A1 US12/994,334 US99433410A US2011066047A1 US 20110066047 A1 US20110066047 A1 US 20110066047A1 US 99433410 A US99433410 A US 99433410A US 2011066047 A1 US2011066047 A1 US 2011066047A1
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- sensor
- catheter
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- catheter device
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- 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
- A61B5/021—Measuring pressure in heart or blood vessels
- A61B5/0215—Measuring pressure in heart or blood vessels by means inserted into the body
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M2025/0001—Catheters; Hollow probes for pressure measurement
- A61M2025/0002—Catheters; Hollow probes for pressure measurement with a pressure sensor at the distal end
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M2025/0004—Catheters; Hollow probes having two or more concentrically arranged tubes for forming a concentric catheter system
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M2025/0183—Rapid exchange or monorail catheters
Abstract
There is herein described a catheter for measuring a pressure in a cardiovascular system. The catheter comprises: a guiding tube adapted for insertion into the cardiovascular system. The guiding tube defines a lumen for sliding a guidewire therethrough. The catheter further comprises a tip pressure sensor eccentrically mounted relative to the guiding tube and a signal communication means extending therefrom. The tip pressure sensor is for sensing a pressure in the cardiovascular system and the signal communicating means is for transmitting a signal indicative of the pressure to a processing device in order to obtain a pressure measurement reading.
Description
- The present application claims priority of U.S.
provisional application 61/160,933 filed Mar. 17, 2009 and entitled “ECCENTRIC PRESSURE CATHETER WITH GUIDEWIRE COMPATIBILITY”, the content of which is incorporated herein by reference. - The field of this disclosure relates to catheters for use in the cardiovascular system to measure pressure. More specifically, the present disclosure relates to catheter devices having the capability to be used in conjunction, and be compatible, with standard guidewire assemblies.
- Pressure measurement guidewires have been in existence since at least the last ten years. These guidewires are most commonly used to measure pressures distal to a lesion, most commonly in the coronary vasculature. By calculating the ratio between the measured pressure distal to the lesion and some point more proximal, most commonly in the ascending aorta or the coronary tree root, the fractional flow reserve (FFR) is obtained. The FFR is now commonly used to assess the degree of lesion stenosis and thereby informs the physician as to the most appropriate treatment strategy. Recently there has been greater clinical acceptance of the importance of measuring translesional pressure gradients and calculating FFR prior to deciding whether to place a stent. As detailed in Pips et al. “Percutaneous Coronary Intervention of Functionally Nonsignificant Stenosis 5-Year Follow-Up of the DEFER Study.” J Am Coll Cardiol (2007) vol. 49 (21) pp. 2105-2111, which is hereby incorporated by reference, stenting a vessel with an FFR greater or equal to 0.75 does not lead to better outcomes compared to non stenting. Another recent study detailed in Fearon et al. “Rationale and design of the fractional flow reserve versus angiography for multi-vessel evaluation (FAME) study.” American Heart Journal (2007) vol. 154 (4) pp. 632-636, which is also hereby incorporated by reference, a multi-center multi-lesion disease, had a similar conclusion suggesting that not stenting an FFR greater or equal to 0.80 lesion leads to better outcomes. It is expected that FFR will soon become the standard of care to document lesion gradient and determine whether a stent is appropriate.
- A common method of measuring the pressure distal to the lesion is through the use of a specialized guidewire with pressure sensors mounted in the guidewire. This is exemplified by the devices described in U.S. Pat. Nos. 6,167,763; 6,112,598 and 6,565,514. These types of devices are now commonly used in coronary vasculature, although their use is not limited to the coronary arteries and they could be used in other vessels of the body. These guidewires serve a double function of pressure measurement to obtain FFR, while at the same time, are used in a fashion similar to standard guidewires, to deliver balloon angioplasty and/or stent therapeutic devices to the diseased plaque location.
