CA2198909A1 - Ultra miniature pressure sensor and guidewire using the same and method - Google Patents
Ultra miniature pressure sensor and guidewire using the same and methodInfo
- Publication number
- CA2198909A1 CA2198909A1 CA002198909A CA2198909A CA2198909A1 CA 2198909 A1 CA2198909 A1 CA 2198909A1 CA 002198909 A CA002198909 A CA 002198909A CA 2198909 A CA2198909 A CA 2198909A CA 2198909 A1 CA2198909 A1 CA 2198909A1
- Authority
- CA
- Canada
- Prior art keywords
- guidewire
- pressure
- housing
- distal
- diaphragm
- Prior art date
- Legal status (The legal status 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 status listed.)
- Abandoned
Links
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
- G01L19/00—Details of, or accessories for, apparatus for measuring steady or quasi-steady pressure of a fluent medium insofar as such details or accessories are not special to particular types of pressure gauges
- G01L19/14—Housings
- G01L19/141—Monolithic housings, e.g. molded or one-piece housings
-
- 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
- A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
- A61B5/6851—Guide wires
-
- 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
- A61M25/09—Guide wires
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
- G01L19/00—Details of, or accessories for, apparatus for measuring steady or quasi-steady pressure of a fluent medium insofar as such details or accessories are not special to particular types of pressure gauges
- G01L19/0061—Electrical connection means
- G01L19/0084—Electrical connection means to the outside of the housing
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
- G01L19/00—Details of, or accessories for, apparatus for measuring steady or quasi-steady pressure of a fluent medium insofar as such details or accessories are not special to particular types of pressure gauges
- G01L19/14—Housings
- G01L19/147—Details about the mounting of the sensor to support or covering means
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
- G01L19/00—Details of, or accessories for, apparatus for measuring steady or quasi-steady pressure of a fluent medium insofar as such details or accessories are not special to particular types of pressure gauges
- G01L19/14—Housings
- G01L19/149—Housings of immersion sensor, e.g. where the sensor is immersed in the measuring medium or for in vivo measurements, e.g. by using catheter tips
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
- G01L9/00—Measuring steady of quasi-steady pressure of fluid or fluent solid material by electric or magnetic pressure-sensitive elements; Transmitting or indicating the displacement of mechanical pressure-sensitive elements, used to measure the steady or quasi-steady pressure of a fluid or fluent solid material, by electric or magnetic means
- G01L9/0041—Transmitting or indicating the displacement of flexible diaphragms
- G01L9/0051—Transmitting or indicating the displacement of flexible diaphragms using variations in ohmic resistance
- G01L9/0052—Transmitting or indicating the displacement of flexible diaphragms using variations in ohmic resistance of piezoresistive elements
- G01L9/0054—Transmitting or indicating the displacement of flexible diaphragms using variations in ohmic resistance of piezoresistive elements integral with a semiconducting diaphragm
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/06—Measuring blood flow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
-
- 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
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/09—Guide wires
- A61M2025/09008—Guide wires having a balloon
-
- 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
- A61M25/09—Guide wires
- A61M2025/09058—Basic structures of guide wires
- A61M2025/09083—Basic structures of guide wires having a coil around a core
-
- 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
- A61M25/10—Balloon catheters
Abstract
This invention is a guidewire (21) having pressure sensing capabilities for measuring pressure of a liquid in a vessel comprising a flexible elongate member (41) and having proximal (42) and distal (43) extremities, and having an outside diameter of 0.018'' or less. The distal extremity of said flexible elongate member (41) is adapted to be disposed in the liquid in said vessel. A
housing (51) is carried by the flexible elongate member (41) and has a diameter substantially the same as the diameter of the flexible elongate member (41). The housing (51) has a space therein with a pressure sensor (76) mounted in the housing space in the housing. The pressure sensor (76) has a diaphragm (79) formed in a crystal (77) of semiconductor material, that is sensitive to changes in pressure of the liquid in the vessel. The diaphragm (79) is rectangular in shape and is mounted in a well (84), and is bordered by a rim (86) surrounding the well (84). A backing plate (78) is formed of an insulating material bonded to the crystal (77) and serves to reinforce the rim (86) of the crystal (77). The backing plate (78) has a cavity (101) therein underlying the diaphragm and is in substantial registration with the diaphragm (79). The cavity (101) serves as a pressure reference.
housing (51) is carried by the flexible elongate member (41) and has a diameter substantially the same as the diameter of the flexible elongate member (41). The housing (51) has a space therein with a pressure sensor (76) mounted in the housing space in the housing. The pressure sensor (76) has a diaphragm (79) formed in a crystal (77) of semiconductor material, that is sensitive to changes in pressure of the liquid in the vessel. The diaphragm (79) is rectangular in shape and is mounted in a well (84), and is bordered by a rim (86) surrounding the well (84). A backing plate (78) is formed of an insulating material bonded to the crystal (77) and serves to reinforce the rim (86) of the crystal (77). The backing plate (78) has a cavity (101) therein underlying the diaphragm and is in substantial registration with the diaphragm (79). The cavity (101) serves as a pressure reference.
Description
WO ~/07351 PCT/U~3~ 3~
ULTRA ~TNT~TURE PRESSURE 8ENSOR AND
This inven~ion relates to an ultra miniature pressure sensor and guidewire and apparatus using the same and method, which is particularly suitable for making pressure measurements in coronary arteries of human beings.
It has been well known that it is desirable to make pressure measurements in vessels and particularly in coronary arteries with the advent of angioplasty.
Typically in the past, such pressure measurements have been made by measuring the pressure at a proximal extremity of a lumen provided in a catheter advanced into the coronary artery of interest. However, such an approach has been less efficacious as the diameters of the catheters became smaller with the need to advance the catheter into smaller vessels. This made necessary the use of smaller lumens which gave less accurate pressure measurements and in the smallest catheters necessitated the elimination of such a pressure lumen entirely. In an attempt to overcome these difficulties, ultra miniature pressure sensors have been proposed for use on the distal extremities of catheters. However, it has not been ; feasible prior to the present invention to provide such ultra miniature pressure sensors which are capable of being incorporated in a guidewire for making pressure WO96/07351 PCT/U~3~ 9a -2- 02 1 98 9 og measurements in a very small arterial vessels. There is therefore a need for a new and improved ultra miniature pressure sensor and a guidewire and apparatus utilizing the same.
In general it is an object of the present invention to provide an ultra miniature pressure sensor and guidewire and apparatus utilizing the same making possible pressure and velocity measurements.
Another object of the invention is to provide a sensor which can be utilized on the distal extremity of a guidewire .018" or .014" in diameter.
Another object of the invention is to provide a sensor of the above character which is formed of a silicon chip of a small dimension which is reinforced by an additional member to provide reinforcement for the chip.
Another object of the invention is to provide a sensor of the above character in which a thin diaphragm is formed in the crystalline silicon chip.
Another object of the invention is to provide a sensor of the above character in which the reinforcing member extends for approximately 200 microns beyond the si~icon diaphragm.
Another object of the invention is to provide a guidewire with the above character in which the number of conducting wires required is kept to a minimum.
Another object of the invention is to provide a guidewire and method in which simultaneous pressure and velocity measurements can be made.
Another object of the invention is to provide a guidewire of the above character in which the diaphragm area has been maximized.
Another object of the invention is to provide a guidewire with the above character in which two pressure sensors are provided on the guidewire which are spaced apart so that pressure measurements can be made on both sides of a stenosis.
WOg6/07351 PCT/U'3S~'~9~3~
"~ , ~ -3- 0 2 1 98 909 Another object of the invention is to provide a guidewire of the above character in which the sensors are covered to prevent the formation of blood clots.
Another object of the invention is to provide an apparatus of the above character which includes a guidewire with an integral inflatable balloon.
Another object of the invention is to provide an apparatus of the above character in which temperature compensation can be provided.
Another object of the invention is to provide an apparatus of the above character which can be utilized in a half-bridge configuration.
Additional features and objects of the invention will appear from the following description in which the preferred embo*iments are set forth in detail in conjunction with the accompanying drawings.
Figure 1 is a schematic illustration showing use of a guidewire incorporating a pressure sensor of the present invention and apparatus utilizing the same in conjunction with a patient undergoing a catheterization procedure for diagnosis or treatment.
Figure 2 is a side elevational view of a guidewire incorporating an ultra miniature pressure sensor of the present invention.
Figure 3 is an enlarged side elevational view of the distal extremity of the guidewire shown in Figure 2 and showing the pressure sensor mounted therein.
Figure 4 is a top plan view looking along the line 4-4 of Figure 3.
Figure 5 is a bottom plan view looking along the line 5-5 of Figure 3.
Figure 6 is an isometric view of the pressure sensor shown in Figures 3, 4 and 5 with the lead wires connected thereto.
Figure 7 is a side elevational view of the pressure sensor shown in Figure 6.
WO g6/073~1 P~ 3S~'~9 fi9 8 0 2 1 9 8 9 o 9 Figure 8 is a top plan view of the pressure sensor shown in Figures 6 and 7.
Figure 9 is a cross-sectional view taken along the line 9-9 of Figure 8.
Figure 10 is a cross-sectional view taken along the line 10-10 of Figure 8.
Figure 11 is a cross-sectional view taken along the line 11-11 of Figure 8.
Figure 12, is a schematic diagram of the circuitry utilized in the pressure sensor shown in Figures 6-11.
Figure 13 is a side elevational view of the distal extremity of another guidewire incorporating the pressure sensor with the sensor of the present invention being mollnted in the tip housing.
Figure 14 is a side elevational view of the distal extremity of a guidewire having f irst and second pressure sensors mounted in the distal extremity of the same spaced apart to permit simultaneous measurements of proximal and distal pressures with respect to a stenosis.
Figure 15 is a partial side elevational view of another guidewire incorporating the present invention with an enclosed pressure sensor.
Figure 16 is a side elevational view partially in section of the distal extremity of another guidewire incorporating the present invention in which the pressure sensor is enclosed in a transition housing.
Figure 16A is a side elevational view in section showing an end-mounted pressure sensor incorporating the present invention.
Figure 17 is a side elevational view in section of a guidewire housing a tip-mounted sensor incorporating the present invention with an integral balloon.
In general, the guidewire of the present invention having pressure sensing capabilities is comprised of a flexible elongate element having proximal and distal extremities and having a diameter of .018" and less. The pressure sensor is mounted on the distal extremity of a WO96/07351 PCT~S~ 3~
s 0 2 1 9 8 9 0 9 flexible elongate element. It is comprised of a crystal semiconductor material having a recess therein and forming a diaphragm bordered by a rim. A reinforcing member is bonded to the crystal and reinforces the rim of the crystal and has a cavity therein underlying the diaphragm and exposed to the diaphragm. A resistor having opposite ends is carried by the crystal and has a portion thereof overIying a portion of the diaphragm. Leads are connected to opposite ends of the resistor and extend within the flexible elongate member to the proximal extremity of the flexible elongate member.
More in particular, the guidewire 21 of the present invention having pressure measuring capabilities as shown in Figure 1 is one that is adapted to be used in connection with a patient 22 lying on a table or a bed 23 in a cath lab of a typical hospital in which a catheterization procedure such as for diagnosis or treatment is being performed on the patient. The guidewire 21 is used with apparatus 24 which consists of a cable 26 which connects the guidewire 21 to an interface box 27. Interface box 27 is connected by another cable 28 to a control console 29 which has incorporated as a part thereof a video screen 31 on which a waveform 32 displaying ECG measurements may be provided as well as two traces 33 and 34 displaying pressure measurements being made by the guidewire 21.
The guidewire 21 is shown more in detail in Figure 2 and as shown therein, the guidewire 21 can be constructed utilizing the various constructions as shown in Patent Nos. 5,125,137; 5,163,445; 5,178,159; 5,226,421; and 5,240,437. As disclosed therein, such a guidewire consists of a flexible elongate element 41 having a proximal and distal extremities 42 and 43 and which can be formed of a suitable material such as stainless steel having an outside diameter for example of 0.018" or less and having a suitable wall thickness as for example, 0.001" to 0.002" and conventionally called a "hypotube"
W096/07351 PCT/U~3Slj~898 -6-o2~ 98 909 having a length of 150-170 centimeters. Where a smaller guidewire is desired, the hypotube 41 can have an exterior diameter of .014" or less. Typically such a guidewire includes a core wire (not shown) of the type disclosed in the above identified patents which extends from the proximal extremity to the distal extremity of the flexible elongate element 41.
A coil spring 46 is provided and is formed of a suitable material such as stainless steel. It has an outside diameter of 0.018" and is formed from a wire having a diameter of 0.003". The spring 46 is provided with a proximal extremity 47 which is threaded onto the distal extremity 43 of the flexible elongate member 41.
The distal extremity ~8 o~ the coil spring 46 is threaded onto the proximal extremity 49 of an intermediate or transition housing S1 formed of a suitable material such as stainless steel having an outside diameter of 0.018"
and having a suitable wall thickness as for example, 0.001~ to 0.002". The housing 51 is provided with a distal extremity 52 which has the proximal extremity 53 of a coil spring 54 threaded thereon. The coil spring 54 is formed of a highly radiopa~ue material such as palladium or a tungsten platinum alloy. The coil spring 46 can have a suitable length as for example 27 centimeters whereas, the coil spring 54 can have a suitable length such as 3 centimeters. The intermediate or transition housing 51 can have a suitable length as for example, one to five millimeters. The coil 54 is provided with a distal extremity which is threaded onto an end cap 57 also formed of a suitable material such as stainless steel and having an outside diameter of 0.018" and a wall thickness of 0.001" to 0.002". An ultrasonic transducer 58 is mounted in the end cap in a manner described in Patent No.
5,125,137 and has conductors 61 and 62 secured to the front and rear sides of the same which extend interiorly to the proximal extremity of the flexible elongate member 41.
ULTRA ~TNT~TURE PRESSURE 8ENSOR AND
This inven~ion relates to an ultra miniature pressure sensor and guidewire and apparatus using the same and method, which is particularly suitable for making pressure measurements in coronary arteries of human beings.
It has been well known that it is desirable to make pressure measurements in vessels and particularly in coronary arteries with the advent of angioplasty.
Typically in the past, such pressure measurements have been made by measuring the pressure at a proximal extremity of a lumen provided in a catheter advanced into the coronary artery of interest. However, such an approach has been less efficacious as the diameters of the catheters became smaller with the need to advance the catheter into smaller vessels. This made necessary the use of smaller lumens which gave less accurate pressure measurements and in the smallest catheters necessitated the elimination of such a pressure lumen entirely. In an attempt to overcome these difficulties, ultra miniature pressure sensors have been proposed for use on the distal extremities of catheters. However, it has not been ; feasible prior to the present invention to provide such ultra miniature pressure sensors which are capable of being incorporated in a guidewire for making pressure WO96/07351 PCT/U~3~ 9a -2- 02 1 98 9 og measurements in a very small arterial vessels. There is therefore a need for a new and improved ultra miniature pressure sensor and a guidewire and apparatus utilizing the same.
In general it is an object of the present invention to provide an ultra miniature pressure sensor and guidewire and apparatus utilizing the same making possible pressure and velocity measurements.
Another object of the invention is to provide a sensor which can be utilized on the distal extremity of a guidewire .018" or .014" in diameter.
Another object of the invention is to provide a sensor of the above character which is formed of a silicon chip of a small dimension which is reinforced by an additional member to provide reinforcement for the chip.
Another object of the invention is to provide a sensor of the above character in which a thin diaphragm is formed in the crystalline silicon chip.
Another object of the invention is to provide a sensor of the above character in which the reinforcing member extends for approximately 200 microns beyond the si~icon diaphragm.
Another object of the invention is to provide a guidewire with the above character in which the number of conducting wires required is kept to a minimum.
Another object of the invention is to provide a guidewire and method in which simultaneous pressure and velocity measurements can be made.
Another object of the invention is to provide a guidewire of the above character in which the diaphragm area has been maximized.
Another object of the invention is to provide a guidewire with the above character in which two pressure sensors are provided on the guidewire which are spaced apart so that pressure measurements can be made on both sides of a stenosis.
WOg6/07351 PCT/U'3S~'~9~3~
"~ , ~ -3- 0 2 1 98 909 Another object of the invention is to provide a guidewire of the above character in which the sensors are covered to prevent the formation of blood clots.
Another object of the invention is to provide an apparatus of the above character which includes a guidewire with an integral inflatable balloon.
Another object of the invention is to provide an apparatus of the above character in which temperature compensation can be provided.
Another object of the invention is to provide an apparatus of the above character which can be utilized in a half-bridge configuration.
Additional features and objects of the invention will appear from the following description in which the preferred embo*iments are set forth in detail in conjunction with the accompanying drawings.
Figure 1 is a schematic illustration showing use of a guidewire incorporating a pressure sensor of the present invention and apparatus utilizing the same in conjunction with a patient undergoing a catheterization procedure for diagnosis or treatment.
Figure 2 is a side elevational view of a guidewire incorporating an ultra miniature pressure sensor of the present invention.
Figure 3 is an enlarged side elevational view of the distal extremity of the guidewire shown in Figure 2 and showing the pressure sensor mounted therein.
Figure 4 is a top plan view looking along the line 4-4 of Figure 3.
Figure 5 is a bottom plan view looking along the line 5-5 of Figure 3.
Figure 6 is an isometric view of the pressure sensor shown in Figures 3, 4 and 5 with the lead wires connected thereto.
Figure 7 is a side elevational view of the pressure sensor shown in Figure 6.
WO g6/073~1 P~ 3S~'~9 fi9 8 0 2 1 9 8 9 o 9 Figure 8 is a top plan view of the pressure sensor shown in Figures 6 and 7.
Figure 9 is a cross-sectional view taken along the line 9-9 of Figure 8.
Figure 10 is a cross-sectional view taken along the line 10-10 of Figure 8.
Figure 11 is a cross-sectional view taken along the line 11-11 of Figure 8.
Figure 12, is a schematic diagram of the circuitry utilized in the pressure sensor shown in Figures 6-11.
Figure 13 is a side elevational view of the distal extremity of another guidewire incorporating the pressure sensor with the sensor of the present invention being mollnted in the tip housing.
Figure 14 is a side elevational view of the distal extremity of a guidewire having f irst and second pressure sensors mounted in the distal extremity of the same spaced apart to permit simultaneous measurements of proximal and distal pressures with respect to a stenosis.
Figure 15 is a partial side elevational view of another guidewire incorporating the present invention with an enclosed pressure sensor.
Figure 16 is a side elevational view partially in section of the distal extremity of another guidewire incorporating the present invention in which the pressure sensor is enclosed in a transition housing.
