US20020058873A1 - Volumetric image ultrasound transducer underfluid catheter system - Google Patents

Volumetric image ultrasound transducer underfluid catheter system Download PDF

Info

Publication number
US20020058873A1
US20020058873A1 US10/003,666 US366601A US2002058873A1 US 20020058873 A1 US20020058873 A1 US 20020058873A1 US 366601 A US366601 A US 366601A US 2002058873 A1 US2002058873 A1 US 2002058873A1
Authority
US
United States
Prior art keywords
catheter
array
transducer
elongated body
distal end
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
Application number
US10/003,666
Inventor
James Seward
Abdul Tajik
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Mayo Foundation for Medical Education and Research
Original Assignee
Mayo Foundation for Medical Education and Research
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=32046202&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=US20020058873(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Priority to US07/790,580 priority Critical patent/US5325860A/en
Priority to PCT/US1992/009835 priority patent/WO1993008738A1/en
Priority to US07/972,626 priority patent/US5345940A/en
Priority claimed from US08/678,380 external-priority patent/US5704361A/en
Priority to US09/586,193 priority patent/US6306096B1/en
Application filed by Mayo Foundation for Medical Education and Research filed Critical Mayo Foundation for Medical Education and Research
Priority to US10/003,666 priority patent/US20020058873A1/en
Publication of US20020058873A1 publication Critical patent/US20020058873A1/en
Priority to US10/401,287 priority patent/US7156812B2/en
Abandoned legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/32Surgical cutting instruments
    • A61B17/3205Excision instruments
    • A61B17/3207Atherectomy devices working by cutting or abrading; Similar devices specially adapted for non-vascular obstructions
    • A61B17/320758Atherectomy devices working by cutting or abrading; Similar devices specially adapted for non-vascular obstructions with a rotating cutting instrument, e.g. motor driven
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/06Measuring blood flow
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/12Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A61B8/4488Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer the transducer being a phased array
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/00234Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery
    • A61B2017/00238Type of minimally invasive operation
    • A61B2017/00243Type of minimally invasive operation cardiac
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/36Image-producing devices or illumination devices not otherwise provided for
    • A61B90/37Surgical systems with images on a monitor during operation
    • A61B2090/378Surgical systems with images on a monitor during operation using ultrasound
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/36Image-producing devices or illumination devices not otherwise provided for
    • A61B90/37Surgical systems with images on a monitor during operation
    • A61B2090/378Surgical systems with images on a monitor during operation using ultrasound
    • A61B2090/3782Surgical systems with images on a monitor during operation using ultrasound transmitter or receiver in catheter or minimal invasive instrument
    • A61B2090/3784Surgical systems with images on a monitor during operation using ultrasound transmitter or receiver in catheter or minimal invasive instrument both receiver and transmitter being in the instrument or receiver being also transmitter
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4444Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
    • A61B8/445Details of catheter construction