- Because of this double function, the pressure measuring guidewires necessarily have a more complex construction than standard guidewires used in percutaneous coronary interventions to guide therapeutic devices to the coronary tree. Because of this more complex construction, current guidewires with an embedded pressure sensor have handling and other characteristics which are sub optimal. With the constraints for receiving a pressure sensor such as the use of hollow tubing, the design of a guidewire with adequate handling characteristics leads to limited performances. They have inferior lesion crossing characteristics, are more difficult to place in position and have inferior pushability and torquability characteristics. Physicians accept these inferior handling characteristics as the necessary compromise in order to be able to perform pressure measurements and FFR calculations with the same guidewire used to deliver stent and balloon devices.
- Accordingly a need exists for an improved pressure measurement catheter to measure FFR while allowing the physician to use a standard guidewire with optimal handling characteristics.
- To be adaptable to standard off-the-shelf guidewires, the proposed device has a catheter with a pressure sensor eccentrically mounted relative to the longitudinal axis of the guidewire to measure the pressure distal to the lesion. The proposed pressure measuring catheter is designed, in one embodiment, as a ‘rapid exchange’ catheter. In other embodiments, or additionally, it is designed to function similarly to a monorail, in order to be advanced and guided to a working location using a standard guidewire. By placing the pressure sensor within a catheter and separating the guidewire functions from the pressure measuring functions, a physician can perform FFR while at the same time use his/her preferred guidewire. This solution removes the need to compromise between guidewire performance and the ability to perform FFR. The diameter of the proposed catheter that stands within the lesion while performing FFR is minimal, thereby minimizing additional pressure drop across lesion.
- In accordance with an embodiment, there is provided a catheter for measuring a pressure in a cardiovascular system. The catheter comprises: a guiding tube adapted for insertion into the cardiovascular system. The guiding tube defines a lumen for sliding a guidewire therethrough. The catheter further comprises a tip pressure sensor eccentrically mounted relative to the guiding tube and a signal communication means extending therefrom. The tip pressure sensor is for sensing a pressure in the cardiovascular system and the signal communicating means is for transmitting a signal indicative of the pressure to a processing device in order to obtain a pressure measurement reading.
- Further features and advantages of the present invention will become apparent from the following detailed description, taken in combination with the appended drawings which are meant to be exemplary only, in which:
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FIG. 1 is a schematic view of a catheter device in accordance with an embodiment; -
FIG. 2 is a partial perspective schematic view of a distal portion of the catheter device ofFIG. 1 , in accordance with an embodiment; -
FIG. 3 is a cross sectional view of the distal portion ofFIG. 2 , taken along line 3-3; -
FIG. 4 is a longitudinal cross sectional view of the distal portion ofFIG. 2 , taken along line 4-4; -
FIG. 5 is a schematic view of a catheter device in accordance with an embodiment where the distal portion has a reduced catheter section; -
FIG. 6 is a perspective schematic view of the distal portion ofFIG. 5 , in accordance with a first example; -
FIG. 7 is a longitudinal cross sectional view of the distal portion ofFIG. 6 , taken along lines 7-7; -
FIG. 8 is a perspective schematic view of the distal portion ofFIG. 5 , in accordance with a second example; -
FIG. 9 is a perspective schematic view of distal portion ofFIG. 5 , in accordance with a third example. - The proposed concept is a stand-alone eccentric pressure catheter device which can be universally used with a readily available guidewire. If the pressure sensor is small enough, it is possible to mount the sensor eccentrically relative to the guidewire while keeping the ability to cross a lesion and assess FFR.