Figure 16A is a side elevational view in section showing an end-mounted pressure sensor incorporating the present invention.
Figure 17 is a side elevational view in section of a guidewire housing a tip-mounted sensor incorporating the present invention with an integral balloon.
In general, the guidewire of the present invention having pressure sensing capabilities is comprised of a flexible elongate element having proximal and distal extremities and having a diameter of .018" and less. The pressure sensor is mounted on the distal extremity of a WO96/07351 PCT~S~ 3~
s 0 2 1 9 8 9 0 9 flexible elongate element. It is comprised of a crystal semiconductor material having a recess therein and forming a diaphragm bordered by a rim. A reinforcing member is bonded to the crystal and reinforces the rim of the crystal and has a cavity therein underlying the diaphragm and exposed to the diaphragm. A resistor having opposite ends is carried by the crystal and has a portion thereof overIying a portion of the diaphragm. Leads are connected to opposite ends of the resistor and extend within the flexible elongate member to the proximal extremity of the flexible elongate member.
More in particular, the guidewire 21 of the present invention having pressure measuring capabilities as shown in Figure 1 is one that is adapted to be used in connection with a patient 22 lying on a table or a bed 23 in a cath lab of a typical hospital in which a catheterization procedure such as for diagnosis or treatment is being performed on the patient. The guidewire 21 is used with apparatus 24 which consists of a cable 26 which connects the guidewire 21 to an interface box 27. Interface box 27 is connected by another cable 28 to a control console 29 which has incorporated as a part thereof a video screen 31 on which a waveform 32 displaying ECG measurements may be provided as well as two traces 33 and 34 displaying pressure measurements being made by the guidewire 21.
The guidewire 21 is shown more in detail in Figure 2 and as shown therein, the guidewire 21 can be constructed utilizing the various constructions as shown in Patent Nos. 5,125,137; 5,163,445; 5,178,159; 5,226,421; and 5,240,437. As disclosed therein, such a guidewire consists of a flexible elongate element 41 having a proximal and distal extremities 42 and 43 and which can be formed of a suitable material such as stainless steel having an outside diameter for example of 0.018" or less and having a suitable wall thickness as for example, 0.001" to 0.002" and conventionally called a "hypotube"
W096/07351 PCT/U~3Slj~898 -6-o2~ 98 909 having a length of 150-170 centimeters. Where a smaller guidewire is desired, the hypotube 41 can have an exterior diameter of .014" or less. Typically such a guidewire includes a core wire (not shown) of the type disclosed in the above identified patents which extends from the proximal extremity to the distal extremity of the flexible elongate element 41.
A coil spring 46 is provided and is formed of a suitable material such as stainless steel. It has an outside diameter of 0.018" and is formed from a wire having a diameter of 0.003". The spring 46 is provided with a proximal extremity 47 which is threaded onto the distal extremity 43 of the flexible elongate member 41.
The distal extremity ~8 o~ the coil spring 46 is threaded onto the proximal extremity 49 of an intermediate or transition housing S1 formed of a suitable material such as stainless steel having an outside diameter of 0.018"
and having a suitable wall thickness as for example, 0.001~ to 0.002". The housing 51 is provided with a distal extremity 52 which has the proximal extremity 53 of a coil spring 54 threaded thereon. The coil spring 54 is formed of a highly radiopa~ue material such as palladium or a tungsten platinum alloy. The coil spring 46 can have a suitable length as for example 27 centimeters whereas, the coil spring 54 can have a suitable length such as 3 centimeters. The intermediate or transition housing 51 can have a suitable length as for example, one to five millimeters. The coil 54 is provided with a distal extremity which is threaded onto an end cap 57 also formed of a suitable material such as stainless steel and having an outside diameter of 0.018" and a wall thickness of 0.001" to 0.002". An ultrasonic transducer 58 is mounted in the end cap in a manner described in Patent No.
5,125,137 and has conductors 61 and 62 secured to the front and rear sides of the same which extend interiorly to the proximal extremity of the flexible elongate member 41.
3~1 PCT~S~3~95 ~7~ 0 2 1 9 8 9 0 9 A torquer 66 of the type described in Patent No. 5,178,159 is mounted on the proximal extremity 42 of the flexible elongate member 41 for causing a rotation of a guidewire 21 when used in connection with catheterization procedures in a manner well known to those skilled in the art.
The proximal extremity 42 is also provided with a plurality of conducting sleeves (not shown) of the type disclosed in Patent No. 5,178,159. In the present invention, one or more additional sleeves can be provided to make connection to the conductors hereinafter described. The proximal extremity 42 of the flexible elongate member is removably disposed within a housing 68 of the type described in Patent No. 5,178,159 and co-pending applications 128,835 and 114,767 that makes electrical contact with the sleeves on the proximal extremity 42 while permitting rotation of the sleeves and the flexible elongate member 41. The housing 68 carries female receptacles (not shown) which receive the sleeves and which are connected to a cable 71 connected to a connector 72. The connector 72 is connected to another mating connector 73 carried by the cable 26 and connected into the interface box 27.
The portion of the guidewire 21 therefore described is substantially conventional. In accordance with the present invention it is provided with a pressure measuring capability in the form of a pressure sensor assembly 76 which is mounted within the intermediate or transition housing 51. The pressure sensor assembly 76 consists of a diaphragm structure 77 supported by a base plate 78.
The diaphragm structure 77 is formed of suitable materials such as "n" type or "p" type 100 oriented silicon with a resistivity of approximately 6-8 ohm-centimeters. The diaphragm structure 77 is a die made from such a wafer.
In accordance with the present invention, the die has a suitable length, as for example, 1050 microns and for a 0.014" guidewire has a width of 250 microns and for a WO96/07351 PCT/u~5~9a3~
-8- 0 2198 9 o g 0.018" guidewire has a width of between 250 and 350 microns. It can have a suitable thickness, as for example, 50 microns. A rectangular diaphragm 79 is formed in the diaphragm structure 77 of a suitable thickness, as for example, 2.5 microns and having dimensions such as a length of 350 microns. The diaphragm 79 has first and second or top and bottom surfaces 80 and 81. The diaphragm is formed by utilization of conventional masking and crystal etching techniques which create a die with two parallel sloping endwalls 82 and two parallel sidewalls 83 extending at right angles to the end walls 82 leading down to the top surface 80 of the diaphragm 79 to form a well 84. As hereinafter explained, the diaphragm 79 is made relatively wide in comparison to the diaphrdgm structure 77 so that what remains is a relatively narrow rim 86 formed by side portions 87 and 88 and an end portion 89.
As can be seen from Figures 6, 7 and 8, the diaphragm 79 is located at or near one end of the diaphragm structure or die 77. It has been found that it is desirable to provide a rectangular geometry for the diaphragm 79 rather than a square geometry in order to obtain the highest possible sensitivity for pressure measurements. For example, it has been found that the rectangular diaphragm provides approximately 1.5 times more sensitivity than does a square diaphragm for the same diaphragm thickness and width.
In etching the well 84 to form the diaphragm 81, an impurity can be implanted -into the backside of the diaphragm structure 77 before the etching process is commenced so that etching will stop at the desired depth, as for example, within 2 to 3 microns of the bottom surface 81 to provide a diaphragm 79 having a thickness ranging from 2 to 5 microns, and for example, the preferred thickness of 2.5 microns. Because the rim 86 provided on the diaphragm structure 77 surrounding the rectangular diaphragm 79 is relatively thin, the base WO 96/07351 PCI~/Ubg~911g~
plate 78 provides support for this rim to provide the necessary strength for the pressure sensor 76.
In order to obtain adequate performance characteristics such as sensitivity in the miniaturized pressure sensor assembly 76 hereinbefore described, it has been found desirable to have as much of the width of diaphragm structure 77 as possible be occupied by the diaphragm 79 and at the same time to minimize the portion of the diaphragm structure 77 occupied by the rim. In lo order to achieve a diaphragm width ratio of at least 0.45 to 0.9 with respect to the width of the diaphragm 79 to the width of the structure 77 and therefore to obtain the largest diaphragm possible in the diaphragm structure 77, diaphragm 79 is made re atively large compared to rim 86.
With current manufacturing technology, it has been found feasible to have a width of rim 86 of 40 microns, which provides for a diaphragm 79 of 170 microns in a 250 micron-wide diaphragm structure 77 to provide a diaphragm width ratio of 0.68. In a l~rger diaphragm structure such as 350 microns wide, the pressure sensor assembly 76 can be made stronger by increasing the rim width to 90 microns. Alternatively, it can be made more sensitive by increasing the diaphragm width up to 270 microns. This results in a diaphragm width ratio for a 350 micron-wide device of between 0.49 and 0.77, depending on what combination of sensitivity and strength is desired.
Prior to or after the formation of the rectangular diaphragm 79, a plurality of V-shaped recesses or grooves 91 are formed in the diaphragm structure 77 on the end opposite the end at which the diaphragm 79 is located and on the side opposite the side in which the well 84 is formed. These V-shaped recesses 91 also can be formed in a conventional manner by the use of a conventional etch.
It should be appreciated that if desired, the etching can be stopped so that the rPcessec formed are short of a complete V. By way of example, if the etching for the V-shaped recess was stopped at a depth of 12 microns, the Wos6/073sl PCT/U~3S~9~8 lo-02198909 bottom of the substantially V-shaped recess or trench 91 would be approximately 8 microns wide.
After the V-shaped or substantially V-shaped recesses have been formed, a P+ diffusion utilizing a suitable material such as boron can be carried out to create a V-shaped region 92 (in the structure 77) which underlies the V-shaped recess 91. Utilizing suitable masking a common layer 93 of a suitable material such as chromium is sputtered into the V-shaped recess 91 to a suitable thickness as for example, 300 Angstroms followed by a layer 94 of a suitable material such as gold of a suitable thickness as for example 3000 Angstroms. The layers 93 and 94 overlie the bottom surface 81 to form pads 96 thereon. In dzpositing the gold in the V-shaped recess 91 it is desirable to terminate the gold just short of the leftmost extremity of the V-shaped recess as viewed in Figure 8 in order to minimize the likelihood of lead to lead shorting during the dicing operation when a wafer is sawed up into individual sensor chips.
By way of example, the spacing between V-grooves 91 from center to center can be 75 microns with the V-groove having a width of 25 microns and having a typical depth of 18 microns. The metal pads 96 formed by the chromium and gold layers 93 and 94 can have a suitable width as for example, 50 microns with the overlap on each side being approximately 12.5 microns to provide a spacing of approximately 25 microns between adjacent V-shaped pads 96. The bottom of the V-shaped groove can have a total length of approximately 250 microns.
The regions 92 formed from the P+ diffusion have patterns that extend to the right from the three V-shaped recesses 91 as viewed in Figure 8 for a distance so that they underly the approximate midpoint of the diaphragm 81 on opposite sides to provide generally U-shaped portions or resistors 92a which are located on the diaphragm in areas of a maximum stress to provide maximum sensitivity to pressure changes. The resistors 92a are provided with WO96/07351 pcTlu~3sl~38s~
-1l- 0 2 1 9 8 9 0 9 opposite ends, one end being connected to one each of the V-grooves and the other end being connected to the center or common V-groove. Contact is made to these P+ diffused regions by the chromium and gold layers 93 and 94 hereinbefore described.
The base plate 78 can be formed of a suitable material such as Pyrex supplied by Corning Glassworks and can have the same width as the diaphragm structure 77 but has a length which is less than the length of the diaphragm structure 77 so that the V-shaped grooves 91 are exposed on the underside of the diaphragm structure 77 as shown in Figure 6. It also can have a suitable length such as 850 microns. It is provided with a rectangular resess or cavity 101 having substantial'y the same size as the diaphragm 79, It can be etched into the Pyrex by suitable means such as a conventional etching process utilizing hydrochloric acid. After the etching has been completed to form the rectangular recess 101 it is bonded to the lower surface of the diaphragm structure 77 to form a hermetic seal with respect to the same so that the cavity 101 underlies the diaphragm 79 and is exposed to the bottom surface 81 of the diaphragm 79. The cavity 101 below the diaphragm 79 serves as a reference pressure chamber and can be filled with a suitable fluid. For example, it can be filled with air to half an atmosphere to provide a partial vacuum. Alternatively, the cavity 101 can be filled to one atmosphere or it can be completely evacuated.
A trifilar lead structure 106 is connected to the rectangular diaphragm structure 77. It has insulated copper leads 107 of a suitable diameter as for example 48AWG soldered into place to the V-shaped recesses 91 so that the leads 107 extend outwardly therefrom and lie in a plane parallel to the plane of the diaphragm structure 77. The trifilar lead construction 106 provides insulation around each lead and in addition there is provided additional insulation which surrounds the leads W096/07351 pcT~9~9~a and which interconnects the leads into a single unit which can be readily extended through the hypotube forming the flexible elongate member 41.
The pressure sensor assembly 76 is mounted within a cutout 111 provided in the transition housing 51 and secured therein by suitable means such as an epoxy 112 so that the outer surface of the pressure sensor assembly 76 is generally flush with the outer surface of the transition housing 51 (see Figure 3) and so that the diaphragm 79 is exposed to ambient and the leads 106 extend through the flexible elongate member 41 to the proximal extremity 42 of the same where they are connected to the sleeves (not shown) carried by the proximal extremity 4~ disposed within the hou~ing 68. Also, the conductors 61 and 62 of the velocity sensing transducer 58 are connected to two of such sleeves (not shown) provided on the proximal extremity 42.
A schematic of the wiring for the pressure sensor assembly 76 is shown in Figure 12. The two generally U-shaped portions 92a on opposite sides of the diaphragm 79 are represented as resistors and are connected to the three leads 107 in the manner shown. One of the first of the outside leads 107 is "SIGNAL OUT" (+) and the second or other outside lead is "SIGNAL OUT" (-) and the third or middle lead is a common lead as shown. This pattern makes it possible to not cross leads and has the third lead going up the middle or center of the die or the diaphragm structure 77. It can be seen that the two resistors 92a connected as shown form a half bridge one of the resistors responds positively to pressure change and the other resistor responds negatively to a pressure change. Thus, as a pressure is supplied to the diaphragm 79, one resistor increases in value and the other resistor decreases in value to provide a voltage change. By applying the same current to both resistors at the same time, temperature effects can be measured because temperature change will affect both of the resistors in WO96/07351 PCT/U~ 9~
the same way so that the pressure measurements can be compensated for any changes in temperature which are sensed by the resistors 92a. The changes in resistivity caused by the temperature changes in the resistors will cancel each other out because of the half bridge configuration used. In connection with Figure 12 it can be seen that with the use of three leads it is possible to obtain temperature compensation by utilizing a half-bridge configuration for the pressure sensor. Alternatively, a more precise temperature compensation can be provided by directly measuring the two resistances, and then solving the mathematical equations which relate temperature and pressure to the two sensor resistances.
Operation and use of the guidewire 21 in performing a catheterization procedure such as angioplasty may now be briefly described as follows: Let it be assumed that a guiding catheter (not shown) has been introduced into the femoral artery of the patient 22 shown in Figure 1 with the distal extremity near the desired location in the heart in which it is desired to perform an angioplasty.
The guidewire 21 of the present invention is inserted into the guiding catheter. At the time that its distal extremity is in close proximity to the distal extremity of the guiding catheter, the pressure output signal from the guidewire is compared with that of the guiding catheter assuming that the guidewire is provided with pressure sensing capabilities. If there is a difference between the two pressure measurements, the pressure measurement from the guidewire 21 is equalized with that from the guiding catheter at the control console 29. The distal extremity of the guidewire 21 is then advanced so that it is proximal of the stenosis to be treated at which time a pressure measurement is made. After this pressure measurement has been recorded, the distal extremity of the guidewire is then advanced through the stenosis and another pressure measurement made to determine whether the stenosis is severe enough to require treatment by Wo96tO7351 PCT/U~SI'~9~9~
angioplasty. Alternatively, the distal extremity of guidewire 21 can be immediately advanced to the distal side of the stenosis rather than making a pressure measurement proximal of the stenosis and thereafter comparing the pressure measurement on the distal extremity being measured by the guidewire 21 with the pressure measurement being provided proximal of the stenosis by the guiding catheter. If it is determined that the stenosis causes a partial occlusion which is severe enough to warrant use of an angioplasty procedure, an angioplasty catheter having a balloon thereon (not shown) can be advanced over the guidewire 21 and advanced into the stenosis to dilate the stenosis. After dilation has occurred, the angioplasty balloon can be withdrawn rom the stenosis and pressure measurements can be made proximal and distal of the stenosis to ascertain the effect of the angioplastic treatment. If the pressure measurements indicate that the original dilation by the angioplasty balloon has been inadequate, another balloon catheter as for example, one having a balloon of a greater diameter can then be positioned over the guidewire 21 by utilizing an exchange wire if appropriate. The larger angioplasty catheter can be advanced through the stenosis and inflated to again dilate the stenosis to a larger size after which it can be withdrawn. Thereafter, pressure measurements proximal and distal of the stenosis can again be made to ascertain whether or not the second dilation which has been performed is adequate. The decisions to be made in connection with such procedures can be readily made by use of the control console 29 by observing the traces 33 and 34 on the video monitor 31.
It also should be appreciated that at the same time Doppler velocity measurements can be made by the transducer 58. That information can be used in connection with the pressure measurements to ascertain the need for performing the angioplasty procedure or for determining the efficacy of the angioplasty procedure performed.
WO96/07351 PCT/U~g~1'09~9 Because of the very small diameters- of the guidewires as for example, .018" or .014~, it is possible to utilize the guidewire 21 of the present invention with very small coronary vessels in the heart. In connection with the leads from the Doppler transducer 58 it should be appreciated that if desired some of the conductors provided for the Doppler ultrasound transducer can be shared with the wires or conductors provided for the pressure sensor assembly 76. Thus, two of the wires for the pressure sensor can be utilized for the Doppler transducer because the pressure sensor operates at DC or up to a few hundred Hz or KHz whereas the Doppler sensor operates at 10 MHz and above. These frequency ranges can be readily separated by one skilled in the art by using simple filters and the appropriate circuitry.
In connection with the present invention it should be appreciated that rather than bonding the leads 107 into the V-grooves or V-shaped recesses 91, the Pyrex base plate 78 can be formed so it has the same length as the diaphragm structure 77. V-shaped or U-shaped grooves can be formed in the base plate underlying the V-shaped grooves to in effect form little tunnels which can be utilized for receiving ~he wires 107 and for them to be soldered therein. Such a construction aids in the placement of wires which are of the very small diameter, as for example, 1 mil.