Definitions

  • Noninvasive ultrasonic imaging systems are widely used for performing ultrasonic imaging and taking measurements. Such systems typically use scan heads which are placed against a patients skin. Exemplary uses for such systems include heart and internal organ examinations as well as examinations of developing fetuses. These systems operate by transmitting ultrasonic waves into the body, receiving echoes returned from tissue interfaces upon which the waves impinge, and translating the received echo information into a structural representation of the planar slice of the body through which the ultrasonic waves are directed.
  • Catheter based invasive ultrasound imaging systems typically used for intracardiac or transvascular imaging, are a relatively new addition to ultrasound armamentarian.
  • Conventional underfluid transducers for use on catheters are comprised of crystal arrays (e.g. linear phased array) or a single crystal translated over a surface, producing a tomographic field of view in an azimuthal plane of the array.
  • Typical arrays include: 1) linear array (linear sequential array), usually producing a rectangular or rhomboidal picture; 2) cylindrical array or rotating crystal, producing a round pie-shaped tomographic cut of structures; and 3) sector array (linear phased array), producing a triangular shaped image emanating from a small transducer source. All images are tomographic in nature and are focused in the azimuthal and elevation plane. The intent of having these conventional transducer configurations is to produce a thin ultrasound cut of the insonated structures. Such tomographic planes by nature are thin and of high resolution.
  • the present invention relates generally to a volumetric, 3-dimensional image ultrasound transducer underfluid catheter system.
  • the present invention also relates to an ultrasonic and interventional catheter device operated in an intracardiac or transvascular system, with the aid of a volumetric 3-dimensional imaging capability.
  • the present invention relates to a catheter apparatus comprising an underfluid catheter body having proximal and distal ends.
  • An ultrasonic transducer array is mounted longitudinally along the catheter body proximate the distal end.
  • the transducer array has a volumetric field of view that projects radially/laterally outward from the catheter. Additional features in such wide volumetric field of view can be imaged, measured, or intervened by an underfluid therapeutic device with an aid of the real-time image.
  • a first dimension referred to as an azimuthal direction
  • a second dimension referred to as a depth direction
  • a third dimension is perpendicular to both the azimuthal and the depth directions.
  • the transducer array comprises a linear phased array having a single row of piezoelectric crystals
  • a 3-dimensional field of view can be generated by focusing the ultrasound signals in the azimuthal direction (parallel to the longitudinal axis of the catheter) and diverging the ultrasound signals in the elevational direction (transverse to the longitudinal axis of the catheter).
  • the ultrasonic signals can be diverged in the elevational direction through the use of lenses.
  • the signals can be diverged by mounting a silicone rubber concave lens or a plastic convex lens in front of the transducer array.
  • the transducer array comprises multiple rows of piezoelectric crystals
  • a 3-dimensional field of view can be generated by electronically phasing the ultrasound signals in both the azimuthal and elevational directions.
  • lenses can be used in association with multiple row arrays to further widen the field of view.
  • catheters constructed in accordance with the principles of the present invention can optionally include one or more ports that extend longitudinally through the catheter bodies.
  • the ports are preferably adapted for guiding therapeutic instruments through the catheter and preferably have exit ends adjacent to the field of view of the catheter imaging system.
  • the ports guide the therapeutic instruments such that the operative ends of a therapeutic instruments are directed toward the 3-dimensional field of view of the imaging system.
  • catheters constructed in accordance with the principles of the present invention can include one or more guidewire ports which extend longitudinally through the catheters and are adapted for receiving guidewires.
  • One advantage of the present invention is to provide real-time 3-dimensional images of underfluid features so as to visualize contiguous anatomy, such as a large volume of tissues without frequently rotating, flexing, or extending the catheter.
  • the present invention provides a much better underfluid “eye”—a 3-dimensional “motion picture”—for an operator when he/she intervenes the underfluid features by using an underfluid therapeutic device. These images provide the operator a direct aid without opening a large area of a body.
  • a further advantage is that the present invention have numerous clinical applications.
  • One is; related to underfluid imaging: There is a considerable need to increase the field of view when imaging from within chambers or blood vessels. The physical space of the chambers or blood vessels is small, and the anatomy in question is closed approximated and usually totally surrounds the transducer.
  • a conventional tomographic presentation provides only a limited slice, thus requiring frequent manipulation of transducer in order to visualize contiguous anatomy.
  • the present invention is a solution to visualizing larger volumes of tissue.
  • the underfluid defocusing transducer array does not appreciably affect the electronics and does not require alteration in the display format.
  • the catheter apparatus is immersed in fluid, a homogeneous, low scattering medium, which is an ideal environment for this particular transducer modification.
  • a further advantage of the present invention is that by using such a catheter system, major surgical procedures can be avoided. It dramatically reduces the patient's physical pain in operation and mental distress after operation due to any large visible scars, etc.
  • FIG. 1 is a partial perspective view of an embodiment of a catheter in accordance with the principles of the present invention
  • FIG. 2 is an enlarged cross-sectional view taken proximate the distal end of the catheter shown in FIG. 1;
  • FIG. 3 is a block diagram in part and sectional diagram in part illustrating an embodiment of a system utilizing the catheter shown in FIG. 1;
  • FIG. 4A is an illustration illustrating an application of a catheter in accordance with the principles of the present invention.
  • FIG. 4B is a partially enlarged illustration of the catheter shown in FIG. 4A.
  • FIG. 5A shows a partial perspective and cross-sectional view of a first alternate embodiment of a catheter in accordance with the principles of the present invention
  • FIG. 5B shows a view of the distal end of the embodiment of the catheter shown in Figure 5A;
  • FIG. 6A shows a partial perspective and cross-sectional view of a second alternate embodiment of a catheter in accordance with the principles of the present invention
  • FIG. 6B shows a view of the distal end of the catheter shown in FIG. 6A;
  • FIG. 7A shows a partial perspective and cross-sectional view of a variation of the second alternate embodiment of the catheter shown in FIG. 6A;
  • FIG. 7B shows a view of the distal end of the embodiment of the catheter shown in FIG. 7A;
  • FIG. 8A shows a partial perspective and cross-sectional view of a third alternate embodiment of a catheter in accordance with the principles of the present invention
  • FIG. 8B shows a view of the distal end of the catheter shown in FIG. 8A;
  • FIG. 8C shows a view of the distal end of the catheter shown in FIG. 8A having an alternatively shaped secondary port
  • FIG. 9A shows partial perspective and cross-sectional view of a fourth alternate embodiment of a catheter in accordance with the principles of the present invention.
  • FIG. 9B shows a view of the distal end of the catheter shown in FIG. 9A.
  • FIG. 10 is a partial schematic view of an embodiment of an underfluid catheter system in accordance with the principles of the present invention.
  • FIG. 11 is an enlarged view illustrating the catheter system operated underfluid with an aid of a volumetric field of view.
  • FIG. 12 is an enlarged perspective view illustrating the catheter system providing a volumetric field of view.
  • FIG. 13 is an enlarged perspective view of an ultrasonic transducer array having a single row of crystals covered by a lens which provides a volumetric field of view.
  • FIG. 14 is an enlarged perspective view of an alternative ultrasonic transducer array having multiple rows of crystals which provides a volumetric field of view.
  • FIG. 15 is an enlarged perspective view of a second alternative ultrasonic transducer array having equal number of rows and columns of crystals which provides a volumetric field of view.
  • FIG. 16 is an enlarged schematic cross-sectional view of a concave silicone rubber lens being placed on the ultrasonic transducer array, providing an outwardly defocused ultrasound beam.
  • FIG. 17 is an enlarged schematic cross-sectional view of a convex plastic lens being placed on the ultrasonic transducer array, providing an outwardly defocused ultrasound beam.
  • FIG. 18 is an enlarged schematic cross-sectional view of a convex silicone rubber lens being placed on the ultrasonic transducer array, providing an inwardly focused ultrasound beam.
  • catheter 20 includes an elongated flexible or rigid tubular catheter body 22 having a proximal end 24 and a distal end 26 .
  • catheter 20 includes proximate its longitudinal distal end 26 a phased array ultrasonic transducer 30 which is used to transmit ultrasound and receive resultant echoes so as to provide a field of view within which Doppler flow rates can be measured and features imaged.
  • ultrasonic transducers can be used in the present invention, such as any mechanical types, or any dynamic array types, or any offset stereoscopic imaging types, or any multidimensional imaging types incorporated into a virtual reality environment for underblood operation, etc.
  • An electrical conductor is disposed in the catheter body 22 for electrically connecting transducer 30 to control circuitry 34 external of catheter body 22 .
  • An access port 40 is disposed in catheter body 22 and extends from proximate the proximal end 24 of catheter body 22 to proximate the distal end 26 of catheter body 22 .
  • Access port 40 is configured to receive a therapeutic device, such as a catheter, medication, sensors, etc., so as to enable such items to be delivered via access port 40 to distal end 26 of catheter body 22 for operation within the ultrasonic transducer field of view. Such items might be used for intervention; e.g., ablation catheter, surgical device, etc., monitoring blood pressure, sampling blood, etc.
  • a guide wire access port 42 is also disposed within catheter body 22 and extends from proximate proximal end 24 of the catheter body 22 to proximate distal end 26 of catheter body 22 for receiving a guide wire 44 .
  • the ultrasonic transducer preferably has a frequency of 5 to 30 megahertz (MHz) and more preferably a frequency of 7 to 10 MHz. Intracardiac imaging in an adult will require image penetration of up to 2 to 10 centimeters (cm)
  • catheter body 22 preferably has a diameter of 4 to 24 French (one French divided by Pi equals one millimeter (mm)) and, more preferably, a diameter of 6 to 12 French.
  • access port 40 has a diameter of 7 to 8 French and guide wire port 42 has a diameter of 0.025 to 0.038 inches.
  • catheter 20 of the present invention can be utilized in a medical system including the appropriate control circuitry 34 for controlling operation of the ultrasonic transducer.
  • control circuitry 34 is electrically interconnected to transceiver circuitry 35 (T ⁇ /R) for receiving and transmitting signals via a cable 36 to ultrasonic transducer 30 .
  • transceiver circuitry 35 is electrically interconnected to Doppler circuitry 37 and an appropriate display device 38 for displaying hemodynamics or blood flow.
  • transceiver circuitry 35 is electrically interconnected to suitable imaging circuitry 39 which is interconnected to a display 41 for displaying images.
  • control circuitry 34 might be designed to cause ultrasonic transducer 30 to vibrate so as to cause an appropriate ultrasound wave to project from proximate the distal end 26 of catheter body 22 .
  • the ultrasound wave represented by lines 50 in FIG. 2, will propagate through the blood surrounding distal end 26 and a portion of the body structure. A portion of the ultrasound wave so transmitted will be reflected back from both the moving red blood cells and the like and the body structures to impinge upon transducer 30 .
  • An electrical signal is thereby generated and transmitted by the cable 36 to the input of transceiver 35 .
  • a signal might then be transmitted to Doppler circuitry 37 which will include conventional amplifying and filtering circuitry commonly used in Doppler flow metering equipment.
  • Doppler circuitry 37 will analyze the Doppler shift between the transmitted frequency and the receive frequency to thereby derive an output proportional to flow rate. This output may then be conveniently displayed at display 38 which might be a conventional display terminal. Accordingly, the user will be able to obtain a readout of blood flow rates or hemodynamic information.
  • control circuitry 34 will likewise trigger ultrasonic transducer 30 via transceiver 35 to vibrate and produce an ultrasound wave. Once again, a portion of the wave or energy will be reflected back to ultrasonic transducer 30 by the body features. A corresponding signal will then be sent by cable 36 to transceiver circuitry 35 . A corresponding signal is then sent to the imaging circuitry 39 which will analyze the incoming signal to provide, at display 41 , which also might be a conventional display apparatus, an image of the body features.
  • This imaging can occur while a therapeutic or surgical device is being used at distal end 26 of catheter 20 within the field of view provided by ultrasonic transducer 30 . Accordingly, the user will be able to monitor his/her actions and the result thereof.
  • catheter body 22 might include proximate its proximal end 24 a suitable mounting structure 52 to the access port 40 .
  • a therapeutic or surgical device structure 53 might be suitably attached to structure 52 by suitable means, e.g., threaded, etc.
  • an elongated cable-like member 54 will extend along access port 40 and slightly beyond distal end 26 of catheter body 22 wherein an operative portion 56 of the surgical tool might be interconnected.
  • ultrasonic transducer 30 might include a piezoelectric polymer, such as Polyvinylidenedifloride (PVDF) 60 , which is bonded by an epoxy layer 62 to a depression 64 approximate distal end 26 .
  • PVDF Polyvinylidenedifloride
  • FIGS. 2, 4A, and 4 B ultrasonic transducer 30 might include a piezoelectric polymer, such as Polyvinylidenedifloride (PVDF) 60 , which is bonded by an epoxy layer 62 to a depression 64 approximate distal end 26 .
  • PVDF Polyvinylidenedifloride
  • the operational portion 56 of the therapeutic device is illustrated as generally being capable of operation in the field of view of ultrasonic transducer 30 . Accordingly, it is possible for the user to monitor operation of the therapeutic device by use of the ultrasonic transducer. Moreover, it is possible for the user to monitor the features of the body within the field of view before, during and after interventional activity.
  • ultrasonic transducers can be used in the present invention, such as any mechanical types, or any dynamic array types, or any offset stereoscopic imaging types, or any multidimensional imaging types incorporated into a virtual reality environment for underblood operation, etc., so that all forms of field of views, such as 1) tomographic (slices), 2) stereoscopic, 3) three-dimensional, 4) virtual reality (multidimensional) can be provided in the present invention.
  • the orientations of the scan array on the catheter can be include side-view, end-view, multiview (two or more views that are moveable or imminently directional transducer referred to in the literature as “omnidirectional”), etc.
  • FIG. 5A shows a partial cross-sectional view of a first alternative embodiment 70 of the catheter apparatus.
  • the catheter apparatus has an elongated flexible or rigid body 72 having a longitudinal axis and a proximal end 74 and a distal end 76 .
  • a port 78 Disposed proximate a second side of body 72 is a port 78 extending through body 72 from proximate proximal end 74 to proximate distal end 76 of body 72 .
  • Port 78 is for receiving and delivering to distal end 76 of body 72 a working tool 84 .
  • Working tool 84 shown in the Figures is illustrative only, others types of tools now known or later developed may also be delivered to distal end 76 through port 78 .
  • Proximate a first side of body 72 is a guide wire port 80 extending through body 72 from proximate proximal end 74 to proximate distal end 76 . Shown in guide port 80 is
  • Distal end 76 is disposed at an oblique angle to the longitudinal axis of body 72 , the first side of body 72 extending further in the direction of the distal end than the second side of body 72 .
  • An ultrasonic transducer 82 having a first side and a second side, is disposed at an oblique angle to the longitudinal axis of body 72 approximately corresponding to the oblique angle of distal end 76 of body 72 .
  • the first side of ultrasonic transducer 82 is disposed proximate the first side of body 72 and the second side of transducer 82 is disposed proximate the second side of body 72 .
  • transducer 82 Extending from transducer 82 to proximate proximal end 74 of body 72 is an electrical conductor 83 connecting transducer 82 to control circuitry external of catheter 70 , as described with respect to catheter 20 above. Having transducer 82 disposed on an oblique angle toward port 78 allows for easy visualization of tools, such as tool 84 , extending beyond distal end 76 of body 72 .
  • FIG. 5B shows a view of distal end 76 of body 72 , showing guide wire port means 80 , transducer 82 , and port means 78 .
  • FIG. 6A shows a partial cross-sectional view of a second alternative embodiment of the catheter in accordance with the present invention, generally referred to as 88 .
  • catheter 88 has an elongated flexible or rigid body 90 having a proximal end 92 and a distal end 94 .
  • Catheter 88 also has a port 96 extending through body 90 from proximate proximal end 92 to proximate distal end 94 .
  • Port 96 has a distal end 97 proximal distal end 94 of body 90 .
  • Distal end 97 of port 96 exits body 90 at an acute angle to a first side of body 90 toward distal end 94 .
  • Port 96 is for receiving and delivering to distal end 94 a working tool, such as working tool 84 .
  • Catheter 88 also has a guide wire port 98 extending through body 90 from proximate proximal end 92 to proximate distal end 94 .
  • Guide wire port 98 is for receiving a guide wire 86 .
  • transducer 100 disposed to a first side of body 90 between distal end 94 and distal end 97 of port 96 .
  • Extending from transducer 100 to proximate proximal end 92 of body 90 is an electrical conductor 102 disposed in the catheter body 90 for electrically connecting transducer 100 to control circuitry external of the catheter.
  • FIG. 6B shows a view of distal end 94 of catheter 88 , as shown in FIG. 6A.
  • FIG. 7A shows second alternative embodiment 104 , as shown in FIG. 6A, except instead of having a guide wire port 98 , this variation of the second alternative embodiment 104 has a deflection wire guidance system 106 for manipulating distal end 94 .
  • FIG. 7B shows a view of distal end 94 of the catheter shown in FIG. 7A.
  • FIG. 8A shows a third alternative embodiment 110 of the catheter in accordance with the present invention.
  • Third alternative embodiment 110 has a body 112 having a distal end 114 and proximal end. Disposed proximate a first side of body 112 is a primary port 118 extending through body 112 from proximate proximal end 116 to proximate distal end 114 .
  • Primary port 118 has a distal end 119 proximate distal end 114 of body 112 .
  • a secondary port 120 Oppositely disposed from primary port 118 , proximate a second side of body 112 is a secondary port 120 extending through body 112 from proximate proximal end 116 to proximate distal end 114 .
  • Secondary port 120 has a distal end 121 proximate distal end 114 of body 112 .
  • transducer 122 Mounted proximate distal end 114 of body 112 is a transducer 122 . Extending from transducer 122 through body 112 to proximate proximal end is an electrical conductor for electrically connecting the transducer 122 to control circuitry external of the catheter. Transducer 122 is disposed between distal ends of primary and secondary ports 119 and 121 , respectively. With working ports 118 and 120 oppositely disposed on either side of transducer 122 , it is possible to conduct two simultaneous applications, such as holding an object with a first tool disposed through one port and operating on the object held by the first tool with a second tool disposed through the other port. A typical working tool 123 and working tool 84 are shown disposed within ports 118 and 120 .
  • FIG. 8B shows a view of distal end 114 of catheter 110 .
  • FIG. 8C shows a view of a distal end 124 of a catheter 126 substantially like catheter 110 shown in FIG. 8A and FIG. 8B, except that catheter 126 has a primary port 128 having an arc-like shaped cross-section, rather than a circular shaped cross-section.
  • catheter 126 has a primary port 128 having an arc-like shaped cross-section, rather than a circular shaped cross-section.
  • a circular cross-section has been shown in the Figures for the various ports described herein, the size and shape of the ports can be varied without departing from the principals of the present invention.
  • FIG. 9A shows a fourth alternative embodiment of a catheter 130 of the present invention.
  • Catheter 130 is similar to catheter 70 shown in FIG. 5A and FIG. 5B except that a plurality of ports 132 are disposed proximate a second side of flexible body 131 , rather than one port 78 , as shown in FIG. 5A.
  • a plurality of ports it is possible, for example, to use a therapeutic tool through one port while simultaneously suctioning and removing debris through another port; or a therapeutic tool can be used through one port while simultaneously electrophysiologically monitoring, suctioning and/or biopsying through a second port, third or fourth port.
  • the use of the catheter of the present invention is described with respect to the preferred embodiment 20 . It is understood that the use of alternative embodiments 70 , 88 , 110 , 126 and 130 is analogous.
  • the user would insert flexible catheter body 22 into the body via the appropriate vascular access to the desired location in the body, such as selected venous locations, heart chamber, etc.
  • a guide wire might be first inserted into place and then the catheter body fed along the guide wire.
  • the user might then insert a surgical device into the body through access port 40 and feed the surgical device to proximate distal end 26 of catheter body 22 .
  • the user Prior to, during and after operation of the surgical device, the user might obtain both hemodynamic measurements and images from the ultrasonic transducer field of view. By operation of the surgical device within the field of view of transducer, the user can monitor operation of the surgical device at all times.
  • Frequency agility refers to the ability of a transducer to send and receive at various frequencies, most commonly 3, 5, and 7 MHz. It is also appreciated that a single frequency from a single transducer device can be sent and received. In general, higher frequencies are used to image fine detail of more proximal or closely related objects while lower frequency transducers scan more remote objects with less detail.
  • the proposed device optimally uses a 5 to 20 mHz transducer with the most optimally applied frequency of 7 to 10 mHz.
  • the lower frequency used in the UIHC reflects the need to image larger objects such as the cardiac septa, valves, and extravascular anatomy.
  • One primary function of this catheter system is to guide the logical and safe use of various a) ablation, b) laser, c) cutting, occluding, e) etc., catheter-based interventional tools.
  • the invention has the access port through which other technologies (devices) can be passed. Once the interventional tool exits the catheter tip, it can be directed repeatedly and selectively to specific site for controlled intervention.
  • the invention is also an imaging system capable of visualizing intracardiac, intravascular, and extravascular structures. Because the transducer frequencies utilized are usually lower than intravascular systems, the catheter 20 can see multiple cardiac cavities and visualize structures outside the vascular system.
  • the imaging capability is basically two-fold: 1) diagnostic and 2) application.
  • Diagnostic imaging The catheter 20 can effectively perform diagnostic intracardiac and transvascular imaging. This application will more than likely be performed just prior to an interventional application. The intervention then will follow using the same catheter system and its unique delivery capability.
  • diagnostic imaging include 1) accurate visualization and measurement of an intracardiac defect, 2) characterization of valve orifice, 3) localization of a tumor and its connections, 4) etc.
  • Extravascular diagnoses would include 1) visualize pancreatic mass/pathology, 2) retroperitoneal pathology, 3) intracranial imaging, 4) recognition of perivascular pathology, and 5) imaging of other fluid containing space such as urinary bladder, bile system, fluid filled orifice or cavity (e.g. filled saline), etc.
  • Application imaging refers to the use of the catheter and its imaging capability to deliver and then apply another technology such as 1) occlusion device for closure of a septal defect, 2) ablation catheters for treatment of bypass tracts, 3) creation of a defect such as that with the blade septostomy catheter or laser-based catheter system, and 4) directing of valvuloplasty (such as prostrate surgery, placement of stents, gallstone removal etc.), etc.
  • occlusion device for closure of a septal defect
  • ablation catheters for treatment of bypass tracts
  • creation of a defect such as that with the blade septostomy catheter or laser-based catheter system
  • valvuloplasty such as prostrate surgery, placement of stents, gallstone removal etc.
  • the catheter 20 is a truly combined ultrasound Doppler and conventional hemodynamic catheter. There are Doppler catheters, and there are catheters capable of imaging and measuring hemodynamic pressure. However, the catheter 20 is capable of Doppler hemodynamics (continuous and pulsed wave Doppler) as well as high-fidelity hemodynamic pressure recording while simultaneously imaging the heart and blood vessel. The catheter 20 provides a combination of imaging, hemodynamic, and interventional delivery catheter.
  • intracardiac ultrasound is capable of 1) imaging, 2) delivering a therapeutic device, and 3) obtaining simultaneous hemodynamics which can be used to develop less invasive cardiac surgical techniques.
  • This simultaneous use of one or more devices within the heart or vascular tree opens up the potential to develop less invasive surgical therapies.
  • Examples would include 1) removal of a cardiac tumor by visually grasping the tumor with one device and visually cutting its attachment with a second device, thus allowing less invasive extraction of intracardiac mass lesions, 2) visually placing an electrophysiologic catheter on a bypass tract and then with direct ultrasound visualization ablate the underlying tract with the second device, 3) visually performing laser surgery such as creating an intra-atrial defect, vaporization of obstructing thrombus such as is seen in pseudointimal occlusion of conduits, 4) visually removing a foreign body from the heart or vascular tree, and 5) directing intravascular surgery from within a blood vessel or monitoring concomitant hemodynamic changes.
  • a bypass tract is localized by an electrophysiologic study which systematically maps the atrioventricular valve annulus. Positioning of the ablation catheter is determined by x-ray fluoroscopy and certain electrical measurements which relate the distance of the ablation catheter from a reference catheter. The catheter 20 will allow an operator to map the atrioventricular valve under direct ultrasound visualization. Thus, increased accuracy of catheter placement, precision of the applied therapy, and immediate assessment of outcome would result.
  • the above ablation technique would be particularly applicable for right-sided bypass tracts (in and around the tricuspid valve annulus). This would be accomplished by placement of the catheter 20 through the superior vena cava above the tricuspid annulus.
  • the catheter 20 could be placed across the atrial septum under direct ultrasound visualization.
  • the mitral annulus could thus be mapped directly and the localized bypass tract precisely ablated under visual ultrasonic and hemodynamic direction. Complications such as valve perforation, multiple imprecise applications of ablation energy, and inadvertent ablation of normal conduction tissue would be substantially reduced.
  • the catheter 20 will allow visualization of perivascular and extravascular pathology. Transvascular or transorgan imaging and localization of pathology out of the immediate vascular tree will result in a substantial step forward in the diagnosis and possible treatment of difficult to reach pathology.
  • the catheter 20 cannot only diagnose but guide a biopsy needle and therapeutic device to an extravascular lesion in question.
  • the retroperitoneum, mediastinum, and basal cerebrovascular pathology are logical areas of interest. Accurate characterization of various pathologies will be more feasible. Every organ has its own vascular system, and the proposed ultrasound transvascular system is an ideal tool to assess difficult to reach areas of the body.
  • the vascular system is a conduit to each organ, and the catheter 20 can be delivered to each organ. Characterization of the underlying parenchyma and possible transvascular biopsy or treatment will ultimately be developed.
  • the catheter 20 opens the potential not only to visualize but to directly intervene with the same catheter system.
  • catheter-based systems which to date use conventional x-ray to accomplish their goal of placement and application of a specified therapy.
  • the catheter 20 has all the prerequisites of an ideal imaging and interventional instrument and has the ability to 1) image, 2) obtain hemodynamics by multiple means (pressure dynamics and Doppler), 3) function as a diagnostic as well as therapeutic device, and 4) accommodate other unique technologies which would enhance the application of both systems.
  • intravascular, transvascular, and intracardiac devices could be delivered through the port means described above within or about the heart and blood vessels of the body.
  • the catheters described above could also be used in any ectogenic tissue, such as liver, parenchyma, bile ducts, ureters, urinary bladder, and intracranial—i.e., any place in the body which is echogenic which would allow passage of a catheter for either diagnostic or therapeutic applications using ultrasound visualization.
  • the catheter 20 is a new and exciting innovation to invasive medicine. There are multiple other and yet-to-be-determined applications. However, the new concept described opens the potential development of less expensive, more precise, and safe intravascular and transvascular diagnostic and surgical devices.
  • the catheter 20 is very much different from any conventional ultrasound catheter-based system.
  • the catheter 20 incorporates image and hemodynamic capability as well as the ability to deliver other diverse technologies to specified sites within the cardiovascular system (heart and blood vessels).
  • the catheter 20 is seen as an ideal diagnostic and therapeutic tool for future development.
  • the proposed applications foster greater preciseness, adaptability, and safety.
  • Ultrasound permits visualization from within blood-filled spaces as well as through blood-filled spaces into other water- or fluid-filled tissue.
  • the catheter 20 will evolve into the ultimate interventional system.
  • FIG. 4A is an illustration showing one potential use of the ultrasound imaging and hemodynamic catheter (UIHC).
  • UIHC ultrasound imaging and hemodynamic catheter
  • the UIHC is advanced from the superior vena cava to the tricuspid valve annulus. Simultaneously visualized in the annulus, electrophysiologic and ultimately and ablation procedure are performed. The ability to directly visualize and direct therapeutic catheter devices highlights only one of the many applications of the UIHC.
  • FIG. 10 Another embodiment of the catheter system, generally in accordance with the principles of the present invention is shown in FIG. 10, which is designated as reference numeral 200 .
  • the catheter system 200 has a catheter body 202 and an ultrasonic transducer array 204 mounted on proximate the distal end of the catheter body 202 . It is appreciated that other parts of the catheter system can be similar to those in the catheter systems 20 , 70 , 88 , 104 , 110 , and 130 as shown in FIGS. 1, 5A, 6 A, 7 A, 8 A, and 9 A, respectively.
  • FIG. 10 shows a partial schematic view of the catheter system 200 .
  • the catheter body 202 of the catheter system 200 is inserted into an underfluid cavity of a body 206 .
  • a therapeutic device 208 projects from the catheter system 200 proximate the distal end of the catheter system 200 and manipulates features in the cavity of the body 208 . This manipulation is under observation of a 3-dimensional image shown on a display, which can be similarly connected to the ultrasound transducer array as shown in FIG. 3, outside the body 208 proximate the proximal end of the catheter system 200 .
  • the underfluid catheter body 202 has tool port 210 disposed in the catheter body 202 extending from proximate the proximal end to proximate the distal end of the catheter body 202 for receiving the therapeutic device 208 , such as a catheter, medication, sensor, surgical device, etc., so as to enable such items to be delivered via the tool port to proximate the distal end of the catheter body 202 .
  • the tool port is optional.
  • additional tool ports can be disposed in the catheter body 202 .
  • the therapeutic device 208 is projected into an underfluid environment, as shown in FIGS. 11 - 12 , and operated therein with the aid of a volumetric 3-dimensional image of the underfluid environment and the therapeutic device 208 .
  • the catheter system 200 can also optionally include a guidewire port 212 disposed in the catheter body 202 extending from proximate the proximal end to proximate the distal end of the catheter body 202 for receiving a guide wire 214 .
  • the guide wire 214 guides the catheter body 202 when inserting into a body, such as the body 206 .
  • the catheter system 200 includes a control circuit which can be similar to the control circuitry 34 shown in FIG. 3.
  • the control circuitry 34 is used to control the operation of the ultrasonic transducer array 204 .
  • the control circuitry 34 is electrically interconnected to a transceiver circuitry 35 (T/R) for receiving and transmitting signals via a cable 36 to ultrasonic transducer array 204 .
  • the transceiver circuitry 35 is electrically interconnected to a measuring circuitry, such as the Doppler circuitry 37 , which is interconnected to a first display 38 for displaying hemodynamics, blood flow, etc.
  • the transceiver circuitry 35 is electrically interconnected to an imaging circuitry 39 which is interconnected to a second display 41 for displaying a 3-dimensional image of the underfluid environment.
  • the catheter body 202 can also house some encased electronics 216 .
  • the ultrasonic transducer array 204 is mounted on a side of the catheter body 202 .
  • the array 204 can also be mounted on the tip of the catheter body 202 .
  • the catheter body 202 is a flexible catheter capable of manual or electronic interactive flexible tip.
  • the guidewire port 212 has a diameter of 0.035 inches. It is appreciated that the range of the diameter of the guidewire port 212 can be varied from 0.025 to 0.038 inches.
  • the tool port 210 for transporting the therapeutic device 208 is a 7 French port. It is appreciated that the range of the tool port 210 can be varied from 3 French to 20 French.
  • the ultrasonic transducer array 204 is comprised of a single row of individual crystals 218 . Each crystal 218 is arranged side by side.
  • a field of view generated by the ultrasonic transducer array 204 has a primary tomographic plane 220 in azimuthal dimension along an AZ axis.
  • the row of the array 204 is parallel to the AZ axis.
  • An elevation axis (EL) is perpendicular to the AZ axis.
  • a primary beam from the ultrasonic transducer array 204 lies in the primary tomographic plane 220 .
  • the primary beam has usually a sector configuration (generally a fan or triangle shape) or a linear configuration (generally rectangular shape).
  • the volumetric field of view can be produced by defocusing the primary tomographic plane 220 such that a plurality of elevation planes 222 spread laterally outward from the primary tomographic plane 220 .
  • the primary tomographic plane 220 and the elevation planes 222 together form a volumetric field of view.
  • a lens 224 is placed on the top of the ultrasonic transducer array 204 .
  • the ultrasound beams which are usually collimated are defocused along the elevation direction (EL) after the beams go through the lens 224 (or other lenses 226 , 228 as shown in FIGS. 16 and 17).
  • the lenses 224 , 226 , or 228 are preferred to be made from materials such as a plastic material or silicone rubber. It is appreciated that other types materials can be used to make the lens.
  • the lens 226 is a concave lens, preferably made of silicone rubber, which transmits ultrasound waves slower than the surrounding environment, such as body tissues.
  • the ultrasound waves pass through the lens 226 and then impact on the body tissues.
  • the speed of the ultrasound waves is slower in the lens but faster in tissue (e.g. 1,540 m/sec). Accordingly, the transmitted ultrasound waves, after passing through more slowly transmitted lens 226 and striking faster transmitted body tissues, will be directed outward. As a result, the collimated ultrasound beams are defocused in the elevation dimension.
  • the defocusing can also be achieved by placing a convex lens 228 on the ultrasonic transducer array as shown in FIG. 17 .
  • the convex lens 228 preferably made of plastic, transmits ultrasound waves faster than the surrounding environment, such as body tissues.
  • the ultrasound waves pass through the convex lens 228 and then impact on the body tissues.
  • the ultrasound beams are pulled outward due to the faster velocity in the convex lens 228 .
  • the ultrasound beams are defocused in the elevation dimension.
  • FIG. 18 demonstrates a way of using a lens 230 to, in fact, focus the beams from the transducer array.
  • the collimated ultrasound beams are generated from the ultrasonic transducer array.
  • the convex lens 230 transmits ultrasound waves slower than the surrounding environment, such as body tissues, do. Accordingly, the ultrasound beams are pulled inward due to the faster velocity in body tissues. As a result, the ultrasound beams are focused toward the primary tomographic plane 220 .
  • FIG. 14 shows an alternative embodiment of ultrasonic transducer array 204 ′ which is comprised of multiple rows of individual piezoelectric crystals 218 .
  • the rows of the array 204 ′ are parallel to the AZ axis.
  • the columns of the array 204 ′ are parallel to the elevation dimension along the EL axis, which is perpendicular to AZ axis.
  • This type of array is also called volumetric one and one-half (1 and ⁇ fraction (1/2) ⁇ ) dimensional array.
  • the “elevation” image and the ultimate 3-dimensional image are the result of phasing the crystals in the elevation direction as well as in the azimuthal direction.
  • FIG. 15 shows a second alternative embodiment of ultrasonic transducer array 204 ′′ which is comprised of equal number of crystals 218 in all dimensions. Similar to the one and one-half (1 and 1 ⁇ 2) dimensional array 204 ′ , the rows of the array 204 ′′ are parallel to the AZ axis, and the columns of the array 204 ′′ are parallel to the EL axis. This type of array is also called a two (2) dimensional array. The “elevation” image and the ultimate 3-dimensional image are the result of phasing the crystals in the EL direction as well as the AZ direction.
  • the volumetric field of view as shown in FIGS. 14 - 15 provides 3-dimensional images of structures under observation. Further, the volumetric field of view not only shows, for example, a primary tomographic cut, but also volumes of features, such as tissue.
  • FIGS. 14 and 15 it will be appreciated that no lens is required to generate a volumetric image. Consequently, the ultrasonic beams are focused in both the azimuthal and elevational directions.
  • the volumetric image is generated because the arrays of FIGS. 14 and 15 are 2 dimensional.
  • a volumetric image can be generated by electronically phasing and steering the ultrasonic impulses in both the azimuthal and the elevational directions.
  • the ultrasound transducer is a 7-10 MHz sector array transducer. It is appreciated that the range of the sector array transducer can be varied from 3.7 MHz to 30 MHz.
  • the lenses 224 , 226 , 228 , 230 can be made of different materials which will have variable effects on the transmitted ultrasound beams.
  • a 3-dimensional image can be seen on a 2-dimensional display outside the body 206 in a real-time operation. Elevation defocusing in using a lens does not interfere with the inherent frame rate or adversely affect conventional echo data.
  • the lens can also be fabricated to reduce the strength of the dominant tomographic plane (AZ plane).
  • AZ plane dominant tomographic plane
  • One means of accomplishing this is by changing the attenuation characteristics of the lens so as to reduce the tomographic effect and enhance the volumetric effect of the insonated and displayed object.
  • the lens is optional, for example, as shown in FIGS. 14 and 15 whereby the beams are phased in both the azimuthal and elevational planes.
  • the present invention has numerous clinical applications.
  • One of which is the underfluid imaging when imaging from within chambers, cavities or blood vessels. Since the physical space is small, and the anatomy in question is closely approximated and usually totally surrounds the transducer, a 3-dimensional imaging is a solution to visualizing larger volumes of underfluid tissue.
  • the defocusing lens or electronically controlled phasing in both the azimuthal and elevational directions i.e., using multi-dimensional arrays such as 1- ⁇ fraction (1/2) ⁇ dimensional or 2 dimensional arrays
  • Working port(s) and guidewire(s) are optional. Further, catheter lengths and transducer frequencies are variable.
  • Another application when the working port is optionally used in the catheter, is to intervene or manipulate an underfluid structure, such as cutting an underfluid tissue, etc., by a therapeutic device, such as the therapeutic devices 50 , 84 , 123 , 208 shown in FIGS. 4B, 5A, 8 A, and 12 , respectively. Under such direct volumetric visual guidance, diagnostic and therapeutic procedures can be performed with better spatial orientation.
  • Another application when the guidewire is optionally used in the catheter, is to measure some underfluid features, such as blood flow, etc.
  • the measurement can also be performed under direct volumetric visual guidance in the present invention.