- Referring to
FIG. 1 , there is shown a first embodiment of acatheter device 80 defining adistal portion 81 for insertion into a cardiovascular system, and aproximal portion 95 extending outside patient body for transmitting mechanical force and relaying pressure measurements information. - A
catheter tip assembly 22 is at thedistal portion 81 of thecatheter device 80. Thecatheter tip assembly 22 comprises asensor 16. Thepressure sensor 16 is mounted to the side wall or anywhere other than the geometrical centre (i.e. eccentrically) of a guidingtube 3. Thecatheter tip assembly 22 comprises apressure sensor 16 and a communication means 17 (e.g., an optical fiber) for communication with aprocessing device 7. - In this first illustrated embodiment, the
guiding tube 3 is a hollow tubing with a lumen extending along at least a portion of its length. The lumen is used for entering aguidewire 25 therethrough. The length of the guidingtube 3 in this case defines a distal section A of thecatheter device 80 which is representative of thedistal portion 81. - The guiding
tube 3 is slid over and guided by aguidewire 25 which enters the lumen (not numbered) of the guidingtube 3. Theguidewire 25 then exits the guidingtube 3 from thefirst opening 8 located at guiding tubeproximal end 12 which is in one embodiment, approximately 30 to 40 cm fromdistal end 6 of theguiding tube 3, illustrated as section A. Section A thus extends from thedistal end 6 to aproximal end 12 atfirst opening 8. The guidingtube 3 has as small a diameter as possible while still delivering a minimum pushability and accommodating the guidewire within the lumen. - In one embodiment, the guiding
tube 3 is a relatively soft tubing having a length of about 20 to 30 cm long so as to slide over theguidewire 25. - Still referring to
FIG. 1 , and by way of a non limiting example, the guidingtube 3 is made of polyimide tubing with an inner diameter (ID) of about 0.016″ and outer diameter (OD) of about 0.018″. Alternatively, a braided polyimide tubing with an ID of about 0.016″ and OD of about 0.021″ is used to provide additional pushability and resistance to kinking. - In the embodiment of
FIG. 1 , section B of thecatheter device 80 as shown inFIG. 1 , extends from theproximal end 12 at opening 8 of section A. Section B provides the pushability required to push section A at a lesion site and further through it. Section B has atubing 4 which is made, in one embodiment, of a stainless steel hypo-tube with an outer diameter of about 0.024″ and an inner diameter of about 0.016″. In one instance, the length of thetubing 4 is of the order of 100 cm. Section B is illustrated in this embodiment as aproximal portion 95 of thedevice 80. - In an embodiment where the
tubing 4 is a hypo-tube, such hypo-tube is spliced to the guidingtube 3 in different ways. In any case, a connectingdevice 40 that connects in between the guidingtube 3 and thetubing 4 can also be used. The connectingdevice 40 can also serve to provide anopening 8 for theguidewire 25 to exit the guidingtube 3 distally of thetubing 4, as well as anotheropening 9 used to enter a signal communication means 17 such as a lead wire or an optical fiber into thetubing 4. - The communication means 17 brings the signal from the
tip pressure sensor 16 located on distal end of guidingtube 3 in this example, to aprocessing device 7 located remotely to the catheter. - In one embodiment such as in
FIG. 1 , the signal communicating means 17 has a flexible cable jacket 5 and is connected to aproximal end 13 of thetubing 4 and serves to protect and route the communication means 17 to theprocessing device 7 after the communication means 17 exits thetubing 4. In this specific case, the communication means 17 runs on the surface of the guidingtube 3, and is secured with an overlay of PET heat shrinkable material, from an exit at thesensor 16 to the entrance oropening 9 into thetubing 4. - Still in reference to the
catheter device 80 ofFIG. 1 , it is understood that thesensor 16 can be any type of sensor small enough to enter into a stenosis region of a vessel, such as fiber optic sensors based on a Fabry-Perot cavity or any other kind of optical sensing mechanism, or piezo-electric sensors. In addition, more than one sensor can be used on a single catheter device. Thesensor 16 is adapted to measure a pressure and generate a signal indicative of the pressure which is then sent through the communicatingmeans 17. The signal and the characteristics of the communicatingmeans 17 are thus either electrical or optical in nature depending on the sensor used. - Still in reference to
FIG. 1 , theprocessing device 7 comprises in one embodiment a signal conditioning means for formatting the signal received from the sensor to obtain a pressure measurement reading adapted to a specific need or given situation useful to a user. In one case, for example, the processing device is implemented to generate a fractional flow reserve (FFR) of a vascular lesion and/or a pressure gradient measurement across a cardiac valve, based on the pressure measurement reading. - Pressure sensors are devices responsive to very small blood pressure changes; they are thus sensitive devices. In order to deliver high fidelity pressure measurements, it is helpful to isolate the sensor device from unwanted parasitic mechanical stresses.