Another embodiment of a guidewire 121 incorporating the present invention is shown in Figure 13. In the guidewire 121, pressure sensor assembly 76 is mounted in a tip housing 122. The tip housing 122 can be substituted at the end cap 57 and threaded into the distal extremity 56 of the coil 54. The tip housing 122 can be formed of - a suitable material such as stainless steel having an outside diameter of .018" and a wall thickness of .001" to .002". The sensor assembly 76 can be of the type hereinbefore described and can be mounted in a cutout 123 provided in the tip housing 122 much in the same manner as WO96/07351 PCT/U'9~9~98 -l6-02198909 the sensor assembly 76 was mounted in the cutout 111 in the transition housing 51 such as by use of an epoxy 124.
An hemispherical end cap 126 formed of a radiopaque material such as palladium or tungsten platinum alloy can be mounted on the distal extremity of the tip housing 122.
Alternatively, the end cap 126 can be formed of a non-radiopaque material such as epoxy or silicone rubber.
Thus it can be seen with the embodiment of the guidewire 121 shown in Figure 13, the guidewire 121 can be utilized in the same manner as the guidewire 21 hereinbefore described with the exception of it cannot be used for making velocity measurements because that capability has been removed from the guidewire 121.
Another guidewire 131 incorporating the present invention is shown in Figure 14 in which two pressure sensors 76 have been provided. The sensors 76 have been spaced apart a suitable distance as for example, 3 centimeters with one of the pressure sensors being mounted in the transition housing S1 and the other pressure sensor being mounted in a tip housing 122 of the type shown in Figure 13. With such an arrangement, it can be seen that the distal extremity of the guidewire 131 can be advanced across a stenosis in a vessel with the pressure sensor 76 mounted in the tip housing being distal of the stenosis to measure distal pressure and the pressure sensor 76 in the transition housing 51 being proximal of the stenosis to measure proximal pressure. Thus, it can be seen that it is possible-to measure simultaneously the distal pressure and the proximal pressure with respect to a stenosis in a vessel. This may give more accurate measurements than utilizing the proximal pressure being sensed by the guiding catheter.
When using two pressure sensors 76 in the same guidewire as shown in Figure 14, it is possible to utilize the same common wire for both of the transducers, thus making it nec~ss~ry to provide only five wires rather than six wires for the two pressure sensors.
WO96/07351 0 2 1 9 8 g oP g /u~9~ 8~
Still another guidewire 141 incorporating the present invention is shown in Figure 15 in which a cover 142 is provided for covering the pressure sensor assembly 76 provided in the transition housing 51. The cover is elongate and extends the length of the cutout 111 and is arcuate in cross-section so that it conforms to the conformation of the transition housing 51. The cover 142 can be secured in place by a suitable means such as an adhesive. The cover 142 overlying the pressure sensor assembly 76 is provided with a pin hole 143 which immediately overlies the diaphragm 79. The pin hole 143 can be of a suitable size as for example 2-5 mils in and preferably 3 mils in diameter. The cover 142 serves to prevent the large opening provided by the cutout 111 fr~m collecting blood which could possibly clot. The cover 142 also serves to protect the sensor 76 from damage. It also prevents the sensor 76 from being broken loose during use of the guidewire 141. It should be appreciated that if desired, the volume beneath the cover 142 can be filled with viscous fluid such as oil which can be utilized for transmitting pressure from the pin hole 143 to the diaphragm 81. With a small size pin hole 143, the viscous fluid provided would not have a tendency to bleed out of the transition housing 51. The viscous fluid would be held in place because of the surface tension of the fluid. Because there is a very short distance between the pin hole 143 and the diaphragm 79, there would be very little tendency for the viscous fluid to damp any pressure signal transmitted from the blood in which the guidewire 141 is disposed to the diaphragm.
Another guidewire 151 incorporating the present invention is shown in Figure 16 having a transition - housing 152 formed of a suitable material such as stainless steel and having an OD of .018" or less. A
pressure sensor assembly 76 of the type hereinbefore described is mounted within the bore lS3 of the transition housing 152 and is secured therein by mounting the same in Wo96tO7351 PCT/U~ 898 -18- 0 2 ~ 9 8 9 0 9 an epoxy 154 while leaving the area immediately above the diaphragm 79 eYros~ to a pin hole 156 provided in the transition housing 152. The space overlying the diaphragm 81 exposed to the pin hole 156 can be filled with a viscous fluid lS7 such as oil. The viscous fluid 157 can be retained within the desired location by a barrier 158 formed on the proximal side of the pressure sensor 76 having the trifilar lead structure 106 extending therethrough, in sealing engagement therewith. To seal the other end of the bore 153, an intermediate end cap 161 can be provided which is provided with a barrier 182 extending thereacross to seal the bore 153. The intermediate end cap 161 can be bonded to the transition housing 152 by a suitable means such as an adhecive (not shown). The coil 54 can be threaded onto the intermediate end cap 161 and can be threaded onto a tip housing 166 that carries a rounded hemispherical tip 167. With such a construction it can be seen that the pressure sensor assembly 76 is protected within the transition housing 152.
In Figure 16A a guidewire 168 is shown which is very similar to the guidewire 151 with the exception that the housing 152 has been provided on the distal extremity of the coil 46 with the tip 167 directly mounted on the housing 152 for closing the bore 153.
In Figure 17 there is shown another embodiment of a guidewire 171 incorporating the present invention which has an integral balloon carried thereby. A guidewire with an integral balloon is described in U.S. Patent No.
5,226,421. The guidewire 171 consists of a flexible elongate tubular member 173 in a manner formed of a suitable material such as plastic which is provided with a distal extremity 174. An inflatable balloon 176 is secured to the distal extremity 174 of the flexible elongate member 173 in a manner well known to those skilled in the art. Such a balloon can be formed integral with the distal extremity and can be formed of the same WO96/07351 PCT/~ ~9~9~
material as the flexible elongate tubular member 173.
Alternatively, it can be formed of a different material or the same material and be formed as a separate part and secured to the distal extremity 174 by suitable means such as adhesive.
The balloon 176 is provided with a distal extremity which is closed and which is secured to the proximal extremity of a coil spring 178 formed of a radiopaque material such as a palladium or tungsten platinum alloy threaded onto a tip housing 179. The tip housing 179 can be formed in a manner similar to the tip housing 122 shown in Figure 13 having a pressure sensor 76 mounted therein and carrying an end cap 181. The trifilar leads 106 connected tQ the sensor 76 extend through the coil 178 and through the balloon 176 and through the flexible elongate tubular member 172 to the proximal extremity thereof. A
core wire 186 formed of a suitable material such as stainless steel is provided in the flexible elongate member 173 and can be provided with a diameter such as disclosed in Patent No. 5,226,421. The core wire 186 is provided with a tapered portion 186a extending through the balloon which has a distal extremity secured to the housing 179 by a suitable means such as the epoxy utilized for mounting the sensor 76 within the housing. The flexible elongate tubular member 172 is provided with a balloon inflation lumen 187 which can be used for inflating and deflating the balloon 176.
The guidewire 171 with an integral balloon 171 can be utilized in a manner similar to that hereinbefore described for the other guidewires. Rather than deploying a separate catheter with a balloon thereon over the guidewire, the guidewire 171 itself carries the balloon 176 which can be inflated to dilate the stenosis after the proximal and distal pressure measurements have been made by the tip mounted sensor 76. After the balloon 176 has been deflated, the pressure measurement can be made to ascertain the pressure in the distal extremity after W096/07351 PCT~S~S~9~8 ~ -20- 0 2 1 98 9 0 9 dilation has occurred. If necessary, the balloon 176 can be re-inflated to perform another dilation of the stenosis to obtain improved blood flow through the stenosis.
After an appropriate dilation has occurred, the guidewire 171 with integral balloon can be removed in a conventional manner. The angioplasty procedure can then be completed in a conventional manner.
From the foregoing, it can be seen that there has been provided an ultra miniature pressure sensor which can be utilized on guidewires having a diameter of .018" and less which can be utilized for making accurate measurements proximal and distal of a stenosis in the coronary vessel. This is made possible because of the small size of the pressure sensor incorp~rzted into the distal extremity of the guidewire. In addition to sensing pressure, flow velocity can also be obtained by the use of a distally mounted velocity transducer provided on the same guidewire as on which the pressure sensor is mounted.
Alternatively, additional first and second pressure sensors can be provided on the distal extremity of a guidewire so that pressure measurements can be made simultaneously, proximally and distally of the stenosis.
The pressure sensor is constructed in such a manner so that it can be readily incorporated within the confines of a small guidewire as for example, .018" and less. It can be constructed to avoid a large opening in the distal extremity of the guidewire to inhibit or prevent the formation of clots. The pressure sensor also can be protected so that it cannot be readily damaged or broken loose. In addition, where desired, the guidewire can be provided with an integrally mounted balloon on its distal extremity so that the guidewire can be utilized for performing an angioplasty procedure while at the same time facilitating the making of pressure measurements, proximal and distal of the stenosis being treated.
The proximal extremity 42 is also provided with a plurality of conducting sleeves (not shown) of the type disclosed in Patent No. 5,178,159. In the present invention, one or more additional sleeves can be provided to make connection to the conductors hereinafter described. The proximal extremity 42 of the flexible elongate member is removably disposed within a housing 68 of the type described in Patent No. 5,178,159 and co-pending applications 128,835 and 114,767 that makes electrical contact with the sleeves on the proximal extremity 42 while permitting rotation of the sleeves and the flexible elongate member 41. The housing 68 carries female receptacles (not shown) which receive the sleeves and which are connected to a cable 71 connected to a connector 72. The connector 72 is connected to another mating connector 73 carried by the cable 26 and connected into the interface box 27.
The portion of the guidewire 21 therefore described is substantially conventional. In accordance with the present invention it is provided with a pressure measuring capability in the form of a pressure sensor assembly 76 which is mounted within the intermediate or transition housing 51. The pressure sensor assembly 76 consists of a diaphragm structure 77 supported by a base plate 78.
The diaphragm structure 77 is formed of suitable materials such as "n" type or "p" type 100 oriented silicon with a resistivity of approximately 6-8 ohm-centimeters. The diaphragm structure 77 is a die made from such a wafer.
In accordance with the present invention, the die has a suitable length, as for example, 1050 microns and for a 0.014" guidewire has a width of 250 microns and for a WO96/07351 PCT/u~5~9a3~
-8- 0 2198 9 o g 0.018" guidewire has a width of between 250 and 350 microns. It can have a suitable thickness, as for example, 50 microns. A rectangular diaphragm 79 is formed in the diaphragm structure 77 of a suitable thickness, as for example, 2.5 microns and having dimensions such as a length of 350 microns. The diaphragm 79 has first and second or top and bottom surfaces 80 and 81. The diaphragm is formed by utilization of conventional masking and crystal etching techniques which create a die with two parallel sloping endwalls 82 and two parallel sidewalls 83 extending at right angles to the end walls 82 leading down to the top surface 80 of the diaphragm 79 to form a well 84. As hereinafter explained, the diaphragm 79 is made relatively wide in comparison to the diaphrdgm structure 77 so that what remains is a relatively narrow rim 86 formed by side portions 87 and 88 and an end portion 89.
As can be seen from Figures 6, 7 and 8, the diaphragm 79 is located at or near one end of the diaphragm structure or die 77. It has been found that it is desirable to provide a rectangular geometry for the diaphragm 79 rather than a square geometry in order to obtain the highest possible sensitivity for pressure measurements. For example, it has been found that the rectangular diaphragm provides approximately 1.5 times more sensitivity than does a square diaphragm for the same diaphragm thickness and width.
In etching the well 84 to form the diaphragm 81, an impurity can be implanted -into the backside of the diaphragm structure 77 before the etching process is commenced so that etching will stop at the desired depth, as for example, within 2 to 3 microns of the bottom surface 81 to provide a diaphragm 79 having a thickness ranging from 2 to 5 microns, and for example, the preferred thickness of 2.5 microns. Because the rim 86 provided on the diaphragm structure 77 surrounding the rectangular diaphragm 79 is relatively thin, the base WO 96/07351 PCI~/Ubg~911g~
plate 78 provides support for this rim to provide the necessary strength for the pressure sensor 76.
In order to obtain adequate performance characteristics such as sensitivity in the miniaturized pressure sensor assembly 76 hereinbefore described, it has been found desirable to have as much of the width of diaphragm structure 77 as possible be occupied by the diaphragm 79 and at the same time to minimize the portion of the diaphragm structure 77 occupied by the rim. In lo order to achieve a diaphragm width ratio of at least 0.45 to 0.9 with respect to the width of the diaphragm 79 to the width of the structure 77 and therefore to obtain the largest diaphragm possible in the diaphragm structure 77, diaphragm 79 is made re atively large compared to rim 86.
With current manufacturing technology, it has been found feasible to have a width of rim 86 of 40 microns, which provides for a diaphragm 79 of 170 microns in a 250 micron-wide diaphragm structure 77 to provide a diaphragm width ratio of 0.68. In a l~rger diaphragm structure such as 350 microns wide, the pressure sensor assembly 76 can be made stronger by increasing the rim width to 90 microns. Alternatively, it can be made more sensitive by increasing the diaphragm width up to 270 microns. This results in a diaphragm width ratio for a 350 micron-wide device of between 0.49 and 0.77, depending on what combination of sensitivity and strength is desired.
Prior to or after the formation of the rectangular diaphragm 79, a plurality of V-shaped recesses or grooves 91 are formed in the diaphragm structure 77 on the end opposite the end at which the diaphragm 79 is located and on the side opposite the side in which the well 84 is formed. These V-shaped recesses 91 also can be formed in a conventional manner by the use of a conventional etch.
It should be appreciated that if desired, the etching can be stopped so that the rPcessec formed are short of a complete V. By way of example, if the etching for the V-shaped recess was stopped at a depth of 12 microns, the Wos6/073sl PCT/U~3S~9~8 lo-02198909 bottom of the substantially V-shaped recess or trench 91 would be approximately 8 microns wide.
After the V-shaped or substantially V-shaped recesses have been formed, a P+ diffusion utilizing a suitable material such as boron can be carried out to create a V-shaped region 92 (in the structure 77) which underlies the V-shaped recess 91. Utilizing suitable masking a common layer 93 of a suitable material such as chromium is sputtered into the V-shaped recess 91 to a suitable thickness as for example, 300 Angstroms followed by a layer 94 of a suitable material such as gold of a suitable thickness as for example 3000 Angstroms. The layers 93 and 94 overlie the bottom surface 81 to form pads 96 thereon. In dzpositing the gold in the V-shaped recess 91 it is desirable to terminate the gold just short of the leftmost extremity of the V-shaped recess as viewed in Figure 8 in order to minimize the likelihood of lead to lead shorting during the dicing operation when a wafer is sawed up into individual sensor chips.
By way of example, the spacing between V-grooves 91 from center to center can be 75 microns with the V-groove having a width of 25 microns and having a typical depth of 18 microns. The metal pads 96 formed by the chromium and gold layers 93 and 94 can have a suitable width as for example, 50 microns with the overlap on each side being approximately 12.5 microns to provide a spacing of approximately 25 microns between adjacent V-shaped pads 96. The bottom of the V-shaped groove can have a total length of approximately 250 microns.
The regions 92 formed from the P+ diffusion have patterns that extend to the right from the three V-shaped recesses 91 as viewed in Figure 8 for a distance so that they underly the approximate midpoint of the diaphragm 81 on opposite sides to provide generally U-shaped portions or resistors 92a which are located on the diaphragm in areas of a maximum stress to provide maximum sensitivity to pressure changes. The resistors 92a are provided with WO96/07351 pcTlu~3sl~38s~
-1l- 0 2 1 9 8 9 0 9 opposite ends, one end being connected to one each of the V-grooves and the other end being connected to the center or common V-groove. Contact is made to these P+ diffused regions by the chromium and gold layers 93 and 94 hereinbefore described.
The base plate 78 can be formed of a suitable material such as Pyrex supplied by Corning Glassworks and can have the same width as the diaphragm structure 77 but has a length which is less than the length of the diaphragm structure 77 so that the V-shaped grooves 91 are exposed on the underside of the diaphragm structure 77 as shown in Figure 6. It also can have a suitable length such as 850 microns. It is provided with a rectangular resess or cavity 101 having substantial'y the same size as the diaphragm 79, It can be etched into the Pyrex by suitable means such as a conventional etching process utilizing hydrochloric acid. After the etching has been completed to form the rectangular recess 101 it is bonded to the lower surface of the diaphragm structure 77 to form a hermetic seal with respect to the same so that the cavity 101 underlies the diaphragm 79 and is exposed to the bottom surface 81 of the diaphragm 79. The cavity 101 below the diaphragm 79 serves as a reference pressure chamber and can be filled with a suitable fluid. For example, it can be filled with air to half an atmosphere to provide a partial vacuum. Alternatively, the cavity 101 can be filled to one atmosphere or it can be completely evacuated.
A trifilar lead structure 106 is connected to the rectangular diaphragm structure 77. It has insulated copper leads 107 of a suitable diameter as for example 48AWG soldered into place to the V-shaped recesses 91 so that the leads 107 extend outwardly therefrom and lie in a plane parallel to the plane of the diaphragm structure 77. The trifilar lead construction 106 provides insulation around each lead and in addition there is provided additional insulation which surrounds the leads W096/07351 pcT~9~9~a and which interconnects the leads into a single unit which can be readily extended through the hypotube forming the flexible elongate member 41.
The pressure sensor assembly 76 is mounted within a cutout 111 provided in the transition housing 51 and secured therein by suitable means such as an epoxy 112 so that the outer surface of the pressure sensor assembly 76 is generally flush with the outer surface of the transition housing 51 (see Figure 3) and so that the diaphragm 79 is exposed to ambient and the leads 106 extend through the flexible elongate member 41 to the proximal extremity 42 of the same where they are connected to the sleeves (not shown) carried by the proximal extremity 4~ disposed within the hou~ing 68. Also, the conductors 61 and 62 of the velocity sensing transducer 58 are connected to two of such sleeves (not shown) provided on the proximal extremity 42.