Abstract

An underfluid ultrasound imaging catheter system includes a catheter having a distal end inserted into an underfluid structure, an ultrasonic transducer array mounted proximate the distal end of the catheter wherein the array has a row of individual transducer crystals, a lens mounted on the array for defocusing ultrasound beams in a direction perpendicular to an axis of the array so as to provide a volumetric field of view within which the underfluid features are imaged. Alternatively, the single row of transducer crystals is replaced by multiple rows of transducer crystals so as to provide a volumetric field of view. This imaging catheter system helps an operator see 3-dimensional images of an underfluid environment, such as the 3-dimensional images of fluid-filled cavities of heart, blood vessel, urinary bladder, etc. Features in such wide volumetric field of view can be imaged, measured, or intervened by an underfluid therapeutic device with an aid of the real-time image.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application is a continuation-in-part application of U.S. patent application Ser. No. 08/305,138, filed Sep. 13, 1994, which is a continuation application of U.S. patent application Ser. No. 07/972,626, filed Nov. 6, 1992, now issued U.S. Pat. No. 5,345,940, which is a continuation-in-part application of U.S. patent application Ser. No. 07/790,580, filed on Nov. 8, 1991, now issued U.S. Pat. No. 5,325,860.[0001]
  • BACKGROUND OF THE INVENTION
  • Noninvasive ultrasonic imaging systems are widely used for performing ultrasonic imaging and taking measurements. Such systems typically use scan heads which are placed against a patients skin. Exemplary uses for such systems include heart and internal organ examinations as well as examinations of developing fetuses. These systems operate by transmitting ultrasonic waves into the body, receiving echoes returned from tissue interfaces upon which the waves impinge, and translating the received echo information into a structural representation of the planar slice of the body through which the ultrasonic waves are directed. [0002]
  • Catheter based invasive ultrasound imaging systems, typically used for intracardiac or transvascular imaging, are a relatively new addition to ultrasound armamentarian. Conventional underfluid transducers for use on catheters are comprised of crystal arrays (e.g. linear phased array) or a single crystal translated over a surface, producing a tomographic field of view in an azimuthal plane of the array. Typical arrays include: 1) linear array (linear sequential array), usually producing a rectangular or rhomboidal picture; 2) cylindrical array or rotating crystal, producing a round pie-shaped tomographic cut of structures; and 3) sector array (linear phased array), producing a triangular shaped image emanating from a small transducer source. All images are tomographic in nature and are focused in the azimuthal and elevation plane. The intent of having these conventional transducer configurations is to produce a thin ultrasound cut of the insonated structures. Such tomographic planes by nature are thin and of high resolution. [0003]
  • The narrow field of view provided by conventional catheter transducer configurations is problematic because structures lying outside of the plane of view can only be visualized by reorienting or manipulating the catheter. Due to the tortuous and confined nature of a typical catheter pathway, catheter manipulation is impractical and often impossible. Consequently, the localization of specific targets is difficult and at times can be disorienting because of an inability to appreciate contiguous anatomic landmarks. [0004]
  • Advances in 3-dimensional imaging capabilities have been made with respect to non-catheter related ultrasonic imaging systems. For example, U.S. Pat. No. 5,305,756, issued to Entrekin et al., which is hereby incorporated by reference, discloses general 3-dimensional imaging techniques in a noncatheter based context. What is needed is a catheter based imaging system that utilizes 3-dimensional imaging techniques to provide a wide field of view so as to improve anatomic localization for precision underfluid diagnostics and interventions. [0005]
  • SUMMARY OF THE INVENTION
  • The present invention relates generally to a volumetric, 3-dimensional image ultrasound transducer underfluid catheter system. [0006]
  • The present invention also relates to an ultrasonic and interventional catheter device operated in an intracardiac or transvascular system, with the aid of a volumetric 3-dimensional imaging capability. [0007]
  • In one particular embodiment, the present invention relates to a catheter apparatus comprising an underfluid catheter body having proximal and distal ends. An ultrasonic transducer array is mounted longitudinally along the catheter body proximate the distal end. The transducer array has a volumetric field of view that projects radially/laterally outward from the catheter. Features in such wide volumetric field of view can be imaged, measured, or intervened by an underfluid therapeutic device with an aid of the real-time image. [0008]
  • It is significant that the transducer array described. in the previous paragraph has a 3-dimensional field of view. A first dimension, referred to as an azimuthal direction, is aligned with the length of the transducer array. A second dimension, referred to as a depth direction, is the depth into the body which an ultrasonic signal is transmitted and from which an echo return. A third dimension, referred to as an elevation direction, is perpendicular to both the azimuthal and the depth directions. [0009]
  • If the transducer array comprises a linear phased array having a single row of piezoelectric crystals, a 3-dimensional field of view can be generated by focusing the ultrasound signals in the azimuthal direction (parallel to the longitudinal axis of the catheter) and diverging the ultrasound signals in the elevational direction (transverse to the longitudinal axis of the catheter). The ultrasonic signals can be diverged in the elevational direction through the use of lenses. For example, the signals can be diverged by mounting a silicone rubber concave lens or a plastic convex lens in front of the transducer array. [0010]
  • If the transducer array comprises multiple rows of piezoelectric crystals, a 3-dimensional field of view can be generated by electronically phasing the ultrasound signals in both the azimuthal and elevational directions. Of course, lenses can be used in association with multiple row arrays to further widen the field of view. [0011]
  • It will be appreciated that catheters constructed in accordance with the principles of the present invention can optionally include one or more ports that extend longitudinally through the catheter bodies. The ports are preferably adapted for guiding therapeutic instruments through the catheter and preferably have exit ends adjacent to the field of view of the catheter imaging system. In operation, the ports guide the therapeutic instruments such that the operative ends of a therapeutic instruments are directed toward the 3-dimensional field of view of the imaging system. [0012]
  • It will also be appreciated that catheters constructed in accordance with the principles of the present invention can include one or more guidewire ports which extend longitudinally through the catheters and are adapted for receiving guidewires. [0013]
  • One advantage of the present invention is to provide real-time 3-dimensional images of underfluid features so as to visualize contiguous anatomy, such as a large volume of tissues without frequently rotating, flexing, or extending the catheter. [0014]
  • Another advantage is that the present invention provides a much better underfluid “eye”—a 3-dimensional “motion picture”—for an operator when he/she intervenes the underfluid features by using an underfluid therapeutic device. These images provide the operator a direct aid without opening a large area of a body. [0015]
  • A further advantage is that the present invention have numerous clinical applications. One is; related to underfluid imaging: There is a considerable need to increase the field of view when imaging from within chambers or blood vessels. The physical space of the chambers or blood vessels is small, and the anatomy in question is closed approximated and usually totally surrounds the transducer. A conventional tomographic presentation provides only a limited slice, thus requiring frequent manipulation of transducer in order to visualize contiguous anatomy. The present invention is a solution to visualizing larger volumes of tissue. The underfluid defocusing transducer array does not appreciably affect the electronics and does not require alteration in the display format. The catheter apparatus is immersed in fluid, a homogeneous, low scattering medium, which is an ideal environment for this particular transducer modification. [0016]
  • Another main clinical application is related to underfluid intervention: In diagnostic and therapeutic procedures, there is an increasing need for volumetric 3-dimensional visualization which would improve anatomic localization and recognition of continuous structures and events. [0017]
  • A further advantage of the present invention is that by using such a catheter system, major surgical procedures can be avoided. It dramatically reduces the patient's physical pain in operation and mental distress after operation due to any large visible scars, etc. [0018]
  • These and various other advantages and features of novelty which characterize the invention are pointed out with particularity in the claims annexed hereto and forming a part hereof. However, for a better understanding of the invention, its advantages and objects obtained by its use, reference should be made to the drawings which form a further part hereof, and to the accompanying descriptive matter, in which there is illustrated and described a preferred embodiment of the invention.[0019]
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • A better understanding of the construction and operational characteristics of a preferred embodiment(s) can be realized from a reading of the following detailed description, especially in light of the accompanying drawings in which like reference numerals in the several views generally refer to corresponding parts. [0020]
  • FIG. 1 is a partial perspective view of an embodiment of a catheter in accordance with the principles of the present invention; [0021]
  • FIG. 2 is an enlarged cross-sectional view taken proximate the distal end of the catheter shown in FIG. 1; [0022]
  • FIG. 3 is a block diagram in part and sectional diagram in part illustrating an embodiment of a system utilizing the catheter shown in FIG. 1; [0023]
  • FIG. 4A is an illustration illustrating an application of a catheter in accordance with the principles of the present invention; [0024]
  • FIG. 4B is a partially enlarged illustration of the catheter shown in FIG. 4A. [0025]
  • FIG. 5A shows a partial perspective and cross-sectional view of a first alternate embodiment of a catheter in accordance with the principles of the present invention; [0026]
  • FIG. 5B shows a view of the distal end of the embodiment of the catheter shown in Figure 5A; [0027]
  • FIG. 6A shows a partial perspective and cross-sectional view of a second alternate embodiment of a catheter in accordance with the principles of the present invention; [0028]
  • FIG. 6B shows a view of the distal end of the catheter shown in FIG. 6A; [0029]
  • FIG. 7A shows a partial perspective and cross-sectional view of a variation of the second alternate embodiment of the catheter shown in FIG. 6A; [0030]
  • FIG. 7B shows a view of the distal end of the embodiment of the catheter shown in FIG. 7A; [0031]
  • FIG. 8A shows a partial perspective and cross-sectional view of a third alternate embodiment of a catheter in accordance with the principles of the present invention; [0032]
  • FIG. 8B shows a view of the distal end of the catheter shown in FIG. 8A; [0033]
  • FIG. 8C shows a view of the distal end of the catheter shown in FIG. 8A having an alternatively shaped secondary port;, [0034]
  • FIG. 9A shows partial perspective and cross-sectional view of a fourth alternate embodiment of a catheter in accordance with the principles of the present invention; and [0035]
  • FIG. 9B shows a view of the distal end of the catheter shown in FIG. 9A. [0036]
  • FIG. 10 is a partial schematic view of an embodiment of an underfluid catheter system in accordance with the principles of the present invention. [0037]
  • FIG. 11 is an enlarged view illustrating the catheter system operated underfluid with an aid of a volumetric field of view. [0038]
  • FIG. 12 is an enlarged perspective view illustrating the catheter system providing a volumetric field of view. [0039]
  • FIG. 13 is an enlarged perspective view of an ultrasonic transducer array having a single row of crystals covered by a lens which provides a volumetric field of view. [0040]
  • FIG. 14 is an enlarged perspective view of an alternative ultrasonic transducer array having multiple rows of crystals which provides a volumetric field of view. [0041]
  • FIG. 15 is an enlarged perspective view of a second alternative ultrasonic transducer array having equal number of rows and columns of crystals which provides a volumetric field of view. [0042]
  • FIG. 16 is an enlarged schematic cross-sectional view of a concave silicone rubber lens being placed on the ultrasonic transducer array, providing an outwardly defocused ultrasound beam. [0043]
  • FIG. 17 is an enlarged schematic cross-sectional view of a convex plastic lens being placed on the ultrasonic transducer array, providing an outwardly defocused ultrasound beam. [0044]
  • FIG. 18 is an enlarged schematic cross-sectional view of a convex silicone rubber lens being placed on the ultrasonic transducer array, providing an inwardly focused ultrasound beam. [0045]
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
  • Referring now to FIG. 1-[0046] 3, there is, generally illustrated by reference numeral 20, a catheter in accordance with the principles of the present invention. As shown, catheter 20 includes an elongated flexible or rigid tubular catheter body 22 having a proximal end 24 and a distal end 26. Catheter 20 includes proximate its longitudinal distal end 26 a phased array ultrasonic transducer 30 which is used to transmit ultrasound and receive resultant echoes so as to provide a field of view within which Doppler flow rates can be measured and features imaged. It is appreciated that the other types of ultrasonic transducers can be used in the present invention, such as any mechanical types, or any dynamic array types, or any offset stereoscopic imaging types, or any multidimensional imaging types incorporated into a virtual reality environment for underblood operation, etc. An electrical conductor is disposed in the catheter body 22 for electrically connecting transducer 30 to control circuitry 34 external of catheter body 22. An access port 40 is disposed in catheter body 22 and extends from proximate the proximal end 24 of catheter body 22 to proximate the distal end 26 of catheter body 22. Access port 40 is configured to receive a therapeutic device, such as a catheter, medication, sensors, etc., so as to enable such items to be delivered via access port 40 to distal end 26 of catheter body 22 for operation within the ultrasonic transducer field of view. Such items might be used for intervention; e.g., ablation catheter, surgical device, etc., monitoring blood pressure, sampling blood, etc. A guide wire access port 42 is also disposed within catheter body 22 and extends from proximate proximal end 24 of the catheter body 22 to proximate distal end 26 of catheter body 22 for receiving a guide wire 44.
  • In the preferred embodiment of the present invention, the ultrasonic transducer preferably has a frequency of 5 to 30 megahertz (MHz) and more preferably a frequency of 7 to 10 MHz. Intracardiac imaging in an adult will require image penetration of up to 2 to 10 centimeters (cm) In the preferred embodiment, [0047] catheter body 22 preferably has a diameter of 4 to 24 French (one French divided by Pi equals one millimeter (mm)) and, more preferably, a diameter of 6 to 12 French. In the preferred embodiment, access port 40 has a diameter of 7 to 8 French and guide wire port 42 has a diameter of 0.025 to 0.038 inches.
  • As generally illustrated in FIG. 3, [0048] catheter 20 of the present invention can be utilized in a medical system including the appropriate control circuitry 34 for controlling operation of the ultrasonic transducer. As illustrated in FIG. 3, control circuitry 34 is electrically interconnected to transceiver circuitry 35 (T−/R) for receiving and transmitting signals via a cable 36 to ultrasonic transducer 30. In turn, transceiver circuitry 35 is electrically interconnected to Doppler circuitry 37 and an appropriate display device 38 for displaying hemodynamics or blood flow. In addition, transceiver circuitry 35 is electrically interconnected to suitable imaging circuitry 39 which is interconnected to a display 41 for displaying images.
  • During operation, [0049] control circuitry 34 might be designed to cause ultrasonic transducer 30 to vibrate so as to cause an appropriate ultrasound wave to project from proximate the distal end 26 of catheter body 22. The ultrasound wave, represented by lines 50 in FIG. 2, will propagate through the blood surrounding distal end 26 and a portion of the body structure. A portion of the ultrasound wave so transmitted will be reflected back from both the moving red blood cells and the like and the body structures to impinge upon transducer 30. An electrical signal is thereby generated and transmitted by the cable 36 to the input of transceiver 35. A signal might then be transmitted to Doppler circuitry 37 which will include conventional amplifying and filtering circuitry commonly used in Doppler flow metering equipment. Doppler circuitry 37 will analyze the Doppler shift between the transmitted frequency and the receive frequency to thereby derive an output proportional to flow rate. This output may then be conveniently displayed at display 38 which might be a conventional display terminal. Accordingly, the user will be able to obtain a readout of blood flow rates or hemodynamic information.
  • In order to obtain imaging information, [0050] control circuitry 34 will likewise trigger ultrasonic transducer 30 via transceiver 35 to vibrate and produce an ultrasound wave. Once again, a portion of the wave or energy will be reflected back to ultrasonic transducer 30 by the body features. A corresponding signal will then be sent by cable 36 to transceiver circuitry 35. A corresponding signal is then sent to the imaging circuitry 39 which will analyze the incoming signal to provide, at display 41, which also might be a conventional display apparatus, an image of the body features.
  • This imaging can occur while a therapeutic or surgical device is being used at [0051] distal end 26 of catheter 20 within the field of view provided by ultrasonic transducer 30. Accordingly, the user will be able to monitor his/her actions and the result thereof.
  • As illustrated in FIG. 3, [0052] catheter body 22 might include proximate its proximal end 24 a suitable mounting structure 52 to the access port 40. A therapeutic or surgical device structure 53 might be suitably attached to structure 52 by suitable means, e.g., threaded, etc. As illustrated, an elongated cable-like member 54 will extend along access port 40 and slightly beyond distal end 26 of catheter body 22 wherein an operative portion 56 of the surgical tool might be interconnected.
  • Additional detail of [0053] distal end 26 of catheter body 22 is illustrated in FIGS. 2, 4A, and 4B. As illustrated in FIGS. 2, 4A, and 4B, ultrasonic transducer 30 might include a piezoelectric polymer, such as Polyvinylidenedifloride (PVDF) 60, which is bonded by an epoxy layer 62 to a depression 64 approximate distal end 26. Although some detail is provided with respect to an embodiment of an ultrasonic transducer which might be used, it will be appreciated that various types of transducers having various configurations and orientations might be utilized in keeping with the present invention.
  • As illustrated in FIGS. 4A and 4B, the [0054] operational portion 56 of the therapeutic device is illustrated as generally being capable of operation in the field of view of ultrasonic transducer 30. Accordingly, it is possible for the user to monitor operation of the therapeutic device by use of the ultrasonic transducer. Moreover, it is possible for the user to monitor the features of the body within the field of view before, during and after interventional activity. It is appreciated that the other types of ultrasonic transducers can be used in the present invention, such as any mechanical types, or any dynamic array types, or any offset stereoscopic imaging types, or any multidimensional imaging types incorporated into a virtual reality environment for underblood operation, etc., so that all forms of field of views, such as 1) tomographic (slices), 2) stereoscopic, 3) three-dimensional, 4) virtual reality (multidimensional) can be provided in the present invention. In addition, it is appreciated that the orientations of the scan array on the catheter can be include side-view, end-view, multiview (two or more views that are moveable or imminently directional transducer referred to in the literature as “omnidirectional”), etc.
  • FIG. 5A shows a partial cross-sectional view of a first [0055] alternative embodiment 70 of the catheter apparatus. The catheter apparatus has an elongated flexible or rigid body 72 having a longitudinal axis and a proximal end 74 and a distal end 76. Disposed proximate a second side of body 72 is a port 78 extending through body 72 from proximate proximal end 74 to proximate distal end 76 of body 72. Port 78 is for receiving and delivering to distal end 76 of body 72 a working tool 84. Working tool 84 shown in the Figures is illustrative only, others types of tools now known or later developed may also be delivered to distal end 76 through port 78. Proximate a first side of body 72 is a guide wire port 80 extending through body 72 from proximate proximal end 74 to proximate distal end 76. Shown in guide port 80 is a guide wire 86.
  • [0056] Distal end 76 is disposed at an oblique angle to the longitudinal axis of body 72, the first side of body 72 extending further in the direction of the distal end than the second side of body 72. An ultrasonic transducer 82, having a first side and a second side, is disposed at an oblique angle to the longitudinal axis of body 72 approximately corresponding to the oblique angle of distal end 76 of body 72. The first side of ultrasonic transducer 82 is disposed proximate the first side of body 72 and the second side of transducer 82 is disposed proximate the second side of body 72. Extending from transducer 82 to proximate proximal end 74 of body 72 is an electrical conductor 83 connecting transducer 82 to control circuitry external of catheter 70, as described with respect to catheter 20 above. Having transducer 82 disposed on an oblique angle toward port 78 allows for easy visualization of tools, such as tool 84, extending beyond distal end 76 of body 72.
  • FIG. 5B shows a view of [0057] distal end 76 of body 72, showing guide wire port means 80, transducer 82, and port means 78.
  • FIG. 6A shows a partial cross-sectional view of a second alternative embodiment of the catheter in accordance with the present invention, generally referred to as [0058] 88. Like first alternative embodiment 70, catheter 88 has an elongated flexible or rigid body 90 having a proximal end 92 and a distal end 94. Catheter 88 also has a port 96 extending through body 90 from proximate proximal end 92 to proximate distal end 94. Port 96 has a distal end 97 proximal distal end 94 of body 90. Distal end 97 of port 96 exits body 90 at an acute angle to a first side of body 90 toward distal end 94. Port 96 is for receiving and delivering to distal end 94 a working tool, such as working tool 84. Catheter 88 also has a guide wire port 98 extending through body 90 from proximate proximal end 92 to proximate distal end 94. Guide wire port 98 is for receiving a guide wire 86.
  • Also shown in FIG. 6A is a [0059] transducer 100 disposed to a first side of body 90 between distal end 94 and distal end 97 of port 96. Extending from transducer 100 to proximate proximal end 92 of body 90 is an electrical conductor 102 disposed in the catheter body 90 for electrically connecting transducer 100 to control circuitry external of the catheter. With transducer 100 disposed to the first side of body 90 and distal end 97 of port 96 exiting body 90 at an acute angle relative to the first side of body 90 toward distal end 94, working tools extending from distal end 97 of port 96 will be within the field of view of transducer 100.
  • FIG. 6B shows a view of [0060] distal end 94 of catheter 88, as shown in FIG. 6A.
  • FIG. 7A shows second [0061] alternative embodiment 104, as shown in FIG. 6A, except instead of having a guide wire port 98, this variation of the second alternative embodiment 104 has a deflection wire guidance system 106 for manipulating distal end 94. FIG. 7B shows a view of distal end 94 of the catheter shown in FIG. 7A.
  • FIG. 8A shows a third [0062] alternative embodiment 110 of the catheter in accordance with the present invention. Third alternative embodiment 110 has a body 112 having a distal end 114 and proximal end. Disposed proximate a first side of body 112 is a primary port 118 extending through body 112 from proximate proximal end 116 to proximate distal end 114. Primary port 118 has a distal end 119 proximate distal end 114 of body 112. Oppositely disposed from primary port 118, proximate a second side of body 112 is a secondary port 120 extending through body 112 from proximate proximal end 116 to proximate distal end 114. Secondary port 120 has a distal end 121 proximate distal end 114 of body 112.