- In reference to
FIG. 2 , which shows a portion of distal portion 81 (also referred to as the catheter tip assembly) of thecatheter device 80 ofFIG. 1 , there is also illustrated an example of aprotective housing 60 mounted on a wall of thecatheter device 80. Thehousing 60 is designed to have specific characteristics which are dependent on the nature of thesensor 16. - The
protective housing 60 shown inFIG. 2 accommodates and protects thetip pressure sensor 16 against undesired mechanical stresses for example. In one embodiment, a thin metal sheet is formed to provide aprotective shell 14 to thesensor 16. There is provided in the shell 14 a window 15 (also referred to as an opening) which permits thesensor 16 to sense a pressure in its environment (also referred to as its vicinity). - Once the
sensor 16 is well secured in theprotective shell 14, theshell 14 withsensor 16, is mounted on a wall of the guidingtube 3. Theshell 14 is secured on the wall of guidingtube 3 using an adhesive material such as an epoxy. In one embodiment, it is also covered with an overlay made of a polymer such as polyester (PET) heat shrink having a wall that is as thin as about 0.0005″. Alternatively to a thermoplastic or PET heat shrink, any non toxic tubing material which shrinks in size under given conditions is used. - Because catheters need to be pushed in very tortuous vessel paths and against very narrow lesions, it is desirable to further improve the mechanical stability of the sensor. In one embodiment, the
shell 14 is mounted on astiff tube 10 such as a thin wall metal tube of about 0.016″ ID. In some instances, theshell 14 is bonded to thestiffer tubing 10 with an epoxy, or welded with a laser or other welding method. - The guiding
tube 3 in this example essentially comprises a section of astiffer tube 10. In some cases, it is desirable to provide the guidingtube 3 by enlarging an inner diameter of the distal end offirst tubing 3, fitting and bonding thefirst tubing 3 over the proximal end of thestiffer tube 10, and fitting and bonding a soft atraumatic section oftubing 11, as best seen inFIG. 2 . -
FIG. 3 shows a transversal cross section ofcatheter tip assembly 22, through thesensor 16, taken along line 3-3 ofFIG. 2 . It is shown that it is possible to further reduce the size of the catheter tip diameter by machining a flat 24 on the surface of thetube 10, and bringing thesensor 16 closer to the center of the tube on which it sits. Theguidewire 25 is shown going through thetube 10. -
FIG. 4 shows a longitudinal cross section of the catheter tip seen inFIG. 2 . Thesensor 16 is held in place by bonding the communication means 17, such as an optical fiber, near thesensor 16 with an adhesive 21, such as epoxy. Thetip pressure sensor 16 may be protected by a thin layer of soft silicone or silicone gel. Thevolume 20 in theshell 14 opposite to thesensor 16 head can be filled with a polymer to minimize the void under theshell 14, hence minimizing the risk of trapping too large an air bubble. Thewindow 15 adjacent to thesensor 16, at its diaphragm, is left open to permit blood pressure transmission to thetip pressure sensor 16 for pressure sensing.Window 15 can also be filled with silicone gel or silicone oil. If filled with silicone oil, a barrier, such as a thin polymer film or thin layer of silicone, is used to contain the oil in thewindow 15. AlthoughFIG. 4 shows the guidingtube 3 butted directly against thestiffer tube 10, such a tubing can alternatively be fitted over thestiffer tube 10 to form the guidingtube 3. The same applies for theatraumatic tubing 11. - As previously stated, the guiding
tube 3 can be adapted to provide a certain level of pushability and kink resistance suitable to perform as desired. Constraints on kink resistance and pushability may require the use of braided polyimide tubing. For example, with a minimum wall thickness for polyimide braided tubing in the order of 0.0025″, the diameter of the guidingtube 3 is set at about 0.021″. With these characteristics, the section area of such tubing is thus about 225% the section of a 0.014″ guidewire. Such a larger section may cause a pressure drop not related to the stenosis and hence, FFR measurement may differ from one otherwise obtained with a differently sized guidewire such as a 0.014″ guidewire mounted with a pressure sensor. -