A schematic of the wiring for the pressure sensor assembly 76 is shown in Figure 12. The two generally U-shaped portions 92a on opposite sides of the diaphragm 79 are represented as resistors and are connected to the three leads 107 in the manner shown. One of the first of the outside leads 107 is "SIGNAL OUT" (+) and the second or other outside lead is "SIGNAL OUT" (-) and the third or middle lead is a common lead as shown. This pattern makes it possible to not cross leads and has the third lead going up the middle or center of the die or the diaphragm structure 77. It can be seen that the two resistors 92a connected as shown form a half bridge one of the resistors responds positively to pressure change and the other resistor responds negatively to a pressure change. Thus, as a pressure is supplied to the diaphragm 79, one resistor increases in value and the other resistor decreases in value to provide a voltage change. By applying the same current to both resistors at the same time, temperature effects can be measured because temperature change will affect both of the resistors in WO96/07351 PCT/U~ 9~
the same way so that the pressure measurements can be compensated for any changes in temperature which are sensed by the resistors 92a. The changes in resistivity caused by the temperature changes in the resistors will cancel each other out because of the half bridge configuration used. In connection with Figure 12 it can be seen that with the use of three leads it is possible to obtain temperature compensation by utilizing a half-bridge configuration for the pressure sensor. Alternatively, a more precise temperature compensation can be provided by directly measuring the two resistances, and then solving the mathematical equations which relate temperature and pressure to the two sensor resistances.
Operation and use of the guidewire 21 in performing a catheterization procedure such as angioplasty may now be briefly described as follows: Let it be assumed that a guiding catheter (not shown) has been introduced into the femoral artery of the patient 22 shown in Figure 1 with the distal extremity near the desired location in the heart in which it is desired to perform an angioplasty.
The guidewire 21 of the present invention is inserted into the guiding catheter. At the time that its distal extremity is in close proximity to the distal extremity of the guiding catheter, the pressure output signal from the guidewire is compared with that of the guiding catheter assuming that the guidewire is provided with pressure sensing capabilities. If there is a difference between the two pressure measurements, the pressure measurement from the guidewire 21 is equalized with that from the guiding catheter at the control console 29. The distal extremity of the guidewire 21 is then advanced so that it is proximal of the stenosis to be treated at which time a pressure measurement is made. After this pressure measurement has been recorded, the distal extremity of the guidewire is then advanced through the stenosis and another pressure measurement made to determine whether the stenosis is severe enough to require treatment by Wo96tO7351 PCT/U~SI'~9~9~
angioplasty. Alternatively, the distal extremity of guidewire 21 can be immediately advanced to the distal side of the stenosis rather than making a pressure measurement proximal of the stenosis and thereafter comparing the pressure measurement on the distal extremity being measured by the guidewire 21 with the pressure measurement being provided proximal of the stenosis by the guiding catheter. If it is determined that the stenosis causes a partial occlusion which is severe enough to warrant use of an angioplasty procedure, an angioplasty catheter having a balloon thereon (not shown) can be advanced over the guidewire 21 and advanced into the stenosis to dilate the stenosis. After dilation has occurred, the angioplasty balloon can be withdrawn rom the stenosis and pressure measurements can be made proximal and distal of the stenosis to ascertain the effect of the angioplastic treatment. If the pressure measurements indicate that the original dilation by the angioplasty balloon has been inadequate, another balloon catheter as for example, one having a balloon of a greater diameter can then be positioned over the guidewire 21 by utilizing an exchange wire if appropriate. The larger angioplasty catheter can be advanced through the stenosis and inflated to again dilate the stenosis to a larger size after which it can be withdrawn. Thereafter, pressure measurements proximal and distal of the stenosis can again be made to ascertain whether or not the second dilation which has been performed is adequate. The decisions to be made in connection with such procedures can be readily made by use of the control console 29 by observing the traces 33 and 34 on the video monitor 31.
It also should be appreciated that at the same time Doppler velocity measurements can be made by the transducer 58. That information can be used in connection with the pressure measurements to ascertain the need for performing the angioplasty procedure or for determining the efficacy of the angioplasty procedure performed.
WO96/07351 PCT/U~g~1'09~9 Because of the very small diameters- of the guidewires as for example, .018" or .014~, it is possible to utilize the guidewire 21 of the present invention with very small coronary vessels in the heart. In connection with the leads from the Doppler transducer 58 it should be appreciated that if desired some of the conductors provided for the Doppler ultrasound transducer can be shared with the wires or conductors provided for the pressure sensor assembly 76. Thus, two of the wires for the pressure sensor can be utilized for the Doppler transducer because the pressure sensor operates at DC or up to a few hundred Hz or KHz whereas the Doppler sensor operates at 10 MHz and above. These frequency ranges can be readily separated by one skilled in the art by using simple filters and the appropriate circuitry.
In connection with the present invention it should be appreciated that rather than bonding the leads 107 into the V-grooves or V-shaped recesses 91, the Pyrex base plate 78 can be formed so it has the same length as the diaphragm structure 77. V-shaped or U-shaped grooves can be formed in the base plate underlying the V-shaped grooves to in effect form little tunnels which can be utilized for receiving ~he wires 107 and for them to be soldered therein. Such a construction aids in the placement of wires which are of the very small diameter, as for example, 1 mil.
Another embodiment of a guidewire 121 incorporating the present invention is shown in Figure 13. In the guidewire 121, pressure sensor assembly 76 is mounted in a tip housing 122. The tip housing 122 can be substituted at the end cap 57 and threaded into the distal extremity 56 of the coil 54. The tip housing 122 can be formed of - a suitable material such as stainless steel having an outside diameter of .018" and a wall thickness of .001" to .002". The sensor assembly 76 can be of the type hereinbefore described and can be mounted in a cutout 123 provided in the tip housing 122 much in the same manner as WO96/07351 PCT/U'9~9~98 -l6-02198909 the sensor assembly 76 was mounted in the cutout 111 in the transition housing 51 such as by use of an epoxy 124.
An hemispherical end cap 126 formed of a radiopaque material such as palladium or tungsten platinum alloy can be mounted on the distal extremity of the tip housing 122.
Alternatively, the end cap 126 can be formed of a non-radiopaque material such as epoxy or silicone rubber.
Thus it can be seen with the embodiment of the guidewire 121 shown in Figure 13, the guidewire 121 can be utilized in the same manner as the guidewire 21 hereinbefore described with the exception of it cannot be used for making velocity measurements because that capability has been removed from the guidewire 121.
Another guidewire 131 incorporating the present invention is shown in Figure 14 in which two pressure sensors 76 have been provided. The sensors 76 have been spaced apart a suitable distance as for example, 3 centimeters with one of the pressure sensors being mounted in the transition housing S1 and the other pressure sensor being mounted in a tip housing 122 of the type shown in Figure 13. With such an arrangement, it can be seen that the distal extremity of the guidewire 131 can be advanced across a stenosis in a vessel with the pressure sensor 76 mounted in the tip housing being distal of the stenosis to measure distal pressure and the pressure sensor 76 in the transition housing 51 being proximal of the stenosis to measure proximal pressure. Thus, it can be seen that it is possible-to measure simultaneously the distal pressure and the proximal pressure with respect to a stenosis in a vessel. This may give more accurate measurements than utilizing the proximal pressure being sensed by the guiding catheter.
When using two pressure sensors 76 in the same guidewire as shown in Figure 14, it is possible to utilize the same common wire for both of the transducers, thus making it nec~ss~ry to provide only five wires rather than six wires for the two pressure sensors.
WO96/07351 0 2 1 9 8 g oP g /u~9~ 8~
Still another guidewire 141 incorporating the present invention is shown in Figure 15 in which a cover 142 is provided for covering the pressure sensor assembly 76 provided in the transition housing 51. The cover is elongate and extends the length of the cutout 111 and is arcuate in cross-section so that it conforms to the conformation of the transition housing 51. The cover 142 can be secured in place by a suitable means such as an adhesive. The cover 142 overlying the pressure sensor assembly 76 is provided with a pin hole 143 which immediately overlies the diaphragm 79. The pin hole 143 can be of a suitable size as for example 2-5 mils in and preferably 3 mils in diameter. The cover 142 serves to prevent the large opening provided by the cutout 111 fr~m collecting blood which could possibly clot. The cover 142 also serves to protect the sensor 76 from damage. It also prevents the sensor 76 from being broken loose during use of the guidewire 141. It should be appreciated that if desired, the volume beneath the cover 142 can be filled with viscous fluid such as oil which can be utilized for transmitting pressure from the pin hole 143 to the diaphragm 81. With a small size pin hole 143, the viscous fluid provided would not have a tendency to bleed out of the transition housing 51. The viscous fluid would be held in place because of the surface tension of the fluid. Because there is a very short distance between the pin hole 143 and the diaphragm 79, there would be very little tendency for the viscous fluid to damp any pressure signal transmitted from the blood in which the guidewire 141 is disposed to the diaphragm.
Another guidewire 151 incorporating the present invention is shown in Figure 16 having a transition - housing 152 formed of a suitable material such as stainless steel and having an OD of .018" or less. A
pressure sensor assembly 76 of the type hereinbefore described is mounted within the bore lS3 of the transition housing 152 and is secured therein by mounting the same in Wo96tO7351 PCT/U~ 898 -18- 0 2 ~ 9 8 9 0 9 an epoxy 154 while leaving the area immediately above the diaphragm 79 eYros~ to a pin hole 156 provided in the transition housing 152. The space overlying the diaphragm 81 exposed to the pin hole 156 can be filled with a viscous fluid lS7 such as oil. The viscous fluid 157 can be retained within the desired location by a barrier 158 formed on the proximal side of the pressure sensor 76 having the trifilar lead structure 106 extending therethrough, in sealing engagement therewith. To seal the other end of the bore 153, an intermediate end cap 161 can be provided which is provided with a barrier 182 extending thereacross to seal the bore 153. The intermediate end cap 161 can be bonded to the transition housing 152 by a suitable means such as an adhecive (not shown). The coil 54 can be threaded onto the intermediate end cap 161 and can be threaded onto a tip housing 166 that carries a rounded hemispherical tip 167. With such a construction it can be seen that the pressure sensor assembly 76 is protected within the transition housing 152.
In Figure 16A a guidewire 168 is shown which is very similar to the guidewire 151 with the exception that the housing 152 has been provided on the distal extremity of the coil 46 with the tip 167 directly mounted on the housing 152 for closing the bore 153.
In Figure 17 there is shown another embodiment of a guidewire 171 incorporating the present invention which has an integral balloon carried thereby. A guidewire with an integral balloon is described in U.S. Patent No.
5,226,421. The guidewire 171 consists of a flexible elongate tubular member 173 in a manner formed of a suitable material such as plastic which is provided with a distal extremity 174. An inflatable balloon 176 is secured to the distal extremity 174 of the flexible elongate member 173 in a manner well known to those skilled in the art. Such a balloon can be formed integral with the distal extremity and can be formed of the same WO96/07351 PCT/~ ~9~9~
material as the flexible elongate tubular member 173.
Alternatively, it can be formed of a different material or the same material and be formed as a separate part and secured to the distal extremity 174 by suitable means such as adhesive.
The balloon 176 is provided with a distal extremity which is closed and which is secured to the proximal extremity of a coil spring 178 formed of a radiopaque material such as a palladium or tungsten platinum alloy threaded onto a tip housing 179. The tip housing 179 can be formed in a manner similar to the tip housing 122 shown in Figure 13 having a pressure sensor 76 mounted therein and carrying an end cap 181. The trifilar leads 106 connected tQ the sensor 76 extend through the coil 178 and through the balloon 176 and through the flexible elongate tubular member 172 to the proximal extremity thereof. A
core wire 186 formed of a suitable material such as stainless steel is provided in the flexible elongate member 173 and can be provided with a diameter such as disclosed in Patent No. 5,226,421. The core wire 186 is provided with a tapered portion 186a extending through the balloon which has a distal extremity secured to the housing 179 by a suitable means such as the epoxy utilized for mounting the sensor 76 within the housing. The flexible elongate tubular member 172 is provided with a balloon inflation lumen 187 which can be used for inflating and deflating the balloon 176.
The guidewire 171 with an integral balloon 171 can be utilized in a manner similar to that hereinbefore described for the other guidewires. Rather than deploying a separate catheter with a balloon thereon over the guidewire, the guidewire 171 itself carries the balloon 176 which can be inflated to dilate the stenosis after the proximal and distal pressure measurements have been made by the tip mounted sensor 76. After the balloon 176 has been deflated, the pressure measurement can be made to ascertain the pressure in the distal extremity after W096/07351 PCT~S~S~9~8 ~ -20- 0 2 1 98 9 0 9 dilation has occurred. If necessary, the balloon 176 can be re-inflated to perform another dilation of the stenosis to obtain improved blood flow through the stenosis.
After an appropriate dilation has occurred, the guidewire 171 with integral balloon can be removed in a conventional manner. The angioplasty procedure can then be completed in a conventional manner.
From the foregoing, it can be seen that there has been provided an ultra miniature pressure sensor which can be utilized on guidewires having a diameter of .018" and less which can be utilized for making accurate measurements proximal and distal of a stenosis in the coronary vessel. This is made possible because of the small size of the pressure sensor incorp~rzted into the distal extremity of the guidewire. In addition to sensing pressure, flow velocity can also be obtained by the use of a distally mounted velocity transducer provided on the same guidewire as on which the pressure sensor is mounted.
Alternatively, additional first and second pressure sensors can be provided on the distal extremity of a guidewire so that pressure measurements can be made simultaneously, proximally and distally of the stenosis.
The pressure sensor is constructed in such a manner so that it can be readily incorporated within the confines of a small guidewire as for example, .018" and less. It can be constructed to avoid a large opening in the distal extremity of the guidewire to inhibit or prevent the formation of clots. The pressure sensor also can be protected so that it cannot be readily damaged or broken loose. In addition, where desired, the guidewire can be provided with an integrally mounted balloon on its distal extremity so that the guidewire can be utilized for performing an angioplasty procedure while at the same time facilitating the making of pressure measurements, proximal and distal of the stenosis being treated.
Claims (21)
1. A guidewire having pressure sensing capabilities for measuring the pressure of liquid in a vessel comprising a flexible elongate member and having proximal and distal extremities and having an outside diameter of .018" or less, said distal extremity of said flexible elongate member being adapted to be disposed in the liquid in said vessel, a housing carried by the flexible elongate member and having a diameter substantially the same as the diameter of the flexible elongate member, said housing having a space therein, a pressure sensor mounted in the space in the housing, the pressure sensor comprising a crystal of semiconductor material having a well therein and forming a diaphragm having a thickness ranging from 2 to 5 microns, said diaphragm being disposed in the housing in a manner so that it is sensitive to changes of pressure in the liquid in the vessel, said diaphragm being rectangular in shape and being bordered by a rim surrounding the well and formed of the crystal of semiconductor material, a backing plate formed of an insulating material bonded to the crystal and serving to reinforce the rim of the crystal of semiconductor material, said backing plate having a cavity therein underlying the diaphragm and in substantial registration with the diaphragm with said cavity serving to provide a pressure reference, said crystal of semiconductor material having at least one diffused region therein formed of an impurity, said diffused region overlying the portion of the diaphragm where deflection will occur whereby upon the application of a pressure to the diaphragm a change in resistivity will occur in the diffused region, conductive means carried by the crystal of semiconductor material and coupled to said at least one diffused region, a power source connected to the conductor means for supplying electrical energy to said at least one diffused region and means measuring the change in resistivity in said at least one diffused region to ascertain the pressure being applied to the diaphragm by the liquid in the vessel.
2. A guidewire as in Claim 1 together with means connected to the leads for compensating for temperature changes of the pressure sensor during the time that pressures are being sensed by the pressure sensors.
3. A guidewire as in Claim 1 wherein said diffused region includes first and second diffused portions, said first and second diffused portions overlying said spaced apart portions of the diaphragm and serving as first and second resistor elements having opposite ends.
4. A guidewire as in Claim 3 wherein said crystal of semiconductor material has first and second sides, wherein said well is formed so it extends through said one side together with troughs formed in the crystal of semiconductor material and opening on the opposite side of the crystal of semiconductor material and wherein said conductor means includes leads secured in said troughs and means in said troughs for establishing electrical connections between the leads in the troughs and the first and second diffused portions.
5. A guidewire as in Claim 4 wherein said leads are first and second and third leads secured in said troughs, said first lead being secured to one end of the first resistor element, the second lead being secured to one end of the second resistor element and the third lead being connected to the other ends of the first and second resistor elements to serve as a common lead.
6. A guidewire as in Claim 3 wherein said resistor elements have nominal resistances ranging from 2.5 to 4.5 kilohms and wherein the first and second diffused regions will provide nominally a 100 millivolt output with a 1 milliampere drive, and a pressure change of 300 mm of mercury.
7. A guidewire as in Claim 1 together with adhesive means carried by the housing for securing said pressure sensor in said housing.
8. A guidewire as in Claim 1 together with a velocity sensor mounted on the distal extremity of the guidewire so as to make possible simultaneous pressure and velocity measurements.
9. A guidewire as in Claim 1 together with first and second coil springs formed of different materials and having proximal and distal extremities, with the proximal extremity of the first coil being secured to the distal extremity of the flexible elongate member, an intermediate housing having proximal and distal extremities disposed between the first and second coil springs, the proximal extremity of the intermediate housing being secured to the distal extremity of the first coil spring, the distal extremity of the intermediate housing being secured to the proximal extremity of the second coil spring and a tip housing mounted on the distal extremity of the second coil spring.
10. A guidewire as in Claim 9 wherein said first named housing is the intermediate housing and wherein said pressure sensor is mounted in the intermediate housing.
11. A guidewire as in Claim 9 wherein said first named housing is the tip housing and wherein said pressure sensor is mounted in the tip housing.
12. A guidewire as in Claim 9 wherein said vessel is an arterial vessel with a stenosis therein and wherein a pressure sensor is mounted in each of the said intermediate and tip housings so as to make possible simultaneous pressure measurements on the proximal and distal extremities of the stenosis in the arterial vessel after the guide wire has been advanced through the stenosis.
13. A guidewire as in Claim 1 together with a balloon mounted on the distal extremity of the guidewire.
14. A guidewire as in Claim 1 together with means enclosing the pressure sensor within the housing and having a pin hole opening therein in communication with the well in the semiconductor crystal overlying the diaphragm.
15. A guidewire as in Claim 14 together with a viscous fluid underlying said covering means and serving to establish communication through the pin hole of the pressure of liquid in the vessel encountered by the distal extremity of the guidewire.
16. A guidewire having pressure sensing capabilities for measuring the pressure of blood in a vessel having a stenosis therein, a flexible elongate element having proximal and distal extremities, first and second housings mounted on the distal extremity of the flexible elongate member and being spaced apart a distance greater than the length of the stenosis, a pressure sensor mounted in each of the housings to make possible simultaneous pressure measurements proximal and distal of the stenosis when the distal extremity of the guidewire is disposed within the vessel with the pressure sensors being disposed on opposite sides of the stenosis in the vessel.
17. A guidewire as in Claim 16 together with first and second coils with the second coil being formed of a material different from the first coil, said first housing being mounted between the first and second coils and the second housing being mounted distally of the second coil.