  • Mounted proximate [0063] distal end 114 of body 112 is a transducer 122. Extending from transducer 122 through body 112 to proximate proximal end is an electrical conductor for electrically connecting the transducer 122 to control circuitry external of the catheter. Transducer 122 is disposed between distal ends of primary and secondary ports 119 and 121, respectively. With working ports 118 and 120 oppositely disposed on either side of transducer 122, it is possible to conduct two simultaneous applications, such as holding an object with a first tool disposed through one port and operating on the object held by the first tool with a second tool disposed through the other port. A typical working tool 123 and working tool 84 are shown disposed within ports 118 and 120.
  • Although the third alternative embodiment of the [0064] catheter 110 of the present invention does not include a guide wire port means, a guide wire could be used in primary port 118 or secondary port 120 to initially position catheter 110. Then the guide wire could be retracted from port 118 or 120 and a working tool introduced. FIG. 8B shows a view of distal end 114 of catheter 110.
  • FIG. 8C shows a view of a [0065] distal end 124 of a catheter 126 substantially like catheter 110 shown in FIG. 8A and FIG. 8B, except that catheter 126 has a primary port 128 having an arc-like shaped cross-section, rather than a circular shaped cross-section. Although a circular cross-section has been shown in the Figures for the various ports described herein, the size and shape of the ports can be varied without departing from the principals of the present invention.
  • FIG. 9A shows a fourth alternative embodiment of a [0066] catheter 130 of the present invention. Catheter 130 is similar to catheter 70 shown in FIG. 5A and FIG. 5B except that a plurality of ports 132 are disposed proximate a second side of flexible body 131, rather than one port 78, as shown in FIG. 5A. With a plurality of ports, it is possible, for example, to use a therapeutic tool through one port while simultaneously suctioning and removing debris through another port; or a therapeutic tool can be used through one port while simultaneously electrophysiologically monitoring, suctioning and/or biopsying through a second port, third or fourth port.
  • The use of the catheter of the present invention is described with respect to the [0067] preferred embodiment 20. It is understood that the use of alternative embodiments 70, 88, 110, 126 and 130 is analogous. In use, the user would insert flexible catheter body 22 into the body via the appropriate vascular access to the desired location in the body, such as selected venous locations, heart chamber, etc. In one approach, a guide wire might be first inserted into place and then the catheter body fed along the guide wire. The user might then insert a surgical device into the body through access port 40 and feed the surgical device to proximate distal end 26 of catheter body 22. Prior to, during and after operation of the surgical device, the user might obtain both hemodynamic measurements and images from the ultrasonic transducer field of view. By operation of the surgical device within the field of view of transducer, the user can monitor operation of the surgical device at all times.
  • I. DETAILED FEATURES OF THE DISCLOSED CATHETERS
  • A. Frequency Agility Ultrasound Frequency [0068]
  • Frequency agility refers to the ability of a transducer to send and receive at various frequencies, most commonly 3, 5, and 7 MHz. It is also appreciated that a single frequency from a single transducer device can be sent and received. In general, higher frequencies are used to image fine detail of more proximal or closely related objects while lower frequency transducers scan more remote objects with less detail. The proposed device optimally uses a 5 to 20 mHz transducer with the most optimally applied frequency of 7 to 10 mHz. The lower frequency used in the UIHC reflects the need to image larger objects such as the cardiac septa, valves, and extravascular anatomy. [0069]
  • B. Catheter size [0070]
  • Catheter diameters will generally be larger than intravascular catheters and will range 4 to 24 French with the [0071] optimal catheter diameter 6 to 12 French (French size=French divided by Pi plus millimeter diameter).
  • C. Intervention [0072]
  • One primary function of this catheter system is to guide the logical and safe use of various a) ablation, b) laser, c) cutting, occluding, e) etc., catheter-based interventional tools. The invention has the access port through which other technologies (devices) can be passed. Once the interventional tool exits the catheter tip, it can be directed repeatedly and selectively to specific site for controlled intervention. [0073]
  • D. Imaging [0074]
  • The invention is also an imaging system capable of visualizing intracardiac, intravascular, and extravascular structures. Because the transducer frequencies utilized are usually lower than intravascular systems, the [0075] catheter 20 can see multiple cardiac cavities and visualize structures outside the vascular system. The imaging capability is basically two-fold: 1) diagnostic and 2) application.
  • 1. Diagnostic imaging: The [0076] catheter 20 can effectively perform diagnostic intracardiac and transvascular imaging. This application will more than likely be performed just prior to an interventional application. The intervention then will follow using the same catheter system and its unique delivery capability. Some examples of diagnostic imaging include 1) accurate visualization and measurement of an intracardiac defect, 2) characterization of valve orifice, 3) localization of a tumor and its connections, 4) etc. Extravascular diagnoses would include 1) visualize pancreatic mass/pathology, 2) retroperitoneal pathology, 3) intracranial imaging, 4) recognition of perivascular pathology, and 5) imaging of other fluid containing space such as urinary bladder, bile system, fluid filled orifice or cavity (e.g. filled saline), etc.
  • 2. Application imaging refers to the use of the catheter and its imaging capability to deliver and then apply another technology such as 1) occlusion device for closure of a septal defect, 2) ablation catheters for treatment of bypass tracts, 3) creation of a defect such as that with the blade septostomy catheter or laser-based catheter system, and 4) directing of valvuloplasty (such as prostrate surgery, placement of stents, gallstone removal etc.), etc. By direct imaging of an application, such as ablation, the procedure will be able to be performed more safely and repeatedly, and the result can be better assessed. [0077]
  • E. Hemodynamics [0078]
  • The [0079] catheter 20 is a truly combined ultrasound Doppler and conventional hemodynamic catheter. There are Doppler catheters, and there are catheters capable of imaging and measuring hemodynamic pressure. However, the catheter 20 is capable of Doppler hemodynamics (continuous and pulsed wave Doppler) as well as high-fidelity hemodynamic pressure recording while simultaneously imaging the heart and blood vessel. The catheter 20 provides a combination of imaging, hemodynamic, and interventional delivery catheter.
  • II. ANALOGY WITH OTHER EXISTING THERAPEUTIC TECHNOLOGIES
  • Like interventional peritoneoscopy, intracardiac ultrasound is capable of 1) imaging, 2) delivering a therapeutic device, and 3) obtaining simultaneous hemodynamics which can be used to develop less invasive cardiac surgical techniques. This simultaneous use of one or more devices within the heart or vascular tree opens up the potential to develop less invasive surgical therapies. Examples would include 1) removal of a cardiac tumor by visually grasping the tumor with one device and visually cutting its attachment with a second device, thus allowing less invasive extraction of intracardiac mass lesions, 2) visually placing an electrophysiologic catheter on a bypass tract and then with direct ultrasound visualization ablate the underlying tract with the second device, 3) visually performing laser surgery such as creating an intra-atrial defect, vaporization of obstructing thrombus such as is seen in pseudointimal occlusion of conduits, 4) visually removing a foreign body from the heart or vascular tree, and 5) directing intravascular surgery from within a blood vessel or monitoring concomitant hemodynamic changes. [0080]
  • III. SELECTED APPLICATIONS INCLUDE THE FOLLOWING
  • A. Radio-frequency Ablation [0081]
  • Presently a bypass tract is localized by an electrophysiologic study which systematically maps the atrioventricular valve annulus. Positioning of the ablation catheter is determined by x-ray fluoroscopy and certain electrical measurements which relate the distance of the ablation catheter from a reference catheter. The [0082] catheter 20 will allow an operator to map the atrioventricular valve under direct ultrasound visualization. Thus, increased accuracy of catheter placement, precision of the applied therapy, and immediate assessment of outcome would result.
  • The above ablation technique would be particularly applicable for right-sided bypass tracts (in and around the tricuspid valve annulus). This would be accomplished by placement of the [0083] catheter 20 through the superior vena cava above the tricuspid annulus.
  • For left-sided bypass tracts, the [0084] catheter 20 could be placed across the atrial septum under direct ultrasound visualization. The mitral annulus could thus be mapped directly and the localized bypass tract precisely ablated under visual ultrasonic and hemodynamic direction. Complications such as valve perforation, multiple imprecise applications of ablation energy, and inadvertent ablation of normal conduction tissue would be substantially reduced.
  • Ablation of bypass tracts would be an ideal utilization of the proposed ultrasonic interventional catheter system. [0085]
  • B. Cardiac biopsy [0086]
  • In the era of safe cardiac biopsy, there is a need for precision biopsy. Ultrasound direction of the biopsy device to an intracardiac tumor, avoidance of scar, and selective biopsy of suspect tissue are feasible with the [0087] catheter 20 device. One of the more frequently life-threatening complications in the cardiac catheterization laboratory is catheter perforation of the heart. Such complications most commonly accompany cardiac biopsy, electrophysiologic catheter manipulation, and valvuloplasty. Use of an intracardiac ultrasound imaging, hemodynamics, and delivery catheter should substantially increase or improve safety of these procedures.
  • C. Transvascular diagnoses [0088]
  • The [0089] catheter 20 will allow visualization of perivascular and extravascular pathology. Transvascular or transorgan imaging and localization of pathology out of the immediate vascular tree will result in a substantial step forward in the diagnosis and possible treatment of difficult to reach pathology. The catheter 20 cannot only diagnose but guide a biopsy needle and therapeutic device to an extravascular lesion in question. The retroperitoneum, mediastinum, and basal cerebrovascular pathology are logical areas of interest. Accurate characterization of various pathologies will be more feasible. Every organ has its own vascular system, and the proposed ultrasound transvascular system is an ideal tool to assess difficult to reach areas of the body. The vascular system is a conduit to each organ, and the catheter 20 can be delivered to each organ. Characterization of the underlying parenchyma and possible transvascular biopsy or treatment will ultimately be developed.
  • D. Ultrasound Manipulation of Therapeutic Devices Within the Heart and Blood Vessels [0090]
  • The [0091] catheter 20 opens the potential not only to visualize but to directly intervene with the same catheter system. There are numerous intraoperative catheter-based systems which to date use conventional x-ray to accomplish their goal of placement and application of a specified therapy. There is a need for a device which can more precisely guide such catheter-based systems. It is too expensive and technically impractical to incorporate ultrasound into every catheter based technology. The catheter 20 has all the prerequisites of an ideal imaging and interventional instrument and has the ability to 1) image, 2) obtain hemodynamics by multiple means (pressure dynamics and Doppler), 3) function as a diagnostic as well as therapeutic device, and 4) accommodate other unique technologies which would enhance the application of both systems.
  • E. General Applications [0092]
  • It is anticipated that intravascular, transvascular, and intracardiac devices could be delivered through the port means described above within or about the heart and blood vessels of the body. The catheters described above, however, could also be used in any ectogenic tissue, such as liver, parenchyma, bile ducts, ureters, urinary bladder, and intracranial—i.e., any place in the body which is echogenic which would allow passage of a catheter for either diagnostic or therapeutic applications using ultrasound visualization. [0093]
  • F. Expanding Applications of Technologies [0094]
  • The [0095] catheter 20 is a new and exciting innovation to invasive medicine. There are multiple other and yet-to-be-determined applications. However, the new concept described opens the potential development of less expensive, more precise, and safe intravascular and transvascular diagnostic and surgical devices.
  • IV. SUMMARY
  • The [0096] catheter 20 is very much different from any conventional ultrasound catheter-based system. The catheter 20 incorporates image and hemodynamic capability as well as the ability to deliver other diverse technologies to specified sites within the cardiovascular system (heart and blood vessels). The catheter 20 is seen as an ideal diagnostic and therapeutic tool for future development. The proposed applications foster greater preciseness, adaptability, and safety. Ultrasound permits visualization from within blood-filled spaces as well as through blood-filled spaces into other water- or fluid-filled tissue. The catheter 20 will evolve into the ultimate interventional system.
  • FIG. 4A is an illustration showing one potential use of the ultrasound imaging and hemodynamic catheter (UIHC). In this particular example, the UIHC is advanced from the superior vena cava to the tricuspid valve annulus. Simultaneously visualized in the annulus, electrophysiologic and ultimately and ablation procedure are performed. The ability to directly visualize and direct therapeutic catheter devices highlights only one of the many applications of the UIHC. [0097]
  • Another embodiment of the catheter system, generally in accordance with the principles of the present invention is shown in FIG. 10, which is designated as [0098] reference numeral 200. The catheter system 200 has a catheter body 202 and an ultrasonic transducer array 204 mounted on proximate the distal end of the catheter body 202. It is appreciated that other parts of the catheter system can be similar to those in the catheter systems 20, 70, 88, 104, 110, and 130 as shown in FIGS. 1, 5A, 6A, 7A, 8A, and 9A, respectively. For the purpose of illustration and explanation, FIG. 10 shows a partial schematic view of the catheter system 200.
  • In FIG. 11, the [0099] catheter body 202 of the catheter system 200 is inserted into an underfluid cavity of a body 206. In FIG. 12, a therapeutic device 208 projects from the catheter system 200 proximate the distal end of the catheter system 200 and manipulates features in the cavity of the body 208. This manipulation is under observation of a 3-dimensional image shown on a display, which can be similarly connected to the ultrasound transducer array as shown in FIG. 3, outside the body 208 proximate the proximal end of the catheter system 200.
  • Likewise, the [0100] underfluid catheter body 202 has tool port 210 disposed in the catheter body 202 extending from proximate the proximal end to proximate the distal end of the catheter body 202 for receiving the therapeutic device 208, such as a catheter, medication, sensor, surgical device, etc., so as to enable such items to be delivered via the tool port to proximate the distal end of the catheter body 202. It will be appreciated that the tool port is optional. It will also be appreciated that additional tool ports can be disposed in the catheter body 202. The therapeutic device 208 is projected into an underfluid environment, as shown in FIGS. 11-12, and operated therein with the aid of a volumetric 3-dimensional image of the underfluid environment and the therapeutic device 208.
  • Further, the [0101] catheter system 200 can also optionally include a guidewire port 212 disposed in the catheter body 202 extending from proximate the proximal end to proximate the distal end of the catheter body 202 for receiving a guide wire 214. The guide wire 214 guides the catheter body 202 when inserting into a body, such as the body 206.
  • Further, the [0102] catheter system 200 includes a control circuit which can be similar to the control circuitry 34 shown in FIG. 3. The control circuitry 34 is used to control the operation of the ultrasonic transducer array 204. The control circuitry 34 is electrically interconnected to a transceiver circuitry 35 (T/R) for receiving and transmitting signals via a cable 36 to ultrasonic transducer array 204. In turn, the transceiver circuitry 35 is electrically interconnected to a measuring circuitry, such as the Doppler circuitry 37, which is interconnected to a first display 38 for displaying hemodynamics, blood flow, etc. In addition, the transceiver circuitry 35 is electrically interconnected to an imaging circuitry 39 which is interconnected to a second display 41 for displaying a 3-dimensional image of the underfluid environment.
  • As shown in FIG. 10, the [0103] catheter body 202 can also house some encased electronics 216.
  • In the preferred embodiment of the present invention, the [0104] ultrasonic transducer array 204 is mounted on a side of the catheter body 202. The array 204 can also be mounted on the tip of the catheter body 202. The catheter body 202 is a flexible catheter capable of manual or electronic interactive flexible tip. The guidewire port 212 has a diameter of 0.035 inches. It is appreciated that the range of the diameter of the guidewire port 212 can be varied from 0.025 to 0.038 inches. The tool port 210 for transporting the therapeutic device 208 is a 7 French port. It is appreciated that the range of the tool port 210 can be varied from 3 French to 20 French.
  • As shown in FIG. 13, the [0105] ultrasonic transducer array 204 is comprised of a single row of individual crystals 218. Each crystal 218 is arranged side by side. A field of view generated by the ultrasonic transducer array 204 has a primary tomographic plane 220 in azimuthal dimension along an AZ axis. The row of the array 204 is parallel to the AZ axis. An elevation axis (EL) is perpendicular to the AZ axis. A primary beam from the ultrasonic transducer array 204 lies in the primary tomographic plane 220. The primary beam has usually a sector configuration (generally a fan or triangle shape) or a linear configuration (generally rectangular shape).
  • The volumetric field of view can be produced by defocusing the [0106] primary tomographic plane 220 such that a plurality of elevation planes 222 spread laterally outward from the primary tomographic plane 220. The primary tomographic plane 220 and the elevation planes 222 together form a volumetric field of view. To defocus the primary tomographic plane 220 as shown in FIG. 13, a lens 224 is placed on the top of the ultrasonic transducer array 204. The ultrasound beams which are usually collimated are defocused along the elevation direction (EL) after the beams go through the lens 224 (or other lenses 226, 228 as shown in FIGS. 16 and 17).
  • The [0107] lenses 224, 226, or 228 are preferred to be made from materials such as a plastic material or silicone rubber. It is appreciated that other types materials can be used to make the lens.
  • In FIG. 16, the [0108] lens 226 is a concave lens, preferably made of silicone rubber, which transmits ultrasound waves slower than the surrounding environment, such as body tissues. The ultrasound waves pass through the lens 226 and then impact on the body tissues. The speed of the ultrasound waves is slower in the lens but faster in tissue (e.g. 1,540 m/sec). Accordingly, the transmitted ultrasound waves, after passing through more slowly transmitted lens 226 and striking faster transmitted body tissues, will be directed outward. As a result, the collimated ultrasound beams are defocused in the elevation dimension.
  • The defocusing can also be achieved by placing a [0109] convex lens 228 on the ultrasonic transducer array as shown in FIG. 17. The convex lens 228, preferably made of plastic, transmits ultrasound waves faster than the surrounding environment, such as body tissues. The ultrasound waves pass through the convex lens 228 and then impact on the body tissues. The ultrasound beams are pulled outward due to the faster velocity in the convex lens 228. As a result, the ultrasound beams are defocused in the elevation dimension.
  • FIG. 18, on the other hand, demonstrates a way of using a [0110] lens 230 to, in fact, focus the beams from the transducer array. The collimated ultrasound beams are generated from the ultrasonic transducer array. The convex lens 230 transmits ultrasound waves slower than the surrounding environment, such as body tissues, do. Accordingly, the ultrasound beams are pulled inward due to the faster velocity in body tissues. As a result, the ultrasound beams are focused toward the primary tomographic plane 220.
  • FIG. 14 shows an alternative embodiment of [0111] ultrasonic transducer array 204′ which is comprised of multiple rows of individual piezoelectric crystals 218. The rows of the array 204′ are parallel to the AZ axis. The columns of the array 204′ are parallel to the elevation dimension along the EL axis, which is perpendicular to AZ axis. This type of array is also called volumetric one and one-half (1 and {fraction (1/2)}) dimensional array. The “elevation” image and the ultimate 3-dimensional image are the result of phasing the crystals in the elevation direction as well as in the azimuthal direction.
  • FIG. 15 shows a second alternative embodiment of [0112] ultrasonic transducer array 204″ which is comprised of equal number of crystals 218 in all dimensions. Similar to the one and one-half (1 and ½) dimensional array 204′ , the rows of the array 204″ are parallel to the AZ axis, and the columns of the array 204″ are parallel to the EL axis. This type of array is also called a two (2) dimensional array. The “elevation” image and the ultimate 3-dimensional image are the result of phasing the crystals in the EL direction as well as the AZ direction.
  • Accordingly, the volumetric field of view as shown in FIGS. [0113] 14-15 provides 3-dimensional images of structures under observation. Further, the volumetric field of view not only shows, for example, a primary tomographic cut, but also volumes of features, such as tissue.
  • In the embodiments of FIGS. 14 and 15, it will be appreciated that no lens is required to generate a volumetric image. Consequently, the ultrasonic beams are focused in both the azimuthal and elevational directions. The volumetric image is generated because the arrays of FIGS. 14 and 15 are 2 dimensional. As a result, a volumetric image can be generated by electronically phasing and steering the ultrasonic impulses in both the azimuthal and the elevational directions. [0114]
  • In the preferred embodiment, the ultrasound transducer is a 7-10 MHz sector array transducer. It is appreciated that the range of the sector array transducer can be varied from 3.7 MHz to 30 MHz. [0115]
  • It is also appreciated that the [0116] lenses 224, 226, 228, 230 can be made of different materials which will have variable effects on the transmitted ultrasound beams. By using such defocusing lens, a 3-dimensional image can be seen on a 2-dimensional display outside the body 206 in a real-time operation. Elevation defocusing in using a lens does not interfere with the inherent frame rate or adversely affect conventional echo data.
  • The lens can also be fabricated to reduce the strength of the dominant tomographic plane (AZ plane). One means of accomplishing this is by changing the attenuation characteristics of the lens so as to reduce the tomographic effect and enhance the volumetric effect of the insonated and displayed object. [0117]
  • The lens is optional, for example, as shown in FIGS. 14 and 15 whereby the beams are phased in both the azimuthal and elevational planes. [0118]
  • The present invention has numerous clinical applications. One of which is the underfluid imaging when imaging from within chambers, cavities or blood vessels. Since the physical space is small, and the anatomy in question is closely approximated and usually totally surrounds the transducer, a 3-dimensional imaging is a solution to visualizing larger volumes of underfluid tissue. In this imaging application, the defocusing lens or electronically controlled phasing in both the azimuthal and elevational directions (i.e., using multi-dimensional arrays such as 1-{fraction (1/2)} dimensional or 2 dimensional arrays) produces volumetric images. Working port(s) and guidewire(s) are optional. Further, catheter lengths and transducer frequencies are variable. [0119]
  • Another application, when the working port is optionally used in the catheter, is to intervene or manipulate an underfluid structure, such as cutting an underfluid tissue, etc., by a therapeutic device, such as the [0120] therapeutic devices 50, 84, 123, 208 shown in FIGS. 4B, 5A, 8A, and 12, respectively. Under such direct volumetric visual guidance, diagnostic and therapeutic procedures can be performed with better spatial orientation.
  • Another application, when the guidewire is optionally used in the catheter, is to measure some underfluid features, such as blood flow, etc. The measurement can also be performed under direct volumetric visual guidance in the present invention. [0121]
  • Other generic applications include Doppler blood flow determination, color flow imaging, etc. [0122]
  • Thus, the preferred embodiment of the present invention has been described in detail. It is to be understood, however, that even though numerous characteristics and advantages of the present invention have been set forth in the foregoing description, together with details of the structure and function of the invention, the disclosure is illustrative only, and changes may be made in detail, especially in matters of shape, size and arrangement of parts within the principles of the invention to the full extent indicated by the broad general meaning of the terms in which the appended claims are expressed. [0123]