FIG. 5 illustrates another embodiment for acatheter device 84 similar to thedevice 80 ofFIG. 1 , but designed to further minimize the sectional size of the portion of the catheter standing across the stenosis while performing. While performing FFR, thecatheter tip 22 is located some 2 to 3 cm distally to the lesion and therefore, hypo-tube 51 is the portion of the catheter standing across the stenosis while performing FFR. This section of the catheter needs to be kept to the smallest possible diameter. - The guiding tube 54 in which the
guidewire 57 slides through is significantly reduced in length compared to the embodiment ofFIG. 1 . Theguidewire 57 enters intodistal end 55 of the guiding tube 54 and exits from a guiding tubeproximal end 56. By way of non limiting example, the length of the guiding tube 54 can be as short as about 1 to 2 cm. - The
sensor 16 is eccentrically positioned relative to guiding tube 54. The distal end of first hypo-tube 51 is eccentrically mounted to a wall of the guiding tube 54 and concentrically mounted within sensor housing 60 (seeFIG. 6 ), using a laser welding or other available welding methods. For example, the first hypo-tube 51 has an outside diameter of about 0.009″ and an inner diameter of about 0.005″. The total obstructive section area of both guidewire and pressure catheter across lesion under scrutiny is given by the addition of 0.014″guidewire 57 and 0.009″ hypo-tube 51, both running in parallel. The section area is thus kept to no more than approximately 140% the section of the 0.014″ guidewire 57 section area alone. - In one embodiment,
proximal end 53 of first hypo-tube 51 is connected to the distal end of second hypo-tube 52, by sliding theproximal end 53 of thetubing 51 into the distal end of thesecond tubing 52. This connection is in some cases secured by laser welding, friction welding and/or bonding with adhesive. By way of non limiting example, the length of the first hypo-tube 51 is about 20 to 30 cm long. The communication means 17 that connects thesensor 16 to thesignal conditioner 7 is guided through both first hypo-tube 51 and second hypo-tube 52. Once exiting the second hypo-tube 52, the communication means 17 goes through a cable jacket 5. -
FIG. 6 shows a schematic of one first embodiment for the distal portion 22 (i.e., the catheter tip assembly) of thecatheter device 84 ofFIG. 5 . -
Sensor housing 60 is for the protection oftip pressure sensor 16, such as a fiber optic pressure sensor. In this embodiment, the diameter ofsensor housing 60 is of about 0.012″ or less. Thedistal end 61 of the housing (also referred to as a protective shell) 60 protecting thesensor 16 has a form that makes thesensor housing 60 smooth for the wall of blood vessel. Theproximal end 62 of thehousing 60 has a circular shape to accommodate the first hypo-tube 51. First hypo-tube 51 can be bonded or welded to one or both thehousing 60 andmetal tube 65. Awindow 66 is also provided to let the blood pressure transmission to thesensor 16 or permit the sensor to sense the blood pressure from the blood entering thewindow 66. Both ends ofmetal tube 65 are connected to softatraumatic tubings -
FIG. 7 shows a longitudinal cross section of the catheter tip assembly 58 as shown inFIG. 6 . In this embodiment, the communication means 17, here an optical fiber goes through the first hypo-tube 51. To keep the section of the tip of thecatheter device 84 at the location of thesensor 16 as small as possible, themetal tube 65 has aflat surface 72. First hypo-tube 51 also has a flattenedsurface 71 to bring thesensor 16 down withinflat surface 72 provided on themetal tube 65. - Still referring to the
catheter tip assembly 22 as illustrated inFIG. 7 , it is noted that a longerflat surface 72 can alternatively be provided on themetal tube 65 so as to avoid having a flattenedsurface 71 on the first hypo-tube 51. The cross section of thecatheter device 84 at thesensor 16 can be further reduced by thinning thehousing 60 in theregion 74 wheretip pressure sensor 16 and first hypo-tube 51 are positioned. As illustrated inFIGS. 1 to 4 in reference to thewindow 15, thewindow 66 can be left open, filled with a soft silicone, a silicone gel or silicone oil. - Relatively long portion of stiff guiding tube 65 (