18. A guidewire having pressure sensing capabilities for measuring the pressure proximal of and distal of a stenosis in a blood carrying vessel comprising a flexible elongate tubular member having proximal and distal extremities, an inflatable balloon secured to the distal extremity, means carried by the flexible elongate member for inflating and deflating the balloon, the balloon having a distal extremity, a housing, means securing the housing to the distal extremity of the flexible elongate tubular member distal of the balloon, the housing having a space therein, a pressure sensor disposed in the housing and having the leads extending through the balloon to the proximal extremity of a flexible elongate member whereby when the balloon is disposed in the stenosis in the vessel, the pressure of the blood distal of the stenosis can be measured.
19. Apparatus for measuring the pressure proximally and distally of a stenosis in a blood carrying vessel, a flexible elongate member having a diameter of .018" or less and having a distal extremity, a housing having a space therein secured to the distal extremity of the flexible elongate member, a pressure sensor mounted in the housing and leads connected to the pressure sensor and extending through the flexible elongate member, said pressure sensor including a movable diaphragm that is adapted to be placed in communication with the pressure of the blood in the vessel and deflecting in accordance with the pressure of the blood in the vessel, first and second resistive elements carried by the diaphragm, leads coupled to the resistive elements and extending to the proximal extremity of the flexible elongate member, means for supplying a current to the resistive elements and means for measuring changes in voltage as the diaphragm is deflected to ascertain the pressure being measured by the pressure sensor.
20. A method for making pressure measurements proximal and distal of a stenosis in a vessel carrying blood by the use of a guidewire having a distal extremity and having a diameter of .018" or less and having a pressure sensing capability carried by the distal extremity thereof, advancing the guidewire into the vessel so that its distal extremity is proximal of the stenosis and recording the pressure of the blood in the vessel proximal of the stenosis being measured by the distal extremity of the guidewire, advancing the guidewire through the stenosis, making another pressure measurement of the blood in the vessel distal of the stenosis and making a decision as to whether or not an angioplasty procedure is appropriate for the stenosis.
21. A method as in Claim 20 together with the step of measuring simultaneously the pressure of the blood proximal of the stenosis and the pressure of the blood distal of the stenosis.
Applications Claiming Priority (2)
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US30044594A | 1994-09-02 | 1994-09-02 | |
US08/300,445 | 1994-09-02 |
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CA002198909A Abandoned CA2198909A1 (en) | 1994-09-02 | 1995-08-04 | Ultra miniature pressure sensor and guidewire using the same and method |
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US (9) | US5715827A (en) |
EP (2) | EP1658808A1 (en) |
JP (1) | JP3619845B2 (en) |
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CA (1) | CA2198909A1 (en) |
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Families Citing this family (370)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1996007351A1 (en) * | 1994-09-02 | 1996-03-14 | Cardiometrics, Inc. | Ultra miniature pressure sensor and guidewire using the same and method |
SE9600334D0 (en) * | 1996-01-30 | 1996-01-30 | Radi Medical Systems | Combined flow, pressure and temperature sensor |
US6019728A (en) * | 1996-05-08 | 2000-02-01 | Kabushiki Kaisha Tokai Rika Denki Seisakusho | Catheter and sensor having pressure detecting function |
IL127138A0 (en) * | 1996-05-20 | 1999-09-22 | Percusurge Inc | Catheter balloon core wire |
DE19638813C1 (en) * | 1996-09-20 | 1998-03-05 | Sican F & E Gmbh Sibet | Measuring device for medical applications with an intracorporeally usable sensor element and method for its production |
ES2208963T3 (en) * | 1997-01-03 | 2004-06-16 | Biosense, Inc. | PRESSURE SENSITIVE VASCULAR ENDOPROTESIS. |
US6190332B1 (en) | 1998-02-19 | 2001-02-20 | Percusurge, Inc. | Core wire with shapeable tip |
US6355016B1 (en) | 1997-03-06 | 2002-03-12 | Medtronic Percusurge, Inc. | Catheter core wire |
EP0973438B1 (en) * | 1997-03-25 | 2003-11-26 | Radi Medical Systems Ab | Device for pressure measurements |
US6248083B1 (en) | 1997-03-25 | 2001-06-19 | Radi Medical Systems Ab | Device for pressure measurements |
JPH1133004A (en) * | 1997-07-15 | 1999-02-09 | Nippon B X I Kk | Guide wire with pressure sensor |
WO1999034724A2 (en) * | 1998-01-12 | 1999-07-15 | Florence Medical Ltd. | Characterizing blood vessel using multi-point pressure measurements |
CA2286107C (en) * | 1998-02-10 | 2007-01-09 | Biosense, Inc. | Improved catheter calibration |
ATE308923T1 (en) | 1998-03-05 | 2005-11-15 | Gil M Vardi | OPTICAL-ACUSTIC IMAGING DEVICE |
US6264611B1 (en) * | 1998-11-25 | 2001-07-24 | Ball Semiconductor, Inc. | Monitor for interventional procedures |
EP1479407B1 (en) * | 1998-12-23 | 2006-03-01 | Radi Medical Systems Ab | Sensor and guide wire assembly |
US6142958A (en) | 1998-12-23 | 2000-11-07 | Radi Medical Systems Ab | Sensor and guide wire assembly |
US6210339B1 (en) * | 1999-03-03 | 2001-04-03 | Endosonics Corporation | Flexible elongate member having one or more electrical contacts |
US6471656B1 (en) | 1999-06-25 | 2002-10-29 | Florence Medical Ltd | Method and system for pressure based measurements of CFR and additional clinical hemodynamic parameters |
US20030032886A1 (en) * | 1999-03-09 | 2003-02-13 | Elhanan Dgany | System for determining coronary flow reserve (CFR) value for a stenosed blood vessel, CFR processor therefor, and method therefor |
US6546787B1 (en) | 1999-03-25 | 2003-04-15 | Regents Of The University Of Minnesota | Means and method for modeling and treating specific tissue structures |
ATE389353T1 (en) | 1999-05-27 | 2008-04-15 | Radi Medical Systems | METHOD FOR TEMPERATURE COMPENSATION IN A COMBINED PRESSURE AND TEMPERATURE SENSOR |
US6409677B1 (en) | 1999-05-27 | 2002-06-25 | Radi Medical Systems Ab | Method for temperature compensation in a combined pressure and temperature sensor |
DE20012237U1 (en) * | 1999-07-26 | 2000-10-12 | Storz Karl Gmbh & Co Kg | Medical instrument with a contactlessly readable information carrier |
WO2001013779A2 (en) * | 1999-08-25 | 2001-03-01 | Florence Medical Ltd. | A method and system for stenosis identification, localization and characterization using pressure measurements |
US6265792B1 (en) | 1999-09-08 | 2001-07-24 | Endosonics Corporation | Medical device having precision interconnect |
US6394986B1 (en) | 1999-11-06 | 2002-05-28 | Millar Instruments, Inc. | Pressure sensing module for a catheter pressure transducer |
DE60138360D1 (en) | 2000-01-04 | 2009-05-28 | Medtronic Vascular Inc | DEVICE FOR ADJUSTING A CHANNEL BETWEEN ADJUSTING BODY LIQUIDS |
US6685716B1 (en) | 2000-01-04 | 2004-02-03 | Transvascular, Inc. | Over-the-wire apparatus and method for open surgery making of fluid connection between two neighboring vessels |
US6561038B2 (en) | 2000-01-06 | 2003-05-13 | Rosemount Inc. | Sensor with fluid isolation barrier |
US6508129B1 (en) | 2000-01-06 | 2003-01-21 | Rosemount Inc. | Pressure sensor capsule with improved isolation |
DE60108217T2 (en) | 2000-01-06 | 2005-12-29 | Rosemount Inc., Eden Prairie | CORN GROWTH METHOD FOR THE PRODUCTION OF AN ELECTRICAL CONNECTION FOR MICROELECTROMECHANICAL SYSTEMS (MEMS) |
US6520020B1 (en) | 2000-01-06 | 2003-02-18 | Rosemount Inc. | Method and apparatus for a direct bonded isolated pressure sensor |
US6505516B1 (en) | 2000-01-06 | 2003-01-14 | Rosemount Inc. | Capacitive pressure sensing with moving dielectric |
US6264612B1 (en) * | 2000-01-14 | 2001-07-24 | Children's Hospital Medical Center | Catheter with mechano-responsive element for sensing physiological conditions |
JP3619464B2 (en) * | 2000-03-21 | 2005-02-09 | ラディ・メディカル・システムズ・アクチェボラーグ | Resonant pressure transducer system |
SE0001213D0 (en) * | 2000-04-04 | 2000-04-04 | Patrik Melvaas | Sensing device |
US6746404B2 (en) | 2000-12-18 | 2004-06-08 | Biosense, Inc. | Method for anchoring a medical device between tissue |
US6658300B2 (en) | 2000-12-18 | 2003-12-02 | Biosense, Inc. | Telemetric reader/charger device for medical sensor |
US6652464B2 (en) | 2000-12-18 | 2003-11-25 | Biosense, Inc. | Intracardiac pressure monitoring method |
US6783499B2 (en) | 2000-12-18 | 2004-08-31 | Biosense, Inc. | Anchoring mechanism for implantable telemetric medical sensor |
US6638231B2 (en) * | 2000-12-18 | 2003-10-28 | Biosense, Inc. | Implantable telemetric medical sensor and method |
US6636769B2 (en) | 2000-12-18 | 2003-10-21 | Biosense, Inc. | Telemetric medical system and method |
WO2002056940A2 (en) * | 2001-01-22 | 2002-07-25 | Integrated Sensing Systems, Inc. | Sensing catheter system and method of fabrication |
US20040243175A1 (en) * | 2001-03-12 | 2004-12-02 | Don Michael T. Anthony | Vascular obstruction removal system and method |
US6673023B2 (en) * | 2001-03-23 | 2004-01-06 | Stryker Puerto Rico Limited | Micro-invasive breast biopsy device |
US7100148B2 (en) * | 2001-03-16 | 2006-08-29 | Sap Ag | Development computer, development program for combining components to applications, using component descriptors related to the components, method, and computer program |
US6881194B2 (en) * | 2001-03-21 | 2005-04-19 | Asahi Intec Co., Ltd. | Wire-stranded medical hollow tube, and a medical guide wire |
US20020138091A1 (en) * | 2001-03-23 | 2002-09-26 | Devonrex, Inc. | Micro-invasive nucleotomy device and method |
US20020138021A1 (en) * | 2001-03-23 | 2002-09-26 | Devonrex, Inc. | Micro-invasive tissue removal device |
US6585660B2 (en) * | 2001-05-18 | 2003-07-01 | Jomed Inc. | Signal conditioning device for interfacing intravascular sensors having varying operational characteristics to a physiology monitor |
US6890303B2 (en) * | 2001-05-31 | 2005-05-10 | Matthew Joseph Fitz | Implantable device for monitoring aneurysm sac parameters |
US8579825B2 (en) * | 2001-06-15 | 2013-11-12 | Radi Medical Systems Ab | Electrically conductive guide wire |
US7455666B2 (en) | 2001-07-13 | 2008-11-25 | Board Of Regents, The University Of Texas System | Methods and apparatuses for navigating the subarachnoid space |
US6912759B2 (en) * | 2001-07-20 | 2005-07-05 | Rosemount Aerospace Inc. | Method of manufacturing a thin piezo resistive pressure sensor |
JP2005504275A (en) * | 2001-09-18 | 2005-02-10 | ユー.エス. ジェノミクス, インコーポレイテッド | Differential tagging of polymers for high-resolution linear analysis |
US6663570B2 (en) * | 2002-02-27 | 2003-12-16 | Volcano Therapeutics, Inc. | Connector for interfacing intravascular sensors to a physiology monitor |
US7134994B2 (en) | 2002-05-20 | 2006-11-14 | Volcano Corporation | Multipurpose host system for invasive cardiovascular diagnostic measurement acquisition and display |
US7282330B2 (en) | 2002-05-28 | 2007-10-16 | U.S. Genomics, Inc. | Methods and apparati using single polymer analysis |
US7371520B2 (en) * | 2002-05-28 | 2008-05-13 | U.S. Genomics, Inc. | Methods and apparati using single polymer analysis |
US7060075B2 (en) * | 2002-07-18 | 2006-06-13 | Biosense, Inc. | Distal targeting of locking screws in intramedullary nails |
US7139613B2 (en) * | 2002-09-25 | 2006-11-21 | Medtronic, Inc. | Implantable medical device communication system with pulsed power biasing |
US7013178B2 (en) * | 2002-09-25 | 2006-03-14 | Medtronic, Inc. | Implantable medical device communication system |
ATE536201T1 (en) * | 2002-09-26 | 2011-12-15 | Pacesetter Inc | CARDIOVASCULAR ANCHORING DEVICE |
US8303511B2 (en) | 2002-09-26 | 2012-11-06 | Pacesetter, Inc. | Implantable pressure transducer system optimized for reduced thrombosis effect |
US7245789B2 (en) | 2002-10-07 | 2007-07-17 | Vascular Imaging Corporation | Systems and methods for minimally-invasive optical-acoustic imaging |
US20040102806A1 (en) * | 2002-11-27 | 2004-05-27 | Scimed Life Systems, Inc. | Intravascular filter monitoring |
US20060106321A1 (en) * | 2003-01-16 | 2006-05-18 | Galil Medical Ltd. | Device, system, and method for detecting, localizing, and characterizing plaque-induced stenosis of a blood vessel |
WO2004062525A2 (en) | 2003-01-16 | 2004-07-29 | Galil Medical Ltd. | Device, system, and method for detecting and localizing obstruction within a blood vessel |
SE526036C2 (en) * | 2003-07-02 | 2005-06-21 | Radi Medical Systems | Sensor for medical intravascular measurements, has mounting base that extends in direction perpendicular to longitudinal axis of sensor, fixed with core wire such that clearance is obtained between sensitive end of chip and core wire |
US6993974B2 (en) * | 2003-07-02 | 2006-02-07 | Radi Medical Systems Ab | Sensor and guide wire assembly |
GB0329019D0 (en) * | 2003-12-15 | 2004-01-14 | Imp College Innovations Ltd | Acoustic wave devices |
US20080051660A1 (en) * | 2004-01-16 | 2008-02-28 | The University Of Houston System | Methods and apparatuses for medical imaging |
US20050159801A1 (en) * | 2004-01-16 | 2005-07-21 | Medtronic, Inc. | Novel implantable lead including sensor |
US7286884B2 (en) | 2004-01-16 | 2007-10-23 | Medtronic, Inc. | Implantable lead including sensor |
JP4602993B2 (en) * | 2004-01-16 | 2010-12-22 | ボストン サイエンティフィック リミテッド | Method and apparatus for medical imaging |
WO2005069974A2 (en) * | 2004-01-23 | 2005-08-04 | Children's Hospital Medical Center | Microsensor catheter and method for making the same |
EP1715788B1 (en) | 2004-02-17 | 2011-09-07 | Philips Electronics LTD | Method and apparatus for registration, verification, and referencing of internal organs |
US9949647B2 (en) | 2004-06-04 | 2018-04-24 | St. Jude Medical Coordination Center Bvba | Sensor and guide wire assembly |
US7263894B2 (en) * | 2004-06-07 | 2007-09-04 | Radi Medical Systems Ab | Sensor and guide wire assembly |
SE0402145D0 (en) * | 2004-09-08 | 2004-09-08 | Radi Medical Systems | Pressure measurement system |
US8277386B2 (en) | 2004-09-27 | 2012-10-02 | Volcano Corporation | Combination sensor guidewire and methods of use |
US7722565B2 (en) | 2004-11-05 | 2010-05-25 | Traxtal, Inc. | Access system |
KR100689707B1 (en) * | 2004-11-12 | 2007-03-08 | 삼성전자주식회사 | Bank selection signal control circuit, semiconductor memory device having the same and method for control bank selection signal |
US7751868B2 (en) | 2004-11-12 | 2010-07-06 | Philips Electronics Ltd | Integrated skin-mounted multifunction device for use in image-guided surgery |
US7805269B2 (en) | 2004-11-12 | 2010-09-28 | Philips Electronics Ltd | Device and method for ensuring the accuracy of a tracking device in a volume |
US20060116602A1 (en) * | 2004-12-01 | 2006-06-01 | Alden Dana A | Medical sensing device and system |
US20060135953A1 (en) * | 2004-12-22 | 2006-06-22 | Wlodzimierz Kania | Tissue ablation system including guidewire with sensing element |
US7854747B2 (en) | 2005-01-03 | 2010-12-21 | Crux Biomedical, Inc. | Endoluminal filter |
CA2588002A1 (en) | 2005-01-18 | 2006-07-27 | Traxtal Inc. | Method and apparatus for guiding an instrument to a target in the lung |
CA2587986A1 (en) | 2005-01-18 | 2006-07-27 | Traxtal Inc. | Electromagnetically tracked k-wire device |
US20080021336A1 (en) | 2006-04-24 | 2008-01-24 | Dobak John D Iii | Devices and methods for accelerometer-based characterization of cardiac synchrony and dyssynchrony |
US20060178586A1 (en) * | 2005-02-07 | 2006-08-10 | Dobak John D Iii | Devices and methods for accelerometer-based characterization of cardiac function and identification of LV target pacing zones |
US7231829B2 (en) | 2005-03-31 | 2007-06-19 | Medtronic, Inc. | Monolithic integrated circuit/pressure sensor on pacing lead |
DE602006019117D1 (en) | 2005-06-21 | 2011-02-03 | Us Government | DEVICE AND METHOD FOR A TRACKABLE ULTRASOUND |
CA2613360A1 (en) | 2005-06-21 | 2007-01-04 | Traxtal Inc. | System, method and apparatus for navigated therapy and diagnosis |