Claims (11)

What is claimed is:
1. A catheter apparatus, comprising:
an elongated body having proximal and distal ends;
an ultrasonic transducer linear phased array mounted proximate the distal end of the elongated body, the array transmitting ultrasound beams and receiving resultant echoes, the array comprising a row of individual transducer segments aligned generally in an azimuthal dimension;
a lens mounted on the array for defocusing the ultrasound beams such that at least some of the beams are directed laterally outward in an elevational dimension which is perpendicular to the azimuthal dimension so as to provide a volumetric field of view within which flow rates can be measured and features imaged; and
an electrical conductor, disposed in the elongated body, electrically connecting the transducer to a control circuitry external of the elongated body.
2. A catheter apparatus in accordance with claim 1, wherein the lens is a planoconcave lens made from silicone rubber.
3. A catheter apparatus in accordance with claim 1, wherein the lens is a planoconvex lens made from a plastic material.
4. A catheter apparatus, comprising:
an elongated body having proximal and distal ends;
an ultrasonic transducer linear phased array mounted proximate the distal end of the elongated body, the array transmitting ultrasound beams and receiving resultant echoes, the array comprising a plurality of rows of individual transducer segments, the transducer segments being phased in both an elevation direction of the array as well as an azimuthal direction of the array to produce a volumetric field of view within which flow rates can be measured and features imaged; and
an electrical conductor, disposed in the elongated body, electrically connecting the transducer to a control circuitry external of the elongated body.
5. A catheter apparatus, comprising:
an elongated body having proximal and distal ends;
an ultrasonic transducer linear phased array mounted proximate the distal end of the elongated body, the array transmitting ultrasound beams and receiving resultant echoes, the array comprising equal numbers of rows and columns of individual transducer segments, the transducer segments being phased in both an elevation direction of the array as well as an azimuthal direction of the array to produce a volumetric field of view within which flow rates can be measured and features imaged; and
an electrical conductor, disposed in the elongated body, electrically connecting the transducer to a control circuitry external of the elongated body.
6. A catheter apparatus for underfluid imaging, intervention, and measuring, comprising:
an elongated, flexible body having proximal and distal ends, the distal end being inserted into an underfluid structure;
an ultrasonic transducer linear phased array mounted on the elongated body proximate the distal end of the elongated body, the array producing a volumetric field of view of the underfluid structure in front of the array outside the elongated body, within which features can be imaged, intervened by a therapeutic device, and measured;
a port disposed in the elongated body extending from proximate the proximal end to proximate the distal end of the elongated body for receiving the therapeutic device, the therapeutic device being operated underfluid in the volumetric field of view; and
means for actuating the ultrasonic transducer linear phased array.
7. A catheter in accordance with claim 6, further comprising a guidewire port disposed in the elongated body extending from proximate the proximal end to proximate the distal end of the elongated body for receiving a guide wire.
8. A catheter apparatus, comprising:
an elongated catheter body having proximal and distal ends and a longitudinal axis;
an ultrasound imaging system for transmitting ultrasonic beams and receiving resultant echoes, the ultrasound imaging system including a transducer array mounted proximate the distal end of the elongated catheter body and including a plurality of individual transducer segments aligned along an azimuthal dimension that is substantially parallel to the longitudinal axis of the elongated catheter body, the ultrasound imaging system being constructed and arranged to spread the ultrasonic beams such that the ultrasonic beams cover a 3-dimensional scanning region, the scanning region being defined by the azimuthal dimension, a depth dimension transversely aligned with respect to the azimuthal dimension, and an elevational dimension transversely aligned with respect to both the depth dimension and the azimuthal dimension.
9. The catheter apparatus of claim 8, wherein the ultrasound imaging system includes a lens for spreading the ultrasonic beams in the elevational dimension.
10. The catheter apparatus of claim 8, wherein the transducer array includes multiple rows of transducer segments, and the transducer array is phased in both the elevational dimension and the azimuthal dimension.
11. The catheter apparatus of claim 8, wherein the transducer array includes one and one half rows of transducer segments, and the transducer array is phased in both the elevational dimension and the azimuthal dimension.
US10/003,666 1991-11-08 2001-10-23 Volumetric image ultrasound transducer underfluid catheter system Abandoned US20020058873A1 (en)