FIG. 6 ), is compromising good trackability of the catheter over guidewire as it has the effect of forcing the guidewire to locally straighten while tracking over. Also, manufacturability of sensor housing shell illustrated in sameFIG. 6 can be improved by replacing with cylindrical tubing.FIG. 8 shows a schematic of such another embodiment for thecatheter tip assembly 22 of thecatheter device 84. - In this embodiment, the
sensor housing 60 comprises a cylindrical tube connected directly to the distal end of the hypo-tube 51. The inner diameter of thesensor housing 60 accommodates the diameter of thesensor 16. By way of non limiting example, thesensor housing 60 has an ID and an OD of the order of respectively 0.010″ and 0.012″. - The signal communication means 17 for transmitting pressure information from
tip pressure sensor 16 travels through the hypo-tube 51 and also the hypo-tube 52 (shown inFIG. 5 ). - The
sensor housing 60 is here provided with onewindow 76 or multiple windows (not shown) for allowing blood pressure to be transmitted to thetip pressure sensor 16. - In the illustrated embodiment, a short ring-shaped device such as a
metal ring 94 is welded to a surface of thesensor housing 60. Themetal ring 94 is used to hold in place the guidingtube 73 accommodating theguidewire 57, eccentric with respect to thetip pressure sensor 16, itshousing 60 and appendedtubing 51. Theguidewire 57 enters from guiding tubedistal end 78 and exits from guiding tubeproximal end 79. - In one embodiment, the guiding
tube 73 is made of thin soft material in order to minimize a catheter tip diameter, and to provide atraumaticity. This is advantageous, for example, when the catheter is pulled out of blood vessel without being guided by guidewire. - In the illustrated embodiment, the
sensor housing 60 is terminated with a softatraumatic tip 68. Astrain reliever 77 can also be added in some instances to prevent kinking of the hypo-tube 51 connecting tostiffer sensor housing 60. - By way of a non-limiting example, the guiding
tube 73 is made of a material such as Teflon™, soft Pebax™ or other similar materials. Similarly,sensor housing 60 andring 94 are made using for example stainless steel, nitinol, cobalt-chrome material or any other similar materials. Hypo-tube 51 is also preferably made of full hard stainless steel, Nitinol, Cobalt-chromium or other high yield strength materials. - Securing the guiding
tube 73 to stiff sensor housing still compromise trackability of the catheter by locally deforming the guidewire while tracking over. Also, securing the guidingtube 73 directly to sensor housing by way ofring 94 results into a non optimal diameter. -
FIG. 9 shows a schematic of yet another embodiment for thecatheter tip assembly 22 ofcatheter device 84. In accordance with one embodiment, this illustrated construction provides a smaller catheter tip diameter compared to the examples illustrated hereinabove, while also providing good flexibility with regard to the optimization of the stiffness of the guidingtube section 85 and therefore, a better trackability. - In the illustrated case, the
catheter tip assembly 22 main components include thesensor housing 60,core member 83 connected to sensor housing and extending forward, and guidingtube 85 which again is eccentrically mounted onto a wall ofcore member 83 and therefore, eccentric to tippressure sensor 16. -
Sensor housing 60 is made out of a cylindrical tube connected directly to the distal end of first hypo-tube 51. Thesensor housing 60 is provided with one ormultiple windows 90 for allowing blood pressure to be transmitted to thetip pressure sensor 16. - The inner diameter of the
sensor housing 60 shall accommodate the diameter of thesensor 16. By way of non limiting example, the sensor housing ID and OD can be respectively of 0.010″ and 0.012″. - The signal communicating means (not shown) for transmitting pressure information signal from
tip pressure sensor 16 travels though first hypo-tube 51 and second hypo-tube 52 (not shown). - In this example, the
core member 83 is provided and extends distally to thesensor housing 60. In one embodiment, thecore member 83 is tapered in various ways in order to optimize the stiffness of the guidingtube 85 section. In a specific example, core member can be tapered uniformly from 0.008″ down to 0.003″. The core diameter can also be tapered according to diameter step reduction. - In one example, the