DE102005032755B4 (en) * | 2005-07-13 | 2014-09-04 | Siemens Aktiengesellschaft | System for performing and monitoring minimally invasive procedures |
US9661991B2 (en) | 2005-08-24 | 2017-05-30 | Koninklijke Philips N.V. | System, method and devices for navigated flexible endoscopy |
US7599588B2 (en) | 2005-11-22 | 2009-10-06 | Vascular Imaging Corporation | Optical imaging probe connector |
JP4755890B2 (en) * | 2005-12-09 | 2011-08-24 | 佳彦 平尾 | Measuring device and measuring system |
US7927288B2 (en) * | 2006-01-20 | 2011-04-19 | The Regents Of The University Of Michigan | In situ tissue analysis device and method |
ES2347010T3 (en) * | 2006-04-28 | 2010-10-22 | Radi Medical Systems Ab | SENSOR AND CABLE GUIDE ASSEMBLY. |
US20070255145A1 (en) * | 2006-04-28 | 2007-11-01 | Radi Medical Systems Ab | Sensor and guide wire assembly |
US20110276127A1 (en) * | 2006-05-24 | 2011-11-10 | Forster David C | Multiple inflation of an expandable member as a precursor to an implant procedure |
US9101264B2 (en) | 2006-06-15 | 2015-08-11 | Peerbridge Health, Inc. | Wireless electrode arrangement and method for patient monitoring via electrocardiography |
US7979111B2 (en) * | 2006-06-15 | 2011-07-12 | Angelo Joseph Acquista | Wireless electrode arrangement and method for patient monitoring via electrocardiography |
DE102006030407A1 (en) * | 2006-06-29 | 2008-01-03 | Werthschützky, Roland, Prof. Dr.-Ing. | Force sensor with asymmetric basic body for detecting at least one force component |
DE102006031635A1 (en) * | 2006-07-06 | 2008-01-17 | Werthschützky, Roland, Prof. Dr.-Ing. | Minaturisable force sensor for detecting a force vector |
US9867530B2 (en) | 2006-08-14 | 2018-01-16 | Volcano Corporation | Telescopic side port catheter device with imaging system and method for accessing side branch occlusions |
US11234650B2 (en) | 2006-11-20 | 2022-02-01 | St. Jude Medical Coordination Center Bvba | Measurement system |
US8174395B2 (en) * | 2006-11-20 | 2012-05-08 | St. Jude Medical Systems Ab | Transceiver unit in a measurement system |
US7967761B2 (en) * | 2006-12-01 | 2011-06-28 | Radi Medical Systems Ab | Sensor and guide wire assembly |
DE102006061178A1 (en) * | 2006-12-22 | 2008-06-26 | Siemens Ag | Medical system for carrying out and monitoring a minimal invasive intrusion, especially for treating electro-physiological diseases, has X-ray equipment and a control/evaluation unit |
US7946997B2 (en) * | 2007-02-16 | 2011-05-24 | Radi Medical Systems Ab | Measurement system to measure a physiological condition in a body |
DE102007012060A1 (en) * | 2007-03-13 | 2008-09-18 | Robert Bosch Gmbh | Sensor arrangement for pressure measurement |
US9596993B2 (en) | 2007-07-12 | 2017-03-21 | Volcano Corporation | Automatic calibration systems and methods of use |
WO2009009799A1 (en) | 2007-07-12 | 2009-01-15 | Volcano Corporation | Catheter for in vivo imaging |
US10219780B2 (en) | 2007-07-12 | 2019-03-05 | Volcano Corporation | OCT-IVUS catheter for concurrent luminal imaging |
US7472601B1 (en) * | 2007-09-21 | 2009-01-06 | Radi Medical Systems Ab | Sensor for intravascular measurements within a living body |
EP2767227A1 (en) * | 2007-09-25 | 2014-08-20 | Radi Medical Systems Ab | Pressure wire assembly |
US9289137B2 (en) | 2007-09-28 | 2016-03-22 | Volcano Corporation | Intravascular pressure devices incorporating sensors manufactured using deep reactive ion etching |
EP2211701A1 (en) * | 2007-10-26 | 2010-08-04 | St. Jude Medical Systems AB | Sensor guide wire with micro-cable winding |
US8974398B2 (en) * | 2007-11-08 | 2015-03-10 | St. Jude Medical Coordination Center Bvba | Removable energy source for sensor guidewire |
US7998089B2 (en) * | 2007-11-08 | 2011-08-16 | Radi Medical Systems Ab | Method of making a guide wire based assembly and reusing an energy source |
US8968345B2 (en) * | 2008-03-24 | 2015-03-03 | Covidien Lp | Surgical introducer with indicators |
US8298156B2 (en) | 2008-09-11 | 2012-10-30 | Acist Medical Systems, Inc. | Physiological sensor delivery device and method |
EP2356412B1 (en) | 2008-10-02 | 2012-08-15 | Vascular Imaging Corporation | Optical ultrasound receiver |
EP2417484B1 (en) | 2008-10-31 | 2014-12-31 | Vascular Imaging Corporation | Optical imaging probe connector |
US8594799B2 (en) * | 2008-10-31 | 2013-11-26 | Advanced Bionics | Cochlear electrode insertion |
US9526418B2 (en) | 2008-12-04 | 2016-12-27 | Deep Science, Llc | Device for storage of intraluminally generated power |
US9759202B2 (en) * | 2008-12-04 | 2017-09-12 | Deep Science, Llc | Method for generation of power from intraluminal pressure changes |
US9567983B2 (en) * | 2008-12-04 | 2017-02-14 | Deep Science, Llc | Method for generation of power from intraluminal pressure changes |
US20100140958A1 (en) * | 2008-12-04 | 2010-06-10 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Method for powering devices from intraluminal pressure changes |
US9353733B2 (en) | 2008-12-04 | 2016-05-31 | Deep Science, Llc | Device and system for generation of power from intraluminal pressure changes |
US9631610B2 (en) | 2008-12-04 | 2017-04-25 | Deep Science, Llc | System for powering devices from intraluminal pressure changes |
US9366938B1 (en) | 2009-02-17 | 2016-06-14 | Vescent Photonics, Inc. | Electro-optic beam deflector device |
US20110092955A1 (en) * | 2009-10-07 | 2011-04-21 | Purdy Phillip D | Pressure-Sensing Medical Devices, Systems and Methods, and Methods of Forming Medical Devices |
WO2011053766A1 (en) * | 2009-10-30 | 2011-05-05 | Advanced Bionics, Llc | Steerable stylet |
US8771289B2 (en) | 2009-12-21 | 2014-07-08 | Acist Medical Systems, Inc. | Thrombus removal device and system |
US8478384B2 (en) | 2010-01-19 | 2013-07-02 | Lightlab Imaging, Inc. | Intravascular optical coherence tomography system with pressure monitoring interface and accessories |
US20110184313A1 (en) * | 2010-01-22 | 2011-07-28 | The Regents Of The University Of Michigan | Cauterization Device and Method of Cauterizing |
US8396563B2 (en) | 2010-01-29 | 2013-03-12 | Medtronic, Inc. | Clock synchronization in an implantable medical device system |
US20110245693A1 (en) * | 2010-03-30 | 2011-10-06 | Boston Scientific Scimed, Inc. | Intravascular pressure sensing |
AU2011242697B2 (en) | 2010-04-21 | 2015-01-22 | Government Of The United States | Fluoroscopy-independent, endovascular aortic occlusion system |
US20140142398A1 (en) * | 2010-06-13 | 2014-05-22 | Angiometrix Corporation | Multifunctional guidewire assemblies and system for analyzing anatomical and functional parameters |
US8569851B2 (en) | 2010-06-18 | 2013-10-29 | General Electric Company | Sensor and method for fabricating the same |
US8435821B2 (en) | 2010-06-18 | 2013-05-07 | General Electric Company | Sensor and method for fabricating the same |
SE1050741A1 (en) * | 2010-07-06 | 2012-01-07 | St Jude Medical Systems Ab | Sensor element |
US8479585B2 (en) | 2010-09-08 | 2013-07-09 | Micropen Technologies Corporation | Pressure sensing or force generating device |
WO2012061935A1 (en) | 2010-11-09 | 2012-05-18 | Opsens Inc. | Guidewire with internal pressure sensor |
SE537180C2 (en) | 2010-11-12 | 2015-02-24 | St Jude Medical Systems Ab | Extracorporeal interface unit for an intravascular measurement system |
WO2012082715A2 (en) * | 2010-12-13 | 2012-06-21 | Case Western Reserve University | Device with external pressure sensors for enhancing patient care and methods of using same |
US11141063B2 (en) | 2010-12-23 | 2021-10-12 | Philips Image Guided Therapy Corporation | Integrated system architectures and methods of use |
US9247909B2 (en) * | 2010-12-31 | 2016-02-02 | Volcano Corporation | Lumen based pressure sensing guidewire system with distortion correction |
US11040140B2 (en) | 2010-12-31 | 2021-06-22 | Philips Image Guided Therapy Corporation | Deep vein thrombosis therapeutic methods |
GB201100136D0 (en) * | 2011-01-06 | 2011-02-23 | Davies Helen C S | Apparatus and method of characterising a narrowing in a filled tube |
GB201100137D0 (en) | 2011-01-06 | 2011-02-23 | Davies Helen C S | Apparatus and method of assessing a narrowing in a fluid tube |
US20120215133A1 (en) * | 2011-02-22 | 2012-08-23 | Brad Jeffrey Neiman | Catheter tip device and method for manufacturing same |
US8662200B2 (en) | 2011-03-24 | 2014-03-04 | Merlin Technology Inc. | Sonde with integral pressure sensor and method |
EP2706908B1 (en) | 2011-05-11 | 2019-07-10 | Acist Medical Systems, Inc. | Intravascular sensing system |
US9610064B2 (en) | 2011-05-31 | 2017-04-04 | Desmond Adler | Multimodal imaging system, apparatus, and methods |
AU2012271236A1 (en) * | 2011-06-13 | 2014-01-16 | Angiometrix Corporation | Multifunctional guidewire assemblies and system for analyzing anatomical and functional parameters |
US9295447B2 (en) | 2011-08-17 | 2016-03-29 | Volcano Corporation | Systems and methods for identifying vascular borders |
WO2013028612A2 (en) | 2011-08-20 | 2013-02-28 | Volcano Corporation | Devices, systems, and methods for visually depicting a vessel and evaluating treatment options |
US9339348B2 (en) | 2011-08-20 | 2016-05-17 | Imperial Colege of Science, Technology and Medicine | Devices, systems, and methods for assessing a vessel |
WO2015109339A1 (en) * | 2014-01-16 | 2015-07-23 | Volcano Corporation | Devices, systems, and methods for assessing a vessel |
US10888232B2 (en) | 2011-08-20 | 2021-01-12 | Philips Image Guided Therapy Corporation | Devices, systems, and methods for assessing a vessel |
WO2013033592A1 (en) | 2011-08-31 | 2013-03-07 | Volcano Corporation | Optical-electrical rotary joint and methods of use |
US10463259B2 (en) | 2011-10-28 | 2019-11-05 | Three Rivers Cardiovascular Systems Inc. | System and apparatus comprising a multi-sensor catheter for right heart and pulmonary artery catheterization |
US20140243688A1 (en) | 2011-10-28 | 2014-08-28 | Three Rivers Cardiovascular Systems Inc. | Fluid temperature and flow sensor apparatus and system for cardiovascular and other medical applications |
US20130109980A1 (en) * | 2011-11-01 | 2013-05-02 | Tat-Jin Teo | Systems and methods for a wireless vascular pressure measurement device |
SE1151051A1 (en) * | 2011-11-09 | 2013-05-10 | Koninklijke Philips Electronics Nv | Sensor wire |
US10426501B2 (en) | 2012-01-13 | 2019-10-01 | Crux Biomedical, Inc. | Retrieval snare device and method |
US10548706B2 (en) | 2012-01-13 | 2020-02-04 | Volcano Corporation | Retrieval snare device and method |
US10736519B2 (en) * | 2012-01-19 | 2020-08-11 | Philips Image Guided Therapy Corporation | Interface devices, systems, and methods for use with intravascular pressure monitoring devices |
US10213288B2 (en) | 2012-03-06 | 2019-02-26 | Crux Biomedical, Inc. | Distal protection filter |
US9492071B2 (en) * | 2012-04-05 | 2016-11-15 | Stryker Corporation | In-joint sensor for a surgical fluid management pump system |
US20130289377A1 (en) | 2012-04-27 | 2013-10-31 | Medtronic, Inc. | Method and apparatus for cardiac function monitoring |
EP2856098B1 (en) | 2012-05-25 | 2019-10-16 | Vascular Imaging Corporation | Optical fiber pressure sensor |
CN105142506A (en) | 2012-08-27 | 2015-12-09 | 波士顿科学国际有限公司 | Pressure-sensing medical devices and medical device systems |
CA2882198A1 (en) * | 2012-08-31 | 2014-03-06 | Volcano Corporation | Mounting structures for components of intravascular devices |
WO2014036477A1 (en) | 2012-08-31 | 2014-03-06 | Volcano Corporation | Pressure sensing intravascular devices with reduced drift and associated systems and methods |
JP6086984B2 (en) * | 2012-09-17 | 2017-03-01 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Pressure sensing guide wire |
WO2014055729A1 (en) | 2012-10-04 | 2014-04-10 | Vascular Imaging Corporatoin | Polarization scrambling for intra-body fiber optic sensor |
JP2015532536A (en) | 2012-10-05 | 2015-11-09 | デイビッド ウェルフォード, | System and method for amplifying light |
US9858668B2 (en) | 2012-10-05 | 2018-01-02 | Volcano Corporation | Guidewire artifact removal in images |
US9324141B2 (en) | 2012-10-05 | 2016-04-26 | Volcano Corporation | Removal of A-scan streaking artifact |
US9286673B2 (en) | 2012-10-05 | 2016-03-15 | Volcano Corporation | Systems for correcting distortions in a medical image and methods of use thereof |
US9367965B2 (en) | 2012-10-05 | 2016-06-14 | Volcano Corporation | Systems and methods for generating images of tissue |
US10070827B2 (en) | 2012-10-05 | 2018-09-11 | Volcano Corporation | Automatic image playback |
US9307926B2 (en) | 2012-10-05 | 2016-04-12 | Volcano Corporation | Automatic stent detection |
US11272845B2 (en) | 2012-10-05 | 2022-03-15 | Philips Image Guided Therapy Corporation | System and method for instant and automatic border detection |
US10568586B2 (en) | 2012-10-05 | 2020-02-25 | Volcano Corporation | Systems for indicating parameters in an imaging data set and methods of use |
US9292918B2 (en) | 2012-10-05 | 2016-03-22 | Volcano Corporation | Methods and systems for transforming luminal images |
US9840734B2 (en) | 2012-10-22 | 2017-12-12 | Raindance Technologies, Inc. | Methods for analyzing DNA |
JP6322210B2 (en) | 2012-12-13 | 2018-05-09 | ボルケーノ コーポレイション | Devices, systems, and methods for targeted intubation |
WO2014099899A1 (en) | 2012-12-20 | 2014-06-26 | Jeremy Stigall | Smooth transition catheters |
US10942022B2 (en) | 2012-12-20 | 2021-03-09 | Philips Image Guided Therapy Corporation | Manual calibration of imaging system |
US20140180030A1 (en) * | 2012-12-20 | 2014-06-26 | Volcano Corporation | Intravascular blood pressure and velocity wire |
EP2934282B1 (en) | 2012-12-20 | 2020-04-29 | Volcano Corporation | Locating intravascular images |
US10939826B2 (en) | 2012-12-20 | 2021-03-09 | Philips Image Guided Therapy Corporation | Aspirating and removing biological material |
JP2016504589A (en) | 2012-12-20 | 2016-02-12 | ナサニエル ジェイ. ケンプ, | Optical coherence tomography system reconfigurable between different imaging modes |
US11406498B2 (en) | 2012-12-20 | 2022-08-09 | Philips Image Guided Therapy Corporation | Implant delivery system and implants |
US10413317B2 (en) | 2012-12-21 | 2019-09-17 | Volcano Corporation | System and method for catheter steering and operation |
CA2895769A1 (en) | 2012-12-21 | 2014-06-26 | Douglas Meyer | Rotational ultrasound imaging catheter with extended catheter body telescope |
JP2016508757A (en) | 2012-12-21 | 2016-03-24 | ジェイソン スペンサー, | System and method for graphical processing of medical data |
US10327695B2 (en) | 2012-12-21 | 2019-06-25 | Volcano Corporation | Functional gain measurement technique and representation |
WO2014099760A1 (en) | 2012-12-21 | 2014-06-26 | Mai Jerome | Ultrasound imaging with variable line density |
EP2934304B1 (en) | 2012-12-21 | 2021-10-13 | Philips Image Guided Therapy Corporation | Multi-sensor devices |
JP6290250B2 (en) | 2012-12-21 | 2018-03-07 | ボルケーノ コーポレイション | Pressure sensing endovascular device, system, and method |
US10058284B2 (en) | 2012-12-21 | 2018-08-28 | Volcano Corporation | Simultaneous imaging, monitoring, and therapy |
US9615878B2 (en) | 2012-12-21 | 2017-04-11 | Volcano Corporation | Device, system, and method for imaging and tissue characterization of ablated tissue |
WO2014100458A1 (en) * | 2012-12-21 | 2014-06-26 | Volcano Corporation | Mounting structures for components of intravascular devices |
US10191220B2 (en) | 2012-12-21 | 2019-01-29 | Volcano Corporation | Power-efficient optical circuit |
US20140180089A1 (en) * | 2012-12-21 | 2014-06-26 | Volcano Corporation | System and method for guidewire control |
US9383263B2 (en) | 2012-12-21 | 2016-07-05 | Volcano Corporation | Systems and methods for narrowing a wavelength emission of light |
US20140180066A1 (en) | 2012-12-21 | 2014-06-26 | Volcano Corporation | Introducer having a flow sensor |
US9486143B2 (en) | 2012-12-21 | 2016-11-08 | Volcano Corporation | Intravascular forward imaging device |
US9612105B2 (en) | 2012-12-21 | 2017-04-04 | Volcano Corporation | Polarization sensitive optical coherence tomography system |
JP2016501623A (en) | 2012-12-21 | 2016-01-21 | アンドリュー ハンコック, | System and method for multipath processing of image signals |
CA2896662A1 (en) | 2012-12-28 | 2014-07-03 | Volcano Corporation | Intravascular devices having information stored thereon and/or wireless communication functionality, including associated devices, systems, and methods |