Priority Applications (6)

Application Number Priority Date Filing Date Title
US07/790,580 US5325860A (en) 1991-11-08 1991-11-08 Ultrasonic and interventional catheter and method
PCT/US1992/009835 WO1993008738A1 (en) 1991-11-08 1992-11-06 Transvascular ultrasound hemodynamic catheter and method
US07/972,626 US5345940A (en) 1991-11-08 1992-11-06 Transvascular ultrasound hemodynamic and interventional catheter and method
US09/586,193 US6306096B1 (en) 1991-11-08 2000-06-02 Volumetric image ultrasound transducer underfluid catheter system
US10/003,666 US20020058873A1 (en) 1991-11-08 2001-10-23 Volumetric image ultrasound transducer underfluid catheter system
US10/401,287 US7156812B2 (en) 1991-11-08 2003-03-27 Volumetric image ultrasound transducer underfluid catheter system

Applications Claiming Priority (8)

Application Number Priority Date Filing Date Title
US07/790,580 US5325860A (en) 1991-11-08 1991-11-08 Ultrasonic and interventional catheter and method
US07/972,626 US5345940A (en) 1991-11-08 1992-11-06 Transvascular ultrasound hemodynamic and interventional catheter and method
US30513894A 1994-09-13 1994-09-13
US08/678,380 US5704361A (en) 1991-11-08 1996-06-28 Volumetric image ultrasound transducer underfluid catheter system
US09/003,248 US6129672A (en) 1991-11-08 1998-01-06 Volumetric image ultrasound transducer underfluid catheter system
US09/087,520 US6099475A (en) 1991-11-08 1998-05-29 Volumetric image ultrasound transducer underfluid catheter system
US09/586,193 US6306096B1 (en) 1991-11-08 2000-06-02 Volumetric image ultrasound transducer underfluid catheter system
US10/003,666 US20020058873A1 (en) 1991-11-08 2001-10-23 Volumetric image ultrasound transducer underfluid catheter system

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US09/586,193 Continuation US6306096B1 (en) 1991-11-08 2000-06-02 Volumetric image ultrasound transducer underfluid catheter system

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US10/401,287 Continuation US7156812B2 (en) 1991-11-08 2003-03-27 Volumetric image ultrasound transducer underfluid catheter system

Publications (1)

Publication Number Publication Date
US20020058873A1 true US20020058873A1 (en) 2002-05-16

Family

ID=32046202

Family Applications (5)

Application Number Title Priority Date Filing Date
US07/790,580 Expired - Lifetime US5325860A (en) 1991-11-08 1991-11-08 Ultrasonic and interventional catheter and method
US07/972,626 Expired - Lifetime US5345940A (en) 1991-11-08 1992-11-06 Transvascular ultrasound hemodynamic and interventional catheter and method
US09/586,193 Expired - Fee Related US6306096B1 (en) 1991-11-08 2000-06-02 Volumetric image ultrasound transducer underfluid catheter system
US10/003,666 Abandoned US20020058873A1 (en) 1991-11-08 2001-10-23 Volumetric image ultrasound transducer underfluid catheter system
US10/401,287 Expired - Fee Related US7156812B2 (en) 1991-11-08 2003-03-27 Volumetric image ultrasound transducer underfluid catheter system

Family Applications Before (3)

Application Number Title Priority Date Filing Date
US07/790,580 Expired - Lifetime US5325860A (en) 1991-11-08 1991-11-08 Ultrasonic and interventional catheter and method
US07/972,626 Expired - Lifetime US5345940A (en) 1991-11-08 1992-11-06 Transvascular ultrasound hemodynamic and interventional catheter and method
US09/586,193 Expired - Fee Related US6306096B1 (en) 1991-11-08 2000-06-02 Volumetric image ultrasound transducer underfluid catheter system

Family Applications After (1)

Application Number Title Priority Date Filing Date
US10/401,287 Expired - Fee Related US7156812B2 (en) 1991-11-08 2003-03-27 Volumetric image ultrasound transducer underfluid catheter system

Country Status (2)

Country Link
US (5) US5325860A (en)
WO (1) WO1993008738A1 (en)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060025691A1 (en) * 2004-07-29 2006-02-02 Fujinon Corporation Ultrasonic endoscope
US20070167825A1 (en) * 2005-11-30 2007-07-19 Warren Lee Apparatus for catheter tips, including mechanically scanning ultrasound probe catheter tip
US20070167813A1 (en) * 2005-11-30 2007-07-19 Warren Lee Apparatuses Comprising Catheter Tips, Including Mechanically Scanning Ultrasound Probe Catheter Tip
US20070167826A1 (en) * 2005-11-30 2007-07-19 Warren Lee Apparatuses for thermal management of actuated probes, such as catheter distal ends
US20070167824A1 (en) * 2005-11-30 2007-07-19 Warren Lee Method of manufacture of catheter tips, including mechanically scanning ultrasound probe catheter tip, and apparatus made by the method
US20070182287A1 (en) * 2004-04-20 2007-08-09 Marc Lukacs Arrayed Ultrasonic Transducer
US20100156244A1 (en) * 2008-09-18 2010-06-24 Marc Lukacs Methods for manufacturing ultrasound transducers and other components
US7901358B2 (en) 2005-11-02 2011-03-08 Visualsonics Inc. High frequency array ultrasound system
US9173047B2 (en) 2008-09-18 2015-10-27 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components
US9184369B2 (en) 2008-09-18 2015-11-10 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components