core member 83 is made of a hard material with high yield strength for providing desired flexibility such as tempered stainless steel. - Different schemes can be used to attach the guiding
tube 85 to thecore member 83. One fabrication method consists of shrinking or reflow apolymer tube 92 aroundcore member 83, followed by a reflow process where the guidingtube 85 is fused to thepolymer tube 92. In one example, thepolymer tube 92 and the guidingtube 85 materials are materials such as Teflon™, Pebax™ and the like. Guidingtube 85 can also include a liner for lowering friction with guidewire (not shown). - In one embodiment, the length of the guiding
tube 85 is kept short enough to minimize the overallcatheter tip portion 22 extending distally to tippressure sensor 16. By way of non limiting example, such a length is kept at about 15 mm. - In one embodiment, atraumaticity conditions are kept by having a
distal end 87 of the guidingtube 85 extend forwardly relative to atip 88 ofcore member 83. - In one embodiment, the
distal end 87 of the guidingtube 85 is tapered still to address atraumaticity purposes. - Still referring to
FIG. 9 , in one embodiment, thetip pressure sensor 16 is provided within the tubing formed by hypo-tube 51, to form a microcatheter. An attachment means such as a short monorail formed bypolymer tube 92 is attached to the distal end ofcore member 83 in order to attach thecore member 83 to the guidingtube 85. - The above-described catheter device could easily be extended to other guidewire sizes (i.e. 0.010″, 0.014″, 018″, 0.035″ and 0.038″). In addition, all of the above mentioned length specifications, tubing characteristics, guidewire sizes, diameters, wall thicknesses and percentages can be varied depending on the specific implementation and desired specifications.
- The procedural steps to be taken for measuring a fractional flow reserve (FFR) using the proposed device are described below:
- 1) The distal end of a guiding catheter is advanced in the aorta and positioned nearby the ostium of the coronary. A fluid filled pressure sensor is connected to the proximal end of the guiding catheter and serves for measuring aortic pressure.
- 2) A conventional guidewire is then inserted into the guiding catheter and advanced through the stenosis where FFR is to be assessed.
- 3) The proposed eccentric catheter device is then advanced into the ascending aorta, guided by the guidewire, and positioned near the distal end of the guiding catheter so as to measure the aortic pressure.
- 4) The pressure taken by the eccentric catheter device's sensor at the distal end thereof, and the pressure taken by the external fluid filled pressure sensor are equalized.
- 5) The eccentric catheter is then advanced to cross the lesion. In one embodiment, this step involves locating the pressure sensor some 20 mm further than the lesion.
- 6) The FFR is then obtained by dividing the pressure distal to the lesion which is measured using the eccentric catheter device's sensor, by the aortic pressure measured using the fluid filled pressure sensor connected at the proximal end of the catheter device (i.e. FFR=lesional distal pressure/aortic pressure).
- 7) The eccentric catheter device is removed.
- 8) A balloon or stent is then optionally advanced to the lesion, depending on the circumstances specific to a given procedure.
- The above method for assessing FFR also optionally involves a step of vasodilating the vessels prior to taking the pressure measurement distal to the lesion (i.e. prior to taking a pressure measurement reading using the sensor on the distal end of the catheter device).
- The use of the above-described eccentric catheter device is not limited to coronary applications and can be adapted to perform other pressure gradient or ratio measurements such as but not limited to:
- across valves to measure transvalvular pressure gradient,
- peripheral (renal, femoral, iliac, tibial) pressure gradient.
- In some instances, the catheter device herein proposed is used in the coronary tree to measure coronary FFR. The device can however be adapted to measure pressure gradients or ratio anywhere in the vasculature, such as inside the heart during minimally invasive heart valve surgery, or as a diagnostic tool to measure transvalvular gradient. The catheter may have a single pressure sensor, two or multiple pressure sensors to measure a variety of gradients.