US9624095B2 (en) * | 2012-12-28 | 2017-04-18 | Volcano Corporation | Capacitive intravascular pressure-sensing devices and associated systems and methods |
US20140187978A1 (en) | 2012-12-28 | 2014-07-03 | Volcano Corporation | Intravascular Devices Having Information Stored Thereon And/Or Wireless Communication Functionality, Including Associated Devices, Systems, And Methods |
US20140187984A1 (en) * | 2012-12-31 | 2014-07-03 | Volcano Corporation | In-Wall Hypotube Sensor Mount for Sensored Guidewire |
US10791991B2 (en) * | 2012-12-31 | 2020-10-06 | Philips Image Guided Therapy Corporation | Intravascular devices, systems, and methods |
US9770172B2 (en) | 2013-03-07 | 2017-09-26 | Volcano Corporation | Multimodal segmentation in intravascular images |
US10226597B2 (en) | 2013-03-07 | 2019-03-12 | Volcano Corporation | Guidewire with centering mechanism |
US20140276923A1 (en) | 2013-03-12 | 2014-09-18 | Volcano Corporation | Vibrating catheter and methods of use |
US9351698B2 (en) | 2013-03-12 | 2016-05-31 | Lightlab Imaging, Inc. | Vascular data processing and image registration systems, methods, and apparatuses |
CN105228518B (en) | 2013-03-12 | 2018-10-09 | 火山公司 | System and method for diagnosing coronal microvascular diseases |
US11026591B2 (en) | 2013-03-13 | 2021-06-08 | Philips Image Guided Therapy Corporation | Intravascular pressure sensor calibration |
US9301687B2 (en) | 2013-03-13 | 2016-04-05 | Volcano Corporation | System and method for OCT depth calibration |
CN105120759B (en) | 2013-03-13 | 2018-02-23 | 火山公司 | System and method for producing image from rotation intravascular ultrasound equipment |
US20140275950A1 (en) * | 2013-03-13 | 2014-09-18 | Volcano Corporation | Imaging guidewire with pressure sensing |
WO2014159949A1 (en) * | 2013-03-13 | 2014-10-02 | Millett Bret | Sensing guidewires with centering element and methods of use thereof |
US10292677B2 (en) | 2013-03-14 | 2019-05-21 | Volcano Corporation | Endoluminal filter having enhanced echogenic properties |
US9592027B2 (en) | 2013-03-14 | 2017-03-14 | Volcano Corporation | System and method of adventitial tissue characterization |
CN105208947B (en) | 2013-03-14 | 2018-10-12 | 火山公司 | Filter with echoing characteristic |
WO2014159702A2 (en) | 2013-03-14 | 2014-10-02 | Vascular Imaging Corporation | Optical fiber ribbon imaging guidewire and methods |
US10219887B2 (en) | 2013-03-14 | 2019-03-05 | Volcano Corporation | Filters with echogenic characteristics |
US20140260644A1 (en) * | 2013-03-15 | 2014-09-18 | Sensonetics, Inc. | Modular Systems for Piezoresistive Transducers |
US20140276143A1 (en) * | 2013-03-15 | 2014-09-18 | Volcano Corporation | Smart Interface Cable for Coupling a Diagnostic Medical Device With a Medical Measurement System |
JP6532857B2 (en) | 2013-03-15 | 2019-06-19 | ボルケーノ コーポレイション | Interface device, system and method for use with an intravascular pressure monitoring device |
US20140276117A1 (en) * | 2013-03-15 | 2014-09-18 | Volcano Corporation | Intravascular Devices, Systems, and Methods |
CN105392432B (en) * | 2013-03-15 | 2019-04-30 | 火山公司 | Distal embolic protection system and method with pressure and ultrasonic wave characteristic |
EP2968854B1 (en) | 2013-03-15 | 2019-04-24 | Boston Scientific Scimed, Inc. | Pressure sensing guidewire |
WO2014190195A1 (en) | 2013-05-22 | 2014-11-27 | Boston Scientific Scimed, Inc. | Pressure sensing guidewire systems including an optical connector cable |
US10835183B2 (en) | 2013-07-01 | 2020-11-17 | Zurich Medical Corporation | Apparatus and method for intravascular measurements |
KR101697908B1 (en) | 2013-07-01 | 2017-01-18 | 쥬어리크 메디컬 코퍼레이션 | Apparatus and method for intravascular measurements |
EP3024381B1 (en) | 2013-07-26 | 2019-06-19 | Boston Scientific Scimed, Inc. | Ffr sensor head design that minimizes stress induced pressure offsets |
CN105636508B (en) | 2013-08-14 | 2019-09-27 | 波士顿科学国际有限公司 | Medical instrument system including tapered core fibre |
CA2923419A1 (en) * | 2013-09-09 | 2015-03-12 | Pryor Medical Devices, Inc. | Low-profile occlusion catheter |
US10327645B2 (en) | 2013-10-04 | 2019-06-25 | Vascular Imaging Corporation | Imaging techniques using an imaging guidewire |
US9775523B2 (en) | 2013-10-14 | 2017-10-03 | Boston Scientific Scimed, Inc. | Pressure sensing guidewire and methods for calculating fractional flow reserve |
WO2015057735A1 (en) | 2013-10-15 | 2015-04-23 | Cedars-Sinai Medical Center | Anatomically-orientated and self-positioning transcatheter mitral valve |
US10543078B2 (en) | 2013-10-16 | 2020-01-28 | Cedars-Sinai Medical Center | Modular dis-assembly of transcatheter valve replacement devices and uses thereof |
CN105611889A (en) | 2013-10-17 | 2016-05-25 | 雪松-西奈医学中心 | Device to percutaneously treatment of heart valve embolization |
EP3057495B1 (en) * | 2013-10-18 | 2020-07-15 | Volcano Corporation | System for assessing a stenosis in a blood vessel with optimized proximal and distal pressure measurements |
US9877660B2 (en) | 2013-11-14 | 2018-01-30 | Medtronic Vascular Galway | Systems and methods for determining fractional flow reserve without adenosine or other pharmalogical agent |
US10130269B2 (en) | 2013-11-14 | 2018-11-20 | Medtronic Vascular, Inc | Dual lumen catheter for providing a vascular pressure measurement |
US10687832B2 (en) | 2013-11-18 | 2020-06-23 | Koninklijke Philips N.V. | Methods and devices for thrombus dispersal |
EP3076881B1 (en) | 2013-11-18 | 2022-01-05 | Koninklijke Philips N.V. | Guided thrombus dispersal catheter |
US10537255B2 (en) | 2013-11-21 | 2020-01-21 | Phyzhon Health Inc. | Optical fiber pressure sensor |
WO2015077328A1 (en) * | 2013-11-22 | 2015-05-28 | Volcano Corporation | Sensor mounting assembly for sensored guidewire and associated devices, systems, and methods |
US10820989B2 (en) | 2013-12-11 | 2020-11-03 | Cedars-Sinai Medical Center | Methods, devices and systems for transcatheter mitral valve replacement in a double-orifice mitral valve |
US10350098B2 (en) | 2013-12-20 | 2019-07-16 | Volcano Corporation | Devices and methods for controlled endoluminal filter deployment |
CN103720463B (en) * | 2013-12-31 | 2015-08-26 | 上海交通大学 | Based on intelligent pressure seal wire and the transducer production method of flexible MEMS sensor |
CN105899141A (en) | 2014-01-10 | 2016-08-24 | 火山公司 | Detecting endoleaks associated with aneurysm repair |
WO2015108957A1 (en) | 2014-01-14 | 2015-07-23 | Volcano Corporation | Systems for improving an av access site |
US10874409B2 (en) | 2014-01-14 | 2020-12-29 | Philips Image Guided Therapy Corporation | Methods and systems for clearing thrombus from a vascular access site |
EP3094273A1 (en) | 2014-01-14 | 2016-11-23 | Volcano Corporation | Devices and methods for forming vascular access |
EP3094241B1 (en) | 2014-01-14 | 2018-07-04 | Volcano Corporation | Systems and methods for evaluating hemodialysis arteriovenous fistula maturation |
WO2015108942A1 (en) | 2014-01-14 | 2015-07-23 | Volcano Corporation | Vascular access evaluation and treatment |
US9913585B2 (en) * | 2014-01-15 | 2018-03-13 | Medtronic Vascular, Inc. | Catheter for providing vascular pressure measurements |
US10507301B2 (en) | 2014-01-31 | 2019-12-17 | Cedars-Sinai Medical Center | Pigtail for optimal aortic valvular complex imaging and alignment |
WO2015117066A1 (en) | 2014-02-03 | 2015-08-06 | Volcano Corporation | Intravascular devices,systems, and methods having a core wire with embedded conductors |
US10932679B2 (en) | 2014-03-18 | 2021-03-02 | Boston Scientific Scimed, Inc. | Pressure sensing guidewires and methods of use |
US10441754B2 (en) | 2014-03-26 | 2019-10-15 | Volcano Corporation | Intravascular devices, systems, and methods having a core wire formed of multiple materials |
CA2944114C (en) | 2014-04-04 | 2023-09-26 | St. Jude Medical Systems Ab | Intravascular pressure and flow data diagnostic systems, devices, and methods |
US9429713B2 (en) | 2014-04-17 | 2016-08-30 | Boston Scientific Scimed, Inc. | Self-cleaning optical connector |
EP3133987B1 (en) | 2014-04-21 | 2019-09-11 | Koninklijke Philips N.V. | Sensing guide wire and method of manufacturing thereof |
WO2015164301A1 (en) * | 2014-04-23 | 2015-10-29 | Koninklijke Philips N.V. | Catheter with integrated controller for imaging and pressure sensing |
US9855408B2 (en) | 2014-04-29 | 2018-01-02 | C. R. Bard, Inc. | Kink-resistant guidewire with improved rigidity |
CN106659393B (en) | 2014-06-04 | 2021-02-19 | 波士顿科学国际有限公司 | Pressure sensing guidewire system with reduced pressure excursions |
US10244951B2 (en) | 2014-06-10 | 2019-04-02 | Acist Medical Systems, Inc. | Physiological sensor delivery device and method |
US10232142B2 (en) | 2014-06-10 | 2019-03-19 | Prytime Medical Devices, Inc. | Conduit guiding tip |
US9955917B2 (en) | 2014-06-11 | 2018-05-01 | Vascomed Gmbh | Planar logic board for ablation catheter with force measurement functionality |
US11330989B2 (en) | 2014-06-16 | 2022-05-17 | Medtronic Vascular, Inc. | Microcatheter sensor design for mounting sensor to minimize induced strain |
US10973418B2 (en) | 2014-06-16 | 2021-04-13 | Medtronic Vascular, Inc. | Microcatheter sensor design for minimizing profile and impact of wire strain on sensor |
US10201284B2 (en) | 2014-06-16 | 2019-02-12 | Medtronic Vascular Inc. | Pressure measuring catheter having reduced error from bending stresses |
WO2016009317A1 (en) | 2014-07-13 | 2016-01-21 | Three Rivers Cardiovascular Systems Inc. | System and apparatus comprising a multisensor guidewire for use in interventional cardiology |
CN116172611A (en) | 2014-07-15 | 2023-05-30 | 皇家飞利浦有限公司 | Intrahepatic bypass apparatus and method |
WO2016019207A1 (en) | 2014-08-01 | 2016-02-04 | Boston Scientific Scimed, Inc. | Pressure sensing guidewires |
WO2016027198A1 (en) | 2014-08-21 | 2016-02-25 | Koninklijke Philips N.V. | Device and methods for crossing occlusions |
EP3357413A1 (en) | 2014-08-28 | 2018-08-08 | Koninklijke Philips N.V. | Intravascular devices with variable pitch radiopaque marker element |
WO2016030794A1 (en) | 2014-08-28 | 2016-03-03 | Koninklijke Philips N.V. | Intravascular devices, systems, and methods having an adhesive filled distal tip element |
WO2016034967A1 (en) * | 2014-09-04 | 2016-03-10 | Koninklijke Philips N.V. | Pressure-sensing intravascular devices, systems, and methods with wrapped pressure-sensing component |
WO2016038488A1 (en) | 2014-09-11 | 2016-03-17 | Koninklijke Philips N.V. | Intravascular devices, systems, and methods having a sensing element embedded in adhesive |
US10499813B2 (en) | 2014-09-12 | 2019-12-10 | Lightlab Imaging, Inc. | Methods, systems and apparatus for temporal calibration of an intravascular imaging system |
EP3197368B1 (en) | 2014-09-24 | 2018-11-28 | Koninklijke Philips N.V. | Endoluminal filter having enhanced echogenic properties |
CN107072568B (en) * | 2014-10-24 | 2021-05-28 | 美敦力瓦斯科尔勒公司 | Microcatheter sensor design for minimizing profile and wire strain effects on the sensor |
WO2016071822A1 (en) | 2014-11-03 | 2016-05-12 | Koninklijke Philips N.V. | Intravascular devices, systems, and methods having a radiopaque patterned flexible tip |
US10080872B2 (en) | 2014-11-04 | 2018-09-25 | Abbott Cardiovascular Systems Inc. | System and method for FFR guidewire recovery |
DE102014116221B4 (en) * | 2014-11-06 | 2019-05-23 | Ferton Holding S.A. | Monitoring system and method of monitoring |
US10258240B1 (en) | 2014-11-24 | 2019-04-16 | Vascular Imaging Corporation | Optical fiber pressure sensor |
WO2016090272A1 (en) | 2014-12-05 | 2016-06-09 | Boston Scientific Scimed, Inc. | Pressure sensing guidewires |
US10194812B2 (en) | 2014-12-12 | 2019-02-05 | Medtronic Vascular, Inc. | System and method of integrating a fractional flow reserve device with a conventional hemodynamic monitoring system |
FR3030738B1 (en) * | 2014-12-19 | 2020-03-20 | Commissariat A L'energie Atomique Et Aux Energies Alternatives | PRESSURE SENSOR SUITABLE FOR PRESSURE MEASUREMENTS IN AGGRESSIVE MEDIA |
US10105107B2 (en) | 2015-01-08 | 2018-10-23 | St. Jude Medical International Holding S.À R.L. | Medical system having combined and synergized data output from multiple independent inputs |
US10869756B2 (en) | 2015-03-12 | 2020-12-22 | Cedars-Sinai Medical Center | Devices, systems, and methods to optimize annular orientation of transcatheter valves |
AU2016232781B2 (en) | 2015-03-19 | 2017-11-02 | Prytime Medical Devices, Inc. | System for low-profile occlusion balloon catheter |
JP6670325B2 (en) | 2015-05-08 | 2020-03-18 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Hydrophilic coating for intra-conduit devices |
US10646198B2 (en) | 2015-05-17 | 2020-05-12 | Lightlab Imaging, Inc. | Intravascular imaging and guide catheter detection methods and systems |
US10222956B2 (en) | 2015-05-17 | 2019-03-05 | Lightlab Imaging, Inc. | Intravascular imaging user interface systems and methods |
US9996921B2 (en) | 2015-05-17 | 2018-06-12 | LIGHTLAB IMAGING, lNC. | Detection of metal stent struts |
US10109058B2 (en) | 2015-05-17 | 2018-10-23 | Lightlab Imaging, Inc. | Intravascular imaging system interfaces and stent detection methods |
CN107847137A (en) | 2015-06-30 | 2018-03-27 | 皇家飞利浦有限公司 | The endovascular device of tubular distal section with solid core type proximal section and fluting, system and method |
CN107920764B (en) | 2015-07-17 | 2021-09-21 | 皇家飞利浦有限公司 | Device, system and method for evaluating a vessel |
EP3324837B1 (en) | 2015-07-17 | 2020-04-01 | Koninklijke Philips N.V. | Intravascular devices, systems, and methods with an adhesively attached shaping ribbon |
EP3324830B1 (en) | 2015-07-25 | 2023-01-04 | Lightlab Imaging, Inc. | Intravascular data visualization method and device |
US10349840B2 (en) * | 2015-09-10 | 2019-07-16 | Opsens Inc. | Method for pressure guidewire equalization |
PT3367886T (en) * | 2015-10-29 | 2021-06-18 | Sintef Tto As | Sensor assembly |
CN108633312B (en) | 2015-11-18 | 2022-11-08 | 光学实验室成像公司 | Contrast cloud detection method in X-ray image |
CN115998310A (en) | 2015-11-23 | 2023-04-25 | 光学实验室成像公司 | Detection and verification of shadows in intravascular images |
WO2017136746A1 (en) | 2016-02-03 | 2017-08-10 | Cormetrics Llc | Modular sensing guidewire |
EP3419514B1 (en) | 2016-02-23 | 2023-08-23 | Boston Scientific Scimed, Inc. | Pressure sensing guidewire systems including an optical connector cable |
JP7027331B2 (en) | 2016-04-14 | 2022-03-01 | ライトラボ・イメージング・インコーポレーテッド | Identification of blood vessel branches |
ES2854729T3 (en) | 2016-05-16 | 2021-09-22 | Lightlab Imaging Inc | Method and system for the detection of self-expanding endoprosthesis, or stent, absorbable intravascular |
WO2017198800A1 (en) | 2016-05-20 | 2017-11-23 | Koninklijke Philips N.V. | Devices and methods for stratification of patients for renal denervation based on intravascular pressure and cross-sectional lumen measurements |
CA2990479C (en) | 2016-06-02 | 2019-03-26 | Prytime Medical Devices, Inc. | System and method for low-profile occlusion balloon catheter |
US11272850B2 (en) | 2016-08-09 | 2022-03-15 | Medtronic Vascular, Inc. | Catheter and method for calculating fractional flow reserve |
US11647678B2 (en) | 2016-08-23 | 2023-05-09 | Analog Devices International Unlimited Company | Compact integrated device packages |
US10821268B2 (en) * | 2016-09-14 | 2020-11-03 | Scientia Vascular, Llc | Integrated coil vascular devices |
US11272847B2 (en) | 2016-10-14 | 2022-03-15 | Hemocath Ltd. | System and apparatus comprising a multi-sensor catheter for right heart and pulmonary artery catheterization |
US10697800B2 (en) | 2016-11-04 | 2020-06-30 | Analog Devices Global | Multi-dimensional measurement using magnetic sensors and related systems, methods, and integrated circuits |
JP2020513259A (en) * | 2016-11-28 | 2020-05-14 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Electrical connection for small sensors |
WO2018129455A1 (en) | 2017-01-09 | 2018-07-12 | Boston Scientific Scimed, Inc. | Guidewire with tactile feel |
EP4327732A3 (en) | 2017-01-12 | 2024-04-24 | The Regents of The University of California | Endovascular perfusion augmentation for critical care |
JP7113851B2 (en) | 2017-01-19 | 2022-08-05 | ハイディム ゲーエムベーハー | Devices and methods for determining cardiac function in vivo |