Families Citing this family (372)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5588432A (en) * 1988-03-21 1996-12-31 Boston Scientific Corporation Catheters for imaging, sensing electrical potentials, and ablating tissue
US5749914A (en) * 1989-01-06 1998-05-12 Advanced Coronary Intervention Catheter for obstructed stent
US5704361A (en) * 1991-11-08 1998-01-06 Mayo Foundation For Medical Education And Research Volumetric image ultrasound transducer underfluid catheter system
US5325860A (en) 1991-11-08 1994-07-05 Mayo Foundation For Medical Education And Research Ultrasonic and interventional catheter and method
US5713363A (en) * 1991-11-08 1998-02-03 Mayo Foundation For Medical Education And Research Ultrasound catheter and method for imaging and hemodynamic monitoring
US7930012B2 (en) * 1992-09-23 2011-04-19 St. Jude Medical, Atrial Fibrillation Division, Inc. Chamber location method
USRE41334E1 (en) 1992-09-23 2010-05-11 St. Jude Medical, Atrial Fibrillation Division, Inc. Endocardial mapping system
EP0661948B1 (en) * 1992-09-23 1997-11-19 Endocardial Solutions, Inc. Endocardial mapping system
US7189208B1 (en) * 1992-09-23 2007-03-13 Endocardial Solutions, Inc. Method for measuring heart electrophysiology
US20070016071A1 (en) * 1993-02-01 2007-01-18 Volcano Corporation Ultrasound transducer assembly
WO1994027501A1 (en) * 1993-05-24 1994-12-08 Boston Scientific Corporation Medical acoustic imaging catheter and guidewire
WO1994027502A1 (en) * 1993-05-25 1994-12-08 Boston Scientific Corporation Medical acoustic imaging catheter and guidewire
US5630837A (en) * 1993-07-01 1997-05-20 Boston Scientific Corporation Acoustic ablation
DE69432148T2 (en) * 1993-07-01 2003-10-16 Boston Scient Ltd CATHETER FOR IMAGE DISPLAY, DISPLAY OF ELECTRICAL SIGNALS AND ABLATION
US5840031A (en) * 1993-07-01 1998-11-24 Boston Scientific Corporation Catheters for imaging, sensing electrical potentials and ablating tissue
US5571088A (en) * 1993-07-01 1996-11-05 Boston Scientific Corporation Ablation catheters
US5860974A (en) * 1993-07-01 1999-01-19 Boston Scientific Corporation Heart ablation catheter with expandable electrode and method of coupling energy to an electrode on a catheter shaft
US5391199A (en) * 1993-07-20 1995-02-21 Biosense, Inc. Apparatus and method for treating cardiac arrhythmias
US5409000A (en) * 1993-09-14 1995-04-25 Cardiac Pathways Corporation Endocardial mapping and ablation system utilizing separately controlled steerable ablation catheter with ultrasonic imaging capabilities and method
US5456689A (en) * 1993-10-13 1995-10-10 Arnold J. Kresch Method and device for tissue resection
JP2833456B2 (en) * 1993-11-22 1998-12-09 株式会社東芝 Insertable ultrasound system
US5474075A (en) * 1993-11-24 1995-12-12 Thomas Jefferson University Brush-tipped catheter for ultrasound imaging
DE69417580T2 (en) * 1993-12-22 1999-12-16 Sulzer Osypka Gmbh ULTRASONICALLY MARKED INTRACARDIAL ABLATION CATHETER
US5873828A (en) * 1994-02-18 1999-02-23 Olympus Optical Co., Ltd. Ultrasonic diagnosis and treatment system
US5672172A (en) * 1994-06-23 1997-09-30 Vros Corporation Surgical instrument with ultrasound pulse generator
US5549601A (en) * 1994-10-11 1996-08-27 Devices For Vascular Intervention, Inc. Delivery of intracorporeal probes
US6032673A (en) * 1994-10-13 2000-03-07 Femrx, Inc. Methods and devices for tissue removal
US5766016A (en) * 1994-11-14 1998-06-16 Georgia Tech Research Corporation Surgical simulator and method for simulating surgical procedure
US6176842B1 (en) * 1995-03-08 2001-01-23 Ekos Corporation Ultrasound assembly for use with light activated drugs
US6210356B1 (en) 1998-08-05 2001-04-03 Ekos Corporation Ultrasound assembly for use with a catheter
AU5183096A (en) * 1995-03-08 1996-09-23 Ekos, Llc Ultrasound therapy device
EP0749723A1 (en) * 1995-06-23 1996-12-27 Arno Schnorrenberg Chirurgiemechanik Intestinal ultrasound probe for trans-intestinal diagnosis in birds, reptiles and/or small mammals
CA2225784A1 (en) * 1995-06-30 1997-01-23 Boston Scientific Corporation Ultrasound imaging catheter with a cutting element
US6302875B1 (en) 1996-10-11 2001-10-16 Transvascular, Inc. Catheters and related devices for forming passageways between blood vessels or other anatomical structures
US6726677B1 (en) * 1995-10-13 2004-04-27 Transvascular, Inc. Stabilized tissue penetrating catheters
US6190353B1 (en) * 1995-10-13 2001-02-20 Transvascular, Inc. Methods and apparatus for bypassing arterial obstructions and/or performing other transvascular procedures
US6283951B1 (en) * 1996-10-11 2001-09-04 Transvascular, Inc. Systems and methods for delivering drugs to selected locations within the body
WO1997027897A1 (en) 1996-02-02 1997-08-07 Transvascular, Inc. A device, system and method for interstitial transvascular intervention
ATE440559T1 (en) 1995-10-13 2009-09-15 Medtronic Vascular Inc DEVICE FOR INTERSTITIAL TRANSVASCULAR PROCEDURES
US6375615B1 (en) 1995-10-13 2002-04-23 Transvascular, Inc. Tissue penetrating catheters having integral imaging transducers and their methods of use
US5803083A (en) * 1995-11-09 1998-09-08 Cordis Corporation Guiding catheter with ultrasound imaging capability
US5749848A (en) * 1995-11-13 1998-05-12 Cardiovascular Imaging Systems, Inc. Catheter system having imaging, balloon angioplasty, and stent deployment capabilities, and method of use for guided stent deployment
US5769843A (en) * 1996-02-20 1998-06-23 Cormedica Percutaneous endomyocardial revascularization
DE69736549T2 (en) * 1996-02-29 2007-08-23 Acuson Corp., Mountain View SYSTEM, METHOD AND CONVERTER FOR ORIENTING MULTIPLE ULTRASOUND IMAGES
US5891133A (en) * 1996-03-29 1999-04-06 Eclipse Surgical Technologies, Inc. Apparatus for laser-assisted intra-coronary transmyocardial revascularization and other applications
US5699805A (en) * 1996-06-20 1997-12-23 Mayo Foundation For Medical Education And Research Longitudinal multiplane ultrasound transducer underfluid catheter system
US6296608B1 (en) * 1996-07-08 2001-10-02 Boston Scientific Corporation Diagnosing and performing interventional procedures on tissue in vivo
US5692506A (en) * 1996-08-01 1997-12-02 Linder; Gerald S. Transnasal conduit and method of use
US5800450A (en) * 1996-10-03 1998-09-01 Interventional Technologies Inc. Neovascularization catheter
US6117153A (en) 1996-10-03 2000-09-12 Interventional Technologies, Inc. Neovascularization catheter
US5893848A (en) * 1996-10-24 1999-04-13 Plc Medical Systems, Inc. Gauging system for monitoring channel depth in percutaneous endocardial revascularization
US5848969A (en) * 1996-10-28 1998-12-15 Ep Technologies, Inc. Systems and methods for visualizing interior tissue regions using expandable imaging structures
FR2755020B1 (en) * 1996-10-31 1999-05-28 Benhalima Bouziane DEVICE FOR PERFORMING TRANSOESOPHAGAL ECHOCARDIOGRAPHY AND CARDIOVERSION
US5810008A (en) * 1996-12-03 1998-09-22 Isg Technologies Inc. Apparatus and method for visualizing ultrasonic images
US5853368A (en) * 1996-12-23 1998-12-29 Hewlett-Packard Company Ultrasound imaging catheter having an independently-controllable treatment structure
US5938616A (en) 1997-01-31 1999-08-17 Acuson Corporation Steering mechanism and steering line for a catheter-mounted ultrasonic transducer
US5954654A (en) * 1997-01-31 1999-09-21 Acuson Corporation Steering mechanism and steering line for a catheter-mounted ultrasonic transducer
US6464645B1 (en) 1997-01-31 2002-10-15 Acuson Corporation Ultrasonic transducer assembly controller
US5846205A (en) * 1997-01-31 1998-12-08 Acuson Corporation Catheter-mounted, phased-array ultrasound transducer with improved imaging
US5730741A (en) * 1997-02-07 1998-03-24 Eclipse Surgical Technologies, Inc. Guided spiral catheter
US6045508A (en) * 1997-02-27 2000-04-04 Acuson Corporation Ultrasonic probe, system and method for two-dimensional imaging or three-dimensional reconstruction
US5876345A (en) * 1997-02-27 1999-03-02 Acuson Corporation Ultrasonic catheter, system and method for two dimensional imaging or three-dimensional reconstruction
US6086534A (en) * 1997-03-07 2000-07-11 Cardiogenesis Corporation Apparatus and method of myocardial revascularization using ultrasonic pulse-echo distance ranging
CA2201458C (en) 1997-04-01 2001-06-12 George A. Vilos Improved resectoscope
US6723063B1 (en) 1998-06-29 2004-04-20 Ekos Corporation Sheath for use with an ultrasound element
WO1998048711A1 (en) * 1997-05-01 1998-11-05 Ekos Corporation Ultrasound catheter
US6676626B1 (en) * 1998-05-01 2004-01-13 Ekos Corporation Ultrasound assembly with increased efficacy
US6582392B1 (en) * 1998-05-01 2003-06-24 Ekos Corporation Ultrasound assembly for use with a catheter
US6024740A (en) 1997-07-08 2000-02-15 The Regents Of The University Of California Circumferential ablation device assembly
US5971983A (en) 1997-05-09 1999-10-26 The Regents Of The University Of California Tissue ablation device and method of use
US6012457A (en) 1997-07-08 2000-01-11 The Regents Of The University Of California Device and method for forming a circumferential conduction block in a pulmonary vein
US6171247B1 (en) 1997-06-13 2001-01-09 Mayo Foundation For Medical Education And Research Underfluid catheter system and method having a rotatable multiplane transducer
US5846204A (en) * 1997-07-02 1998-12-08 Hewlett-Packard Company Rotatable ultrasound imaging catheter
US6117101A (en) 1997-07-08 2000-09-12 The Regents Of The University Of California Circumferential ablation device assembly
US6652515B1 (en) 1997-07-08 2003-11-25 Atrionix, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6869431B2 (en) 1997-07-08 2005-03-22 Atrionix, Inc. Medical device with sensor cooperating with expandable member
US6997925B2 (en) 1997-07-08 2006-02-14 Atrionx, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6500174B1 (en) 1997-07-08 2002-12-31 Atrionix, Inc. Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member
US6966908B2 (en) 1997-07-08 2005-11-22 Atrionix, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6090118A (en) 1998-07-23 2000-07-18 Mcguckin, Jr.; James F. Rotational thrombectomy apparatus and method with standing wave
US6027451A (en) 1997-09-26 2000-02-22 Ep Technologies, Inc. Method and apparatus for fixing the anatomical orientation of a displayed ultrasound generated image
US6083166A (en) * 1997-12-02 2000-07-04 Situs Corporation Method and apparatus for determining a measure of tissue manipulation
US6241667B1 (en) * 1998-01-15 2001-06-05 Lumend, Inc. Catheter apparatus for guided transvascular treatment of arterial occlusions
WO1999035980A1 (en) * 1998-01-15 1999-07-22 Lumend, Inc. Catheter apparatus for guided transvascular treatment of arterial occlusions
AU1927399A (en) 1998-01-16 1999-08-02 Lumend, Inc. Catheter apparatus for treating arterial occlusions
US5865748A (en) * 1998-01-16 1999-02-02 Guidant Corporation Guided directional coronary atherectomy distal linear encoder
JP4463983B2 (en) 1998-03-05 2010-05-19 ギル エム. ヴァルディ, Optoacoustic imaging device
US6159196A (en) * 1998-03-09 2000-12-12 Ruiz; Carlos Methods and apparatus for transvascular muscular revascularization and drug delivery
US6173199B1 (en) * 1998-05-05 2001-01-09 Syncro Medical Innovations, Inc. Method and apparatus for intubation of a patient
US7806829B2 (en) * 1998-06-30 2010-10-05 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for navigating an ultrasound catheter to image a beating heart
US7670297B1 (en) 1998-06-30 2010-03-02 St. Jude Medical, Atrial Fibrillation Division, Inc. Chamber mapping system
US7263397B2 (en) 1998-06-30 2007-08-28 St. Jude Medical, Atrial Fibrillation Division, Inc. Method and apparatus for catheter navigation and location and mapping in the heart
US7187973B2 (en) * 1998-06-30 2007-03-06 Endocardial Solutions, Inc. Congestive heart failure pacing optimization method and device
US20030078227A1 (en) * 1998-07-02 2003-04-24 Greenleaf James F. Site-directed transfection with ultrasound and cavitation nuclei
US6059731A (en) * 1998-08-19 2000-05-09 Mayo Foundation For Medical Education And Research Simultaneous side-and-end viewing underfluid catheter
DE29814889U1 (en) * 1998-08-19 1999-12-30 Burgard Gunther Resection instrument
US6022362A (en) 1998-09-03 2000-02-08 Rubicor Medical, Inc. Excisional biopsy devices and methods
US6440147B1 (en) * 1998-09-03 2002-08-27 Rubicor Medical, Inc. Excisional biopsy devices and methods
AU2002336281B2 (en) * 1998-09-03 2004-12-02 Rubicor Medical, Inc. Excisional Biopsy Devices and Methods
US7329253B2 (en) * 2003-12-09 2008-02-12 Rubicor Medical, Inc. Suction sleeve and interventional devices having such a suction sleeve
US6936014B2 (en) * 2002-10-16 2005-08-30 Rubicor Medical, Inc. Devices and methods for performing procedures on a breast
US7517348B2 (en) * 1998-09-03 2009-04-14 Rubicor Medical, Inc. Devices and methods for performing procedures on a breast
US6312402B1 (en) * 1998-09-24 2001-11-06 Ekos Corporation Ultrasound catheter for improving blood flow to the heart
US6217518B1 (en) 1998-10-01 2001-04-17 Situs Corporation Medical instrument sheath comprising a flexible ultrasound transducer
US6645145B1 (en) 1998-11-19 2003-11-11 Siemens Medical Solutions Usa, Inc. Diagnostic medical ultrasound systems and transducers utilizing micro-mechanical components
US6174286B1 (en) 1998-11-25 2001-01-16 Acuson Corporation Medical diagnostic ultrasound method and system for element switching
US6607502B1 (en) 1998-11-25 2003-08-19 Atrionix, Inc. Apparatus and method incorporating an ultrasound transducer onto a delivery member
US6224556B1 (en) 1998-11-25 2001-05-01 Acuson Corporation Diagnostic medical ultrasound system and method for using a sparse array
US6645147B1 (en) 1998-11-25 2003-11-11 Acuson Corporation Diagnostic medical ultrasound image and system for contrast agent imaging
US7524289B2 (en) * 1999-01-25 2009-04-28 Lenker Jay A Resolution optical and ultrasound devices for imaging and treatment of body lumens
US6556695B1 (en) * 1999-02-05 2003-04-29 Mayo Foundation For Medical Education And Research Method for producing high resolution real-time images, of structure and function during medical procedures
US8506519B2 (en) 1999-02-16 2013-08-13 Flowcardia, Inc. Pre-shaped therapeutic catheter
US6855123B2 (en) 2002-08-02 2005-02-15 Flow Cardia, Inc. Therapeutic ultrasound system
US6398736B1 (en) 1999-03-31 2002-06-04 Mayo Foundation For Medical Education And Research Parametric imaging ultrasound catheter
US6306097B1 (en) 1999-06-17 2001-10-23 Acuson Corporation Ultrasound imaging catheter guiding assembly with catheter working port
US6299622B1 (en) * 1999-08-19 2001-10-09 Fox Hollow Technologies, Inc. Atherectomy catheter with aligned imager
US8414543B2 (en) 1999-10-22 2013-04-09 Rex Medical, L.P. Rotational thrombectomy wire with blocking device
AU2614901A (en) 1999-10-22 2001-04-30 Boston Scientific Corporation Double balloon thrombectomy catheter
US6969384B2 (en) * 2000-01-03 2005-11-29 The Johns Hopkins University Surgical devices and methods of use thereof for enhanced tactile perception
US6589164B1 (en) * 2000-02-15 2003-07-08 Transvascular, Inc. Sterility barriers for insertion of non-sterile apparatus into catheters or other medical devices
AU2001239977A1 (en) 2000-03-02 2001-09-12 Mayo Foundation For Medical Education And Research Apparatus and method of holding and manipulating small ultrasound transducers
US7037270B2 (en) * 2000-03-02 2006-05-02 Mayo Foundation For Medical Education And Research Small ultrasound transducers
US6577904B1 (en) 2000-03-30 2003-06-10 Cardiac Pacemakers, Inc. Ultrasound echogenic cardiac lead
US7083628B2 (en) 2002-09-03 2006-08-01 Edwards Lifesciences Corporation Single catheter mitral valve repair device and method for use
AU2001263213B2 (en) 2000-05-16 2005-05-19 Atrionix, Inc. Apparatus and method incorporating an ultrasound transducer onto a delivery member
DE60109444T2 (en) 2000-06-13 2006-04-13 Atrionix, Inc., Irwindale SURGICAL ABLATION PROBE FOR FORMING A RINGED LESION
US6964647B1 (en) 2000-10-06 2005-11-15 Ellaz Babaev Nozzle for ultrasound wound treatment
US6475148B1 (en) 2000-10-25 2002-11-05 Acuson Corporation Medical diagnostic ultrasound-aided drug delivery system and method
US6601581B1 (en) 2000-11-01 2003-08-05 Advanced Medical Applications, Inc. Method and device for ultrasound drug delivery
US20020072739A1 (en) 2000-12-07 2002-06-13 Roberta Lee Methods and devices for radiofrequency electrosurgery
US6533803B2 (en) 2000-12-22 2003-03-18 Advanced Medical Applications, Inc. Wound treatment method and device with combination of ultrasound and laser energy
US6761729B2 (en) 2000-12-22 2004-07-13 Advanced Medicalapplications, Inc. Wound treatment method and device with combination of ultrasound and laser energy
US7914470B2 (en) 2001-01-12 2011-03-29 Celleration, Inc. Ultrasonic method and device for wound treatment
US8235919B2 (en) 2001-01-12 2012-08-07 Celleration, Inc. Ultrasonic method and device for wound treatment
US6960173B2 (en) * 2001-01-30 2005-11-01 Eilaz Babaev Ultrasound wound treatment method and device using standing waves
US6623444B2 (en) 2001-03-21 2003-09-23 Advanced Medical Applications, Inc. Ultrasonic catheter drug delivery method and device
US6478754B1 (en) 2001-04-23 2002-11-12 Advanced Medical Applications, Inc. Ultrasonic method and device for wound treatment
US8123789B2 (en) * 2002-04-29 2012-02-28 Rohit Khanna Central nervous system cooling catheter
US7211044B2 (en) 2001-05-29 2007-05-01 Ethicon Endo-Surgery, Inc. Method for mapping temperature rise using pulse-echo ultrasound
US7846096B2 (en) 2001-05-29 2010-12-07 Ethicon Endo-Surgery, Inc. Method for monitoring of medical treatment using pulse-echo ultrasound
US7473224B2 (en) 2001-05-29 2009-01-06 Ethicon Endo-Surgery, Inc. Deployable ultrasound medical transducers
US6558400B2 (en) * 2001-05-30 2003-05-06 Satiety, Inc. Obesity treatment tools and methods
US6716178B1 (en) 2001-05-31 2004-04-06 Advanced Cardiovascular Systems, Inc. Apparatus and method for performing thermal and laser doppler velocimetry measurements
US6697667B1 (en) 2001-05-31 2004-02-24 Advanced Cardiovascular Systems, Inc. Apparatus and method for locating coronary sinus
US7532920B1 (en) 2001-05-31 2009-05-12 Advanced Cardiovascular Systems, Inc. Guidewire with optical fiber
US7329223B1 (en) * 2001-05-31 2008-02-12 Abbott Cardiovascular Systems Inc. Catheter with optical fiber sensor
US6572628B2 (en) * 2001-06-28 2003-06-03 Cordis Neurovascular, Inc. Method and apparatus for placing a medical agent into a vessel of the body
US20040019318A1 (en) * 2001-11-07 2004-01-29 Wilson Richard R. Ultrasound assembly for use with a catheter
US8175680B2 (en) * 2001-11-09 2012-05-08 Boston Scientific Scimed, Inc. Systems and methods for guiding catheters using registered images
WO2003047439A2 (en) 2001-12-03 2003-06-12 Ekos Corporation Catheter with multiple ultrasound radiating members
JP4279676B2 (en) 2001-12-03 2009-06-17 イコス コーポレイション Small vessel ultrasound catheter
CA2468975A1 (en) * 2001-12-14 2003-06-26 Ekos Corporation Blood flow reestablishment determination
WO2003057275A2 (en) * 2001-12-28 2003-07-17 Ekos Corporation Multi-resonant ultrasonic catheter
AU2003209287A1 (en) 2002-01-15 2003-07-30 The Regents Of The University Of California System and method providing directional ultrasound therapy to skeletal joints
US20050124898A1 (en) * 2002-01-16 2005-06-09 Ep Medsystems, Inc. Method and apparatus for isolating a catheter interface
US20080146943A1 (en) * 2006-12-14 2008-06-19 Ep Medsystems, Inc. Integrated Beam Former And Isolation For An Ultrasound Probe