- In accordance with one embodiment, the above-described device has a pressure sensor corresponding to a fiber optic sensor which converts a pressure into a spectrally encoded light signal representative of the pressure exerted on the sensor. A variety of other types of pressure sensors can however be used, such as and not limited to, piezoelectric transducers or any other miniature tip pressure sensing devices.
- In order to increase sensor fidelity, in one embodiment, the sensing device is packaged on a section of tubing which has an increased stiffness allowing for the support of the sensor at that location.
- In accordance with still another embodiment, the length of tubing (hereinabove referred to
tubing 3 inFIG. 1 , and 54 inFIG. 5 ) sliding over the guidewire (25 inFIG. 1 and 57 inFIG. 5 ) is reduced to provide a diminished section of the overall catheter device in a stenosis area while performing the FFR measurement. - While preferred and exemplary embodiments have been described above and illustrated in the accompanying drawings, it will be evident to those skilled in the art that modifications may be made therein without departing from the essence of the present description. Such modifications are considered as possible variants comprised in the scope of the present invention.
Claims (14)
1. A catheter for measuring a pressure in a cardiovascular system, the catheter comprising:
a guiding tube adapted for insertion into the cardiovascular system, the guiding tube defining a lumen for sliding a guidewire therethrough;
a tip pressure sensor eccentrically mounted relative to the guiding tube, the tip pressure sensor for sensing a pressure in the cardiovascular system; and
a signal communicating means extending from the tip pressure sensor and being for transmitting a signal indicative of the pressure to a processing device in order to obtain a pressure measurement reading.
2. The catheter device of claim 1 , wherein the tip pressure sensor forms part of a catheter tip assembly which further comprises a core member on which is mounted the guiding tube.
3. The catheter device of claim 2 , wherein the catheter tip assembly further comprises a housing on which is mounted a core member, the housing holding the sensor.
4. The catheter device of claim 3 , wherein the housing comprises a window for allowing blood pressure to be transmitted to the sensor.
5. The catheter device of claim 3 , wherein the catheter tip assembly connects to a miniature hypo-tube of diameter smaller than or equal to 0.010″ within which the sensor communication means goes through.
6. The catheter device of claim 5 , further comprising another larger hypo-tube connecting to miniature hypo-tube for providing adequate pushability and within which the sensor communication means still goes through.
7. The catheter device of claim 2 , wherein the core member diameter is tapered or reduced in step.
8. The catheter device of claim 1 , comprising a ring-shaped device for holding therein at least a portion of respectively: the tip pressure sensor and the guiding tube.
9. The catheter device of claim 1 , further comprising the processing device to which is transmitted the signal indicative of the pressure.
10. The catheter device of claim 1 , wherein the processing device calculates the fractional flow reserve (FFR) of a vascular lesion based on the pressure measurement reading.
11. The catheter device of claim 1 , wherein the signal communication means comprises an optical fiber.
12. The catheter device of claim 1 , wherein the sensor comprises a fiber optic sensor, and wherein the signal is an optical signal.
13. The catheter device of claim 1 , wherein the signal communication means comprises an electrical wire.
14. The catheter device of claim 1 , wherein the sensor comprises a piezo-electric sensor, and wherein the signal is an electrical signal.
Priority Applications (1)
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US12/994,334 US20110066047A1 (en) | 2009-03-17 | 2010-03-17 | Eccentric pressure catheter with guidewire compatibility |
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US12/994,334 US20110066047A1 (en) | 2009-03-17 | 2010-03-17 | Eccentric pressure catheter with guidewire compatibility |
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EP (1) | EP2408356B1 (en) |
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Also Published As
Publication number | Publication date |
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CA2721282A1 (en) | 2010-09-23 |
EP2408356A4 (en) | 2013-07-31 |
JP5591906B2 (en) | 2014-09-17 |
CA2721282C (en) | 2011-10-11 |
EP2408356A1 (en) | 2012-01-25 |
US8317715B2 (en) | 2012-11-27 |
EP2408356B1 (en) | 2018-05-23 |
JP2012520690A (en) | 2012-09-10 |
WO2010105356A1 (en) | 2010-09-23 |
US20100241008A1 (en) | 2010-09-23 |
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