US11330994B2 (en) | 2017-03-08 | 2022-05-17 | Medtronic Vascular, Inc. | Reduced profile FFR catheter |
US10952654B2 (en) | 2017-03-14 | 2021-03-23 | International Business Machines Corporation | PH sensitive surgical tool |
WO2018175485A1 (en) * | 2017-03-20 | 2018-09-27 | Corflow Therapeutics Ag | Combined stent reperfusion system |
WO2018195507A1 (en) | 2017-04-21 | 2018-10-25 | The Regents Of The University Of California | Aortic flow meter and pump for partial-aortic occlusion |
US10646122B2 (en) | 2017-04-28 | 2020-05-12 | Medtronic Vascular, Inc. | FFR catheter with covered distal pressure sensor and method of manufacture |
CN116327157A (en) | 2017-08-03 | 2023-06-27 | 波士顿科学国际有限公司 | Fractional flow reserve assessment method |
US11235124B2 (en) | 2017-08-09 | 2022-02-01 | Medtronic Vascular, Inc. | Collapsible catheter and method for calculating fractional flow reserve |
US11219741B2 (en) | 2017-08-09 | 2022-01-11 | Medtronic Vascular, Inc. | Collapsible catheter and method for calculating fractional flow reserve |
EP3679583A1 (en) | 2017-09-07 | 2020-07-15 | Koninklijke Philips N.V. | Automatic normalization of intravascular devices |
CN107837081A (en) * | 2017-12-07 | 2018-03-27 | 上海英诺伟医疗器械有限公司 | A kind of Pressure wire |
CN107802248A (en) * | 2017-12-12 | 2018-03-16 | 吉林大学 | A kind of pulse-taking instrument based on piezoresistive transducer array |
CN109984748A (en) * | 2017-12-29 | 2019-07-09 | 先健科技(深圳)有限公司 | Lumen diameter measuring device |
EP3795076B1 (en) | 2018-01-31 | 2023-07-19 | Analog Devices, Inc. | Electronic devices |
US11311196B2 (en) | 2018-02-23 | 2022-04-26 | Boston Scientific Scimed, Inc. | Methods for assessing a vessel with sequential physiological measurements |
WO2019174984A1 (en) | 2018-03-15 | 2019-09-19 | Koninklijke Philips N.V. | Variable intraluminal ultrasound transmit pulse generation and control devices, systems, and methods |
WO2019183432A1 (en) | 2018-03-23 | 2019-09-26 | Boston Scientific Scimed, Inc. | Medical device with pressure sensor |
JP7138189B2 (en) | 2018-04-06 | 2022-09-15 | ボストン サイエンティフィック サイムド,インコーポレイテッド | Medical device with pressure sensor |
CN112292073A (en) | 2018-04-18 | 2021-01-29 | 波士顿科学国际有限公司 | System for evaluating vessels with continuous physiological measurements |
CN111954487A (en) | 2018-04-20 | 2020-11-17 | 阿西斯特医疗系统有限公司 | Evaluation of blood vessels |
JP2021528178A (en) | 2018-06-27 | 2021-10-21 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Dynamic resource reconfiguration for patient interface module (PIM) in intraluminal medical ultrasound imaging |
US11185244B2 (en) | 2018-08-13 | 2021-11-30 | Medtronic Vascular, Inc. | FFR catheter with suspended pressure sensor |
EP3860466B1 (en) | 2018-10-04 | 2023-08-09 | Koninklijke Philips N.V. | Fluid flow detection for ultrasound imaging devices, systems, and methods |
AU2019402930A1 (en) * | 2018-12-20 | 2021-06-03 | Boston Scientific Scimed, Inc. | Endoscope system with a shaft including a sensor |
US11877864B2 (en) | 2019-05-29 | 2024-01-23 | Measurement Specialties, Inc. | Voltage nulling pressure sensor preamp |
JP6902681B2 (en) | 2019-07-18 | 2021-07-14 | Semitec株式会社 | Pressure sensor |
US20220370037A1 (en) | 2019-10-10 | 2022-11-24 | Koninklijke Philips N.V. | Vascular tissue characterization devices, systems, and methods |
WO2021105358A1 (en) | 2019-11-26 | 2021-06-03 | Koninklijke Philips N.V. | Electromagnetic-radiation-cured radiopaque marker and associated devices, systems, and methods |
WO2021188602A2 (en) | 2020-03-16 | 2021-09-23 | Certus Critical Care, Inc. | Blood flow control devices, systems, and methods and error detection thereof |
WO2023275129A1 (en) * | 2021-07-01 | 2023-01-05 | Koninklijke Philips N.V. | Sensor system for measuring flow velocity and pressure |
US20230181140A1 (en) | 2021-12-11 | 2023-06-15 | Philips Image Guided Therapy Corporation | Registration of intraluminal physiological data to longitudinal image body lumen using extraluminal imaging data |
WO2023104599A1 (en) | 2021-12-11 | 2023-06-15 | Koninklijke Philips N.V. | Automatic segmentation and treatment planning for a vessel with coregistration of physiology data and extraluminal data |
Family Cites Families (73)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3490441A (en) | 1966-01-10 | 1970-01-20 | Statham Instrument Inc | Intra-arterial blood pressure transducers |
US3545275A (en) * | 1968-09-12 | 1970-12-08 | Nasa | Transducer circuit and catheter transducer |
US3724274A (en) * | 1971-02-11 | 1973-04-03 | Millar Instruments | Pressure transducers and method of physiological pressure transducers |
US3748623A (en) | 1972-07-25 | 1973-07-24 | Millar Instruments | Pressure transducers |
DE2246687C3 (en) * | 1972-09-22 | 1978-10-05 | Siemens Ag, 1000 Berlin Und 8000 Muenchen | Pressure receptor |
US4020830A (en) | 1975-03-12 | 1977-05-03 | The University Of Utah | Selective chemical sensitive FET transducers |
JPS5918051B2 (en) | 1976-02-29 | 1984-04-25 | 三菱油化株式会社 | catheter |
JPS5921495B2 (en) * | 1977-12-15 | 1984-05-21 | 株式会社豊田中央研究所 | Capillary pressure gauge |
DE2828206C2 (en) | 1978-06-27 | 1986-09-11 | Siemens AG, 1000 Berlin und 8000 München | Catheter for insertion into a vessel of a patient |
NL8001420A (en) | 1980-03-10 | 1981-10-01 | Cordis Europ | ELECTRODE COMPOSITIVE COMPOSITE, FOR AN ELECTROCHEMICAL MEASUREMENT, IN PARTICULAR AN ISFET-CONSTRUCTED COMPOSITION, AND METHOD FOR MANUFACTURING THE ASSEMBLY. |
US4328806A (en) | 1980-06-18 | 1982-05-11 | American Hospital Supply Corporation | Catheter with trans-luminal gas pathway |
DE3366503D1 (en) * | 1983-02-03 | 1986-11-06 | Honeywell Medical Electronics | Measurement sensor for instalment in a catheter, particularly a pressure sensor |
US4554927A (en) * | 1983-08-30 | 1985-11-26 | Thermometrics Inc. | Pressure and temperature sensor |
US5178153A (en) * | 1984-03-08 | 1993-01-12 | Einzig Robert E | Fluid flow sensing apparatus for in vivo and industrial applications employing novel differential optical fiber pressure sensors |
US4610256A (en) * | 1984-09-25 | 1986-09-09 | Utah Medical Products, Inc. | Pressure transducer |
US4659235A (en) * | 1985-04-16 | 1987-04-21 | Borg-Warner Automotive, Inc. | Fluid pressure sensor with temperature indication |
US4733669A (en) * | 1985-05-24 | 1988-03-29 | Cardiometrics, Inc. | Blood flow measurement catheter |
US4665925A (en) * | 1985-09-13 | 1987-05-19 | Pfizer Hospital Products Group, Inc. | Doppler catheter |
NL8502543A (en) * | 1985-09-17 | 1987-04-16 | Sentron V O F | ELECTRONIC PRESSURE SENSITIVE ELEMENT MADE OF SEMICONDUCTOR MATERIAL. |
US4748986A (en) * | 1985-11-26 | 1988-06-07 | Advanced Cardiovascular Systems, Inc. | Floppy guide wire with opaque tip |
SE454045B (en) * | 1986-08-04 | 1988-03-28 | Radisensor Ab | LEADER FOR MECHANICAL CONTROL OF A CATHETIC DURING HEART AND KERL SURGERY |
US5046497A (en) * | 1986-11-14 | 1991-09-10 | Millar Instruments, Inc. | Structure for coupling a guidewire and a catheter |
US4771782A (en) * | 1986-11-14 | 1988-09-20 | Millar Instruments, Inc. | Method and assembly for introducing multiple catheters into a biological vessel |
US4850358A (en) * | 1986-11-14 | 1989-07-25 | Millar Instruments, Inc. | Method and assembly for introducing multiple devices into a biological vessel |
CA1314410C (en) * | 1986-12-08 | 1993-03-16 | Masanori Nishiguchi | Wiring structure of semiconductor pressure sensor |
US4920972A (en) * | 1987-01-27 | 1990-05-01 | Medex, Inc. | Gel-filled blood pressure transducer |
US5174295A (en) | 1987-04-10 | 1992-12-29 | Cardiometrics, Inc. | Apparatus, system and method for measuring spatial average velocity and/or volumetric flow of blood in a vessel and screw joint for use therewith |
US5163445A (en) * | 1987-04-10 | 1992-11-17 | Cardiometrics, Inc. | Apparatus, system and method for measuring spatial average velocity and/or volumetric flow of blood in a vessel and screw joint for use therewith |
US5113868A (en) * | 1987-06-01 | 1992-05-19 | The Regents Of The University Of Michigan | Ultraminiature pressure sensor with addressable read-out circuit |
US4815472A (en) | 1987-06-01 | 1989-03-28 | The Regents Of The University Of Michigan | Multipoint pressure-sensing catheter system |
US4881410A (en) | 1987-06-01 | 1989-11-21 | The Regents Of The University Of Michigan | Ultraminiature pressure sensor and method of making same |
US5207103A (en) | 1987-06-01 | 1993-05-04 | Wise Kensall D | Ultraminiature single-crystal sensor with movable member |
US5013396A (en) | 1987-06-01 | 1991-05-07 | The Regents Of The University Of Michigan | Method of making an ultraminiature pressure sensor |
US4808164A (en) | 1987-08-24 | 1989-02-28 | Progressive Angioplasty Systems, Inc. | Catheter for balloon angioplasty |
EP0313836A3 (en) * | 1987-09-30 | 1991-01-23 | Advanced Cardiovascular Systems, Inc. | Pressure monitoring guidewire |
US5050606A (en) * | 1987-09-30 | 1991-09-24 | Advanced Cardiovascular Systems, Inc. | Method for measuring pressure within a patient's coronary artery |
US4964409A (en) * | 1989-05-11 | 1990-10-23 | Advanced Cardiovascular Systems, Inc. | Flexible hollow guiding member with means for fluid communication therethrough |
US4953553A (en) * | 1989-05-11 | 1990-09-04 | Advanced Cardiovascular Systems, Inc. | Pressure monitoring guidewire with a flexible distal portion |
US4872483A (en) * | 1987-12-31 | 1989-10-10 | International Medical Products, Inc. | Conveniently hand held self-contained electronic manometer and pressure modulating device |
US4807477A (en) * | 1988-02-01 | 1989-02-28 | Motorola, Inc. | Capacitive temperature compensation for a pressure sensor |
US4901731A (en) * | 1988-04-27 | 1990-02-20 | Millar Instruments, Inc. | Single sensor pressure differential device |
SE460396B (en) * | 1988-07-29 | 1989-10-09 | Radisensor Ab | MINIATURIZED SENSOR DEVICE FOR SEATING PHYSIOLOGICAL PRESSURE IN VIVO |
US5450091A (en) * | 1988-08-05 | 1995-09-12 | Seiko Epson Corporation | Variable size antenna device having resonance frequency compensation |
DE3833723A1 (en) * | 1988-10-04 | 1990-04-12 | Berg Extrakorp Syst Medtech | METHOD FOR ZERO COMPARISON OF A PRESSURE MEASURING CATHETER AND PRESSURE MEASURING CATHETER FOR ITS IMPLEMENTATION |
US5240437A (en) | 1988-11-02 | 1993-08-31 | Cardiometrics, Inc. | Torqueable guide wire assembly with electrical functions, male and female connectors for use therewith and system and apparatus for utilizing the same |
US5178159A (en) * | 1988-11-02 | 1993-01-12 | Cardiometrics, Inc. | Torqueable guide wire assembly with electrical functions, male and female connectors rotatable with respect to one another |
SE462631B (en) | 1989-01-13 | 1990-07-30 | Radisensor Ab | MINIATURIZED PRESSURE SENSOR FOR PHYSIOLOGICAL SEATS IN SITU |
US4945762A (en) * | 1989-01-24 | 1990-08-07 | Sensym, Inc. | Silicon sensor with trimmable wheatstone bridge |
US4928693A (en) * | 1989-03-13 | 1990-05-29 | Schneider (Usa), Inc. | Pressure monitor catheter |
US4957110A (en) | 1989-03-17 | 1990-09-18 | C. R. Bard, Inc. | Steerable guidewire having electrodes for measuring vessel cross-section and blood flow |
US5050297A (en) * | 1989-09-21 | 1991-09-24 | Becton, Dickinson And Company | Method for assembly of a directly exposed catheter sensor on a support tip |
US5067491A (en) * | 1989-12-08 | 1991-11-26 | Becton, Dickinson And Company | Barrier coating on blood contacting devices |
US7033325B1 (en) | 1989-12-19 | 2006-04-25 | Scimed Life Systems, Inc. | Guidewire with multiple radiopaque marker sections |
US5313957A (en) * | 1990-01-05 | 1994-05-24 | Medamicus, Inc. | Guide wire mounted pressure transducer |
SE506135C2 (en) * | 1990-07-11 | 1997-11-17 | Radi Medical Systems | Sensor and conductor construction |
US5125137A (en) * | 1990-09-06 | 1992-06-30 | Cardiometrics, Inc. | Method for providing a miniature ultrasound high efficiency transducer assembly |
JPH04258176A (en) * | 1991-02-12 | 1992-09-14 | Mitsubishi Electric Corp | Semiconductor pressure sensor |
US5226421A (en) * | 1992-03-06 | 1993-07-13 | Cardiometrics, Inc. | Doppler elongate flexible member having an inflatable balloon mounted thereon |
US5873835A (en) | 1993-04-29 | 1999-02-23 | Scimed Life Systems, Inc. | Intravascular pressure and flow sensor |
US5450853A (en) * | 1993-10-22 | 1995-09-19 | Scimed Life Systems, Inc. | Pressure sensor |
US5358409A (en) | 1993-08-31 | 1994-10-25 | Cardiometrics, Inc. | Rotary connector for flexible elongate member having electrical properties |
US5348481A (en) | 1993-09-29 | 1994-09-20 | Cardiometrics, Inc. | Rotary connector for use with small diameter flexible elongate member having electrical capabilities |
US5517989A (en) | 1994-04-01 | 1996-05-21 | Cardiometrics, Inc. | Guidewire assembly |
US5412994A (en) * | 1994-06-14 | 1995-05-09 | Cook; James D. | Offset pressure sensor |
WO1996007351A1 (en) * | 1994-09-02 | 1996-03-14 | Cardiometrics, Inc. | Ultra miniature pressure sensor and guidewire using the same and method |
US5668320A (en) | 1995-06-19 | 1997-09-16 | Cardiometrics, Inc. | Piezoresistive pressure transducer circuitry accommodating transducer variability |
US5551301A (en) | 1995-06-19 | 1996-09-03 | Cardiometrics, Inc. | Piezoresistive pressure transducer circuitry accommodating transducer variability |
SE9600333D0 (en) | 1995-06-22 | 1996-01-30 | Radi Medical Systems | Sensor arrangement |
DE19625869C2 (en) | 1996-06-27 | 2001-01-04 | Fraunhofer Ges Forschung | Method for the parallel merging of N data sets |
US5807477A (en) | 1996-09-23 | 1998-09-15 | Catalytic Distillation Technologies | Process for the treatment of light naphtha hydrocarbon streams |
US5902248A (en) | 1996-11-06 | 1999-05-11 | Millar Instruments, Inc. | Reduced size catheter tip measurement device |
US6142958A (en) | 1998-12-23 | 2000-11-07 | Radi Medical Systems Ab | Sensor and guide wire assembly |
US8277386B2 (en) | 2004-09-27 | 2012-10-02 | Volcano Corporation | Combination sensor guidewire and methods of use |
-
1995
- 1995-08-04 WO PCT/US1995/009898 patent/WO1996007351A1/en active Search and Examination
- 1995-08-04 AU AU32128/95A patent/AU3212895A/en not_active Abandoned
- 1995-08-04 DE DE69534748T patent/DE69534748T2/en not_active Expired - Lifetime
- 1995-08-04 CA CA002198909A patent/CA2198909A1/en not_active Abandoned
- 1995-08-04 EP EP06075026A patent/EP1658808A1/en not_active Withdrawn
- 1995-08-04 EP EP95928311A patent/EP0778746B1/en not_active Expired - Lifetime
- 1995-08-04 JP JP50948796A patent/JP3619845B2/en not_active Expired - Lifetime
-
1996
- 1996-09-09 US US08/710,062 patent/US5715827A/en not_active Expired - Lifetime
-
1997
- 1997-08-15 US US08/912,879 patent/US6106476A/en not_active Expired - Lifetime
-
2000
- 2000-08-21 US US09/644,111 patent/US6767327B1/en not_active Expired - Lifetime
-
2002
- 2002-09-19 US US10/247,391 patent/US7097620B2/en not_active Expired - Fee Related
- 2002-09-19 US US10/247,043 patent/US6976965B2/en not_active Expired - Fee Related
-
2005
- 2005-12-15 US US11/303,249 patent/US8419648B2/en not_active Expired - Fee Related
-
2006
- 2006-05-26 US US11/442,684 patent/US20070149885A1/en not_active Abandoned
-
2007
- 2007-01-04 US US11/650,064 patent/US7967762B2/en not_active Expired - Fee Related
-
2011
- 2011-06-27 US US13/169,174 patent/US8419647B2/en not_active Expired - Fee Related
Also Published As
Publication number | Publication date |
---|---|
US7097620B2 (en) | 2006-08-29 |
US5715827A (en) | 1998-02-10 |
US8419648B2 (en) | 2013-04-16 |
WO1996007351A1 (en) | 1996-03-14 |
EP0778746A4 (en) | 1997-11-05 |
US20030040674A1 (en) | 2003-02-27 |
US20110251497A1 (en) | 2011-10-13 |
DE69534748D1 (en) | 2006-04-06 |
US6976965B2 (en) | 2005-12-20 |
EP1658808A1 (en) | 2006-05-24 |
US6106476A (en) | 2000-08-22 |
US7967762B2 (en) | 2011-06-28 |
DE69534748T2 (en) | 2006-11-02 |
AU3212895A (en) | 1996-03-27 |
US20070135718A1 (en) | 2007-06-14 |
US20030018273A1 (en) | 2003-01-23 |
EP0778746B1 (en) | 2006-01-11 |
US6767327B1 (en) | 2004-07-27 |
US20070149885A1 (en) | 2007-06-28 |
JPH10505269A (en) | 1998-05-26 |
US20060094982A1 (en) | 2006-05-04 |
US8419647B2 (en) | 2013-04-16 |
EP0778746A1 (en) | 1997-06-18 |
JP3619845B2 (en) | 2005-02-16 |
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