US7648462B2 (en) 2002-01-16 2010-01-19 St. Jude Medical, Atrial Fibrillation Division, Inc. Safety systems and methods for ensuring safe use of intra-cardiac ultrasound catheters
WO2003061756A2 (en) * 2002-01-23 2003-07-31 The Regents Of The University Of California Implantable thermal treatment method and apparatus
US20040068189A1 (en) * 2002-02-28 2004-04-08 Wilson Richard R. Ultrasound catheter with embedded conductors
US8226629B1 (en) 2002-04-01 2012-07-24 Ekos Corporation Ultrasonic catheter power control
US6704590B2 (en) * 2002-04-05 2004-03-09 Cardiac Pacemakers, Inc. Doppler guiding catheter using sensed blood turbulence levels
US6932804B2 (en) 2003-01-21 2005-08-23 The Regents Of The University Of California System and method for forming a non-ablative cardiac conduction block
EP1503819A4 (en) * 2002-05-08 2007-07-25 Univ California System and method for forming a non-ablative cardiac conduction block
US20040106896A1 (en) * 2002-11-29 2004-06-03 The Regents Of The University Of California System and method for forming a non-ablative cardiac conduction block
US20040006355A1 (en) * 2002-07-03 2004-01-08 Rubicor Medical, Inc. Methods and devices for cutting and collecting soft tissue
US7044956B2 (en) * 2002-07-03 2006-05-16 Rubicor Medical, Inc. Methods and devices for cutting and collecting soft tissue
US20070083118A1 (en) * 2002-07-22 2007-04-12 Ep Medsystems, Inc. Method and System For Estimating Cardiac Ejection Volume Using Ultrasound Spectral Doppler Image Data
US20070167809A1 (en) * 2002-07-22 2007-07-19 Ep Medsystems, Inc. Method and System For Estimating Cardiac Ejection Volume And Placing Pacemaker Electrodes Using Speckle Tracking
US7314446B2 (en) * 2002-07-22 2008-01-01 Ep Medsystems, Inc. Method and apparatus for time gating of medical images
US20050245822A1 (en) * 2002-07-22 2005-11-03 Ep Medsystems, Inc. Method and apparatus for imaging distant anatomical structures in intra-cardiac ultrasound imaging
US9955994B2 (en) 2002-08-02 2018-05-01 Flowcardia, Inc. Ultrasound catheter having protective feature against breakage
US8133236B2 (en) 2006-11-07 2012-03-13 Flowcardia, Inc. Ultrasound catheter having protective feature against breakage
US7604608B2 (en) 2003-01-14 2009-10-20 Flowcardia, Inc. Ultrasound catheter and methods for making and using same
US7335180B2 (en) 2003-11-24 2008-02-26 Flowcardia, Inc. Steerable ultrasound catheter
US6942677B2 (en) 2003-02-26 2005-09-13 Flowcardia, Inc. Ultrasound catheter apparatus
US7220233B2 (en) * 2003-04-08 2007-05-22 Flowcardia, Inc. Ultrasound catheter devices and methods
US7137963B2 (en) 2002-08-26 2006-11-21 Flowcardia, Inc. Ultrasound catheter for disrupting blood vessel obstructions
US7258690B2 (en) 2003-03-28 2007-08-21 Relievant Medsystems, Inc. Windowed thermal ablation probe
US6907884B2 (en) 2002-09-30 2005-06-21 Depay Acromed, Inc. Method of straddling an intraosseous nerve
US8361067B2 (en) 2002-09-30 2013-01-29 Relievant Medsystems, Inc. Methods of therapeutically heating a vertebral body to treat back pain
US7245789B2 (en) * 2002-10-07 2007-07-17 Vascular Imaging Corporation Systems and methods for minimally-invasive optical-acoustic imaging
US6921371B2 (en) 2002-10-14 2005-07-26 Ekos Corporation Ultrasound radiating members for catheter
US6887263B2 (en) * 2002-10-18 2005-05-03 Radiant Medical, Inc. Valved connector assembly and sterility barriers for heat exchange catheters and other closed loop catheters
US7029451B2 (en) * 2002-11-06 2006-04-18 Rubicor Medical, Inc. Excisional devices having selective cutting and atraumatic configurations and methods of using same
US7317950B2 (en) * 2002-11-16 2008-01-08 The Regents Of The University Of California Cardiac stimulation system with delivery of conductive agent
US7267650B2 (en) * 2002-12-16 2007-09-11 Cardiac Pacemakers, Inc. Ultrasound directed guiding catheter system and method
WO2004060448A2 (en) * 2003-01-03 2004-07-22 Ekos Corporation Ultrasonic catheter with axial energy field
EP1619995A2 (en) 2003-04-22 2006-02-01 Ekos Corporation Ultrasound enhanced central venous catheter
US7122011B2 (en) * 2003-06-18 2006-10-17 Rubicor Medical, Inc. Methods and devices for cutting and collecting soft tissue
US7662099B2 (en) * 2003-06-30 2010-02-16 Ethicon, Inc. Method and instrumentation to sense thermal lesion formation by ultrasound imaging
US8308682B2 (en) 2003-07-18 2012-11-13 Broncus Medical Inc. Devices for maintaining patency of surgically created channels in tissue
US7998073B2 (en) * 2003-08-04 2011-08-16 Imacor Inc. Ultrasound imaging with reduced noise
US7758510B2 (en) 2003-09-19 2010-07-20 Flowcardia, Inc. Connector for securing ultrasound catheter to transducer
WO2005048813A2 (en) * 2003-11-12 2005-06-02 The Board Of Trustees Of The Leland Stanford Junior University Devices and methods for three-dimensional body images
CN100566664C (en) * 2003-11-26 2009-12-09 普瑞斯玛医药技术有限责任公司 Use the ultrasound wave through esophagus of narrow probe
US20080051660A1 (en) * 2004-01-16 2008-02-28 The University Of Houston System Methods and apparatuses for medical imaging
WO2005072409A2 (en) 2004-01-29 2005-08-11 Ekos Corporation Method and apparatus for detecting vascular conditions with a catheter
US20050203410A1 (en) * 2004-02-27 2005-09-15 Ep Medsystems, Inc. Methods and systems for ultrasound imaging of the heart from the pericardium
US20050216044A1 (en) * 2004-03-25 2005-09-29 Hong Mun K Total occlusion recanalization facilitating device
US7507205B2 (en) * 2004-04-07 2009-03-24 St. Jude Medical, Atrial Fibrillation Division, Inc. Steerable ultrasound catheter
US7654958B2 (en) * 2004-04-20 2010-02-02 St. Jude Medical, Atrial Fibrillation Division, Inc. Method and apparatus for ultrasound imaging with autofrequency selection
US7883468B2 (en) * 2004-05-18 2011-02-08 Ethicon Endo-Surgery, Inc. Medical system having an ultrasound source and an acoustic coupling medium
US7951095B2 (en) * 2004-05-20 2011-05-31 Ethicon Endo-Surgery, Inc. Ultrasound medical system
US7473250B2 (en) 2004-05-21 2009-01-06 Ethicon Endo-Surgery, Inc. Ultrasound medical system and method
US7806839B2 (en) * 2004-06-14 2010-10-05 Ethicon Endo-Surgery, Inc. System and method for ultrasound therapy using grating lobes
US8409167B2 (en) 2004-07-19 2013-04-02 Broncus Medical Inc Devices for delivering substances through an extra-anatomic opening created in an airway
US7540852B2 (en) 2004-08-26 2009-06-02 Flowcardia, Inc. Ultrasound catheter devices and methods
US20060184070A1 (en) * 2004-11-12 2006-08-17 Hansmann Douglas R External ultrasonic therapy
US20060111704A1 (en) * 2004-11-22 2006-05-25 Rox Medical, Inc. Devices, systems, and methods for energy assisted arterio-venous fistula creation
US7713210B2 (en) * 2004-11-23 2010-05-11 St. Jude Medical, Atrial Fibrillation Division, Inc. Method and apparatus for localizing an ultrasound catheter
KR100714682B1 (en) * 2004-12-02 2007-05-04 삼성전자주식회사 File system path processing device and method thereof
US20060173387A1 (en) * 2004-12-10 2006-08-03 Douglas Hansmann Externally enhanced ultrasonic therapy
DE602005007316D1 (en) * 2005-01-18 2008-07-17 Esaote Spa Method for ultrasound imaging and probe for 3D gynecological examination
US8221343B2 (en) 2005-01-20 2012-07-17 Flowcardia, Inc. Vibrational catheter devices and methods for making same
US8007440B2 (en) * 2005-02-08 2011-08-30 Volcano Corporation Apparatus and methods for low-cost intravascular ultrasound imaging and for crossing severe vascular occlusions
JP2008531208A (en) * 2005-02-28 2008-08-14 ウィルソン−クック・メディカル・インコーポレーテッド GI medical device echo marker
US8070685B2 (en) * 2005-04-15 2011-12-06 Imacor Inc. Connectorized probe for transesophageal echocardiography
US20070016069A1 (en) 2005-05-06 2007-01-18 Sorin Grunwald Ultrasound sensor
US20090118612A1 (en) 2005-05-06 2009-05-07 Sorin Grunwald Apparatus and Method for Vascular Access
US8932208B2 (en) 2005-05-26 2015-01-13 Maquet Cardiovascular Llc Apparatus and methods for performing minimally-invasive surgical procedures
DE102005028882A1 (en) * 2005-06-22 2007-01-04 Siemens Ag A solution and method for assisting imaging on a patient
US7713218B2 (en) 2005-06-23 2010-05-11 Celleration, Inc. Removable applicator nozzle for ultrasound wound therapy device
US7785277B2 (en) 2005-06-23 2010-08-31 Celleration, Inc. Removable applicator nozzle for ultrasound wound therapy device
US7625343B2 (en) 2005-07-01 2009-12-01 Scimed Life Systems, Inc. Concave phased array imaging catheter
US8784336B2 (en) 2005-08-24 2014-07-22 C. R. Bard, Inc. Stylet apparatuses and methods of manufacture
US20070232941A1 (en) * 2005-10-27 2007-10-04 Stan Rabinovich System, apparatus, and method for imaging and treating tissue
US8047996B2 (en) 2005-10-31 2011-11-01 Volcano Corporation System and method for reducing angular geometric distortion in an imaging device
US7819802B2 (en) * 2005-11-22 2010-10-26 General Electric Company Catheter tip
US7599588B2 (en) * 2005-11-22 2009-10-06 Vascular Imaging Corporation Optical imaging probe connector
US7867169B2 (en) * 2005-12-02 2011-01-11 Abbott Cardiovascular Systems Inc. Echogenic needle catheter configured to produce an improved ultrasound image
US20070167793A1 (en) * 2005-12-14 2007-07-19 Ep Medsystems, Inc. Method and system for enhancing spectral doppler presentation
US8070684B2 (en) * 2005-12-14 2011-12-06 St. Jude Medical, Atrial Fibrillation Division, Inc. Method and system for evaluating valvular function
US20070208256A1 (en) * 2006-03-03 2007-09-06 Medtronic Vascular, Inc. Multiple Branch Tubular Prosthesis and Methods
US9539025B2 (en) * 2006-03-24 2017-01-10 B-K Medical Aps Biopsy system
WO2007110077A2 (en) * 2006-03-24 2007-10-04 B-K Medical Aps Ultrasound probe
US7785286B2 (en) 2006-03-30 2010-08-31 Volcano Corporation Method and system for imaging, diagnosing, and/or treating an area of interest in a patient's body
US20070232949A1 (en) * 2006-03-31 2007-10-04 Ep Medsystems, Inc. Method For Simultaneous Bi-Atrial Mapping Of Atrial Fibrillation
WO2007115307A2 (en) * 2006-04-04 2007-10-11 Volcano Corporation Ultrasound catheter and hand-held device for manipulating a transducer on the catheter's distal end
US9282984B2 (en) 2006-04-05 2016-03-15 Flowcardia, Inc. Therapeutic ultrasound system
US20070239010A1 (en) * 2006-04-11 2007-10-11 Medtronic Vascular, Inc. Catheters with Laterally Deployable Elements and Linear Ultrasound Arrays
US7794393B2 (en) * 2006-04-13 2010-09-14 Larsen Dane M Resectoscopic device and method
EP2015846A2 (en) 2006-04-24 2009-01-21 Ekos Corporation Ultrasound therapy system
US7794402B2 (en) * 2006-05-15 2010-09-14 Advanced Cardiovascular Systems, Inc. Echogenic needle catheter configured to produce an improved ultrasound image
US7612773B2 (en) * 2006-05-22 2009-11-03 Magnin Paul A Apparatus and method for rendering for display forward-looking image data
US7431704B2 (en) 2006-06-07 2008-10-07 Bacoustics, Llc Apparatus and method for the treatment of tissue with ultrasound energy by direct contact
US8562547B2 (en) 2006-06-07 2013-10-22 Eliaz Babaev Method for debriding wounds
US20070299479A1 (en) * 2006-06-27 2007-12-27 Ep Medsystems, Inc. Method for Reversing Ventricular Dyssynchrony
US20080009733A1 (en) * 2006-06-27 2008-01-10 Ep Medsystems, Inc. Method for Evaluating Regional Ventricular Function and Incoordinate Ventricular Contraction
WO2008021343A2 (en) * 2006-08-14 2008-02-21 Novelis Inc. Imaging device, imaging system, and methods of imaging
US7794407B2 (en) 2006-10-23 2010-09-14 Bard Access Systems, Inc. Method of locating the tip of a central venous catheter
US8388546B2 (en) 2006-10-23 2013-03-05 Bard Access Systems, Inc. Method of locating the tip of a central venous catheter
DE102006050885B4 (en) * 2006-10-27 2016-11-03 Siemens Healthcare Gmbh Device for generating tissue section images
US8192363B2 (en) 2006-10-27 2012-06-05 Ekos Corporation Catheter with multiple ultrasound radiating members
DE102006050886B4 (en) * 2006-10-27 2016-12-22 Siemens Healthcare Gmbh Medical instrument and device for generating tissue sections
US8246643B2 (en) 2006-11-07 2012-08-21 Flowcardia, Inc. Ultrasound catheter having improved distal end
WO2008065570A1 (en) * 2006-11-30 2008-06-05 Koninklijke Philips Electronics, N.V. Catheter with ultrasound transducer and variable focus lens used in aneurysm assessment
EP1930045A1 (en) * 2006-12-08 2008-06-11 BIOTRONIK CRM Patent AG Implantable medical system with acoustic sensor to measure mitral blood flow
US20080146942A1 (en) * 2006-12-13 2008-06-19 Ep Medsystems, Inc. Catheter Position Tracking Methods Using Fluoroscopy and Rotational Sensors
US8187190B2 (en) * 2006-12-14 2012-05-29 St. Jude Medical, Atrial Fibrillation Division, Inc. Method and system for configuration of a pacemaker and for placement of pacemaker electrodes
US20080146940A1 (en) * 2006-12-14 2008-06-19 Ep Medsystems, Inc. External and Internal Ultrasound Imaging System
US8491521B2 (en) 2007-01-04 2013-07-23 Celleration, Inc. Removable multi-channel applicator nozzle
PL2111261T3 (en) 2007-01-08 2015-08-31 Ekos Corp Power parameters for ultrasonic catheter
US10182833B2 (en) 2007-01-08 2019-01-22 Ekos Corporation Power parameters for ultrasonic catheter
EP2117437A1 (en) * 2007-01-11 2009-11-18 Koninklijke Philips Electronics N.V. Catheter for three-dimensional intracardiac echocardiography and system including the same
WO2008109760A2 (en) * 2007-03-06 2008-09-12 Broncus Technologies, Inc. Blood vessel sensing catheter having working lumen for medical appliances
US8721553B2 (en) * 2007-05-15 2014-05-13 General Electric Company Fluid-fillable ultrasound imaging catheter tips
US8317711B2 (en) 2007-06-16 2012-11-27 St. Jude Medical, Atrial Fibrillation Division, Inc. Oscillating phased-array ultrasound imaging catheter system
EP2494932B1 (en) 2007-06-22 2020-05-20 Ekos Corporation Apparatus for treatment of intracranial hemorrhages
JP5660890B2 (en) 2007-06-26 2015-01-28 バソノバ・インコーポレイテッドVasonova, Inc. Vascular access and guidance system
US8852112B2 (en) 2007-06-28 2014-10-07 W. L. Gore & Associates, Inc. Catheter with deflectable imaging device and bendable electrical conductor
US8285362B2 (en) * 2007-06-28 2012-10-09 W. L. Gore & Associates, Inc. Catheter with deflectable imaging device
US8864675B2 (en) 2007-06-28 2014-10-21 W. L. Gore & Associates, Inc. Catheter
US8057394B2 (en) 2007-06-30 2011-11-15 St. Jude Medical, Atrial Fibrillation Division, Inc. Ultrasound image processing to render three-dimensional images from two-dimensional images
US8702609B2 (en) * 2007-07-27 2014-04-22 Meridian Cardiovascular Systems, Inc. Image-guided intravascular therapy catheters
WO2009029869A2 (en) * 2007-08-30 2009-03-05 Syncro Medical Innovations, Inc. Guided catheter with removable magnetic guide
JP2010540160A (en) 2007-10-05 2010-12-24 マッケ カーディオバスキュラー,エルエルシー Apparatus and method for minimally invasive surgical procedures
US9649048B2 (en) 2007-11-26 2017-05-16 C. R. Bard, Inc. Systems and methods for breaching a sterile field for intravascular placement of a catheter
US10751509B2 (en) 2007-11-26 2020-08-25 C. R. Bard, Inc. Iconic representations for guidance of an indwelling medical device
US8849382B2 (en) 2007-11-26 2014-09-30 C. R. Bard, Inc. Apparatus and display methods relating to intravascular placement of a catheter
CN103750858B (en) 2007-11-26 2017-04-12 C·R·巴德股份有限公司 Integrated system for intravascular placement of a catheter
US10524691B2 (en) 2007-11-26 2020-01-07 C. R. Bard, Inc. Needle assembly including an aligned magnetic element
US10449330B2 (en) 2007-11-26 2019-10-22 C. R. Bard, Inc. Magnetic element-equipped needle assemblies
US8781555B2 (en) 2007-11-26 2014-07-15 C. R. Bard, Inc. System for placement of a catheter including a signal-generating stylet
US9521961B2 (en) 2007-11-26 2016-12-20 C. R. Bard, Inc. Systems and methods for guiding a medical instrument
US20110004235A1 (en) * 2008-02-08 2011-01-06 Sundt Iii Thoralf M Transapical heart port
US8478382B2 (en) 2008-02-11 2013-07-02 C. R. Bard, Inc. Systems and methods for positioning a catheter
US8792964B2 (en) * 2008-03-12 2014-07-29 Siemens Aktiengesellschaft Method and apparatus for conducting an interventional procedure involving heart valves using a robot-based X-ray device
US8052607B2 (en) * 2008-04-22 2011-11-08 St. Jude Medical, Atrial Fibrillation Division, Inc. Ultrasound imaging catheter with pivoting head
CA2725357C (en) * 2008-05-30 2014-02-18 Gore Enterprise Holdings, Inc. Real time ultrasound catheter probe
US8197413B2 (en) * 2008-06-06 2012-06-12 Boston Scientific Scimed, Inc. Transducers, devices and systems containing the transducers, and methods of manufacture
WO2010022370A1 (en) 2008-08-22 2010-02-25 C.R. Bard, Inc. Catheter assembly including ecg sensor and magnetic assemblies
WO2010028080A1 (en) * 2008-09-02 2010-03-11 Syncro Medical Innovations, Inc. Magnetic device for guiding catheter and method of use therefor
US10028753B2 (en) 2008-09-26 2018-07-24 Relievant Medsystems, Inc. Spine treatment kits
CA2737374C (en) 2008-09-26 2017-03-28 Relievant Medsystems, Inc. Systems and methods for navigating an instrument through bone
EP2356412B1 (en) 2008-10-02 2012-08-15 Vascular Imaging Corporation Optical ultrasound receiver
US8437833B2 (en) 2008-10-07 2013-05-07 Bard Access Systems, Inc. Percutaneous magnetic gastrostomy
US8583218B2 (en) 2008-10-31 2013-11-12 Vascular Imaging Corporation Optical imaging probe connector
US8361039B2 (en) * 2009-01-26 2013-01-29 Schatz Richard A Myocardial injector with spring loaded protective array
US9366938B1 (en) 2009-02-17 2016-06-14 Vescent Photonics, Inc. Electro-optic beam deflector device
EP2243561B1 (en) * 2009-04-23 2018-11-28 Esaote S.p.A. Array of electroacoustic transducers and electronic probe for three-dimensional images comprising said transducer array
US8206306B2 (en) * 2009-05-07 2012-06-26 Hitachi Aloka Medical, Ltd. Ultrasound systems and methods for orthopedic applications
CN102421374B (en) * 2009-05-07 2014-12-17 日立阿洛卡医疗株式会社 Ultrasound systems for orthopedic applications
US9532724B2 (en) 2009-06-12 2017-01-03 Bard Access Systems, Inc. Apparatus and method for catheter navigation using endovascular energy mapping
EP2440122B1 (en) 2009-06-12 2019-08-14 Bard Access Systems, Inc. Apparatus, computer-based data processing algorithm and computer storage medium for positioning an endovascular device in or near the heart
US8226566B2 (en) 2009-06-12 2012-07-24 Flowcardia, Inc. Device and method for vascular re-entry
ES2503140T3 (en) 2009-07-03 2014-10-06 Ekos Corporation Power parameters for ultrasonic catheter
EP2464407A4 (en) 2009-08-10 2014-04-02 Bard Access Systems Inc Devices and methods for endovascular electrography
EP2517622A3 (en) 2009-09-29 2013-04-24 C. R. Bard, Inc. Stylets for use with apparatus for intravascular placement of a catheter
US10639008B2 (en) 2009-10-08 2020-05-05 C. R. Bard, Inc. Support and cover structures for an ultrasound probe head
WO2011044421A1 (en) 2009-10-08 2011-04-14 C. R. Bard, Inc. Spacers for use with an ultrasound probe
US20110160591A1 (en) * 2009-12-30 2011-06-30 General Electric Company Fetal heart rate monitor with wide search area
JP2013518676A (en) 2010-02-02 2013-05-23 シー・アール・バード・インコーポレーテッド Apparatus and method for locating catheter navigation and tip
US10117564B2 (en) 2010-04-16 2018-11-06 Hitachi Healthcare Americas Corporation Ultrasound and detachable instrument for procedures
EP2912999B1 (en) 2010-05-28 2022-06-29 C. R. Bard, Inc. Apparatus for use with needle insertion guidance system
ES2778041T3 (en) 2010-05-28 2020-08-07 Bard Inc C R Apparatus for use with needle insertion guidance system
MX338127B (en) 2010-08-20 2016-04-04 Bard Inc C R Reconfirmation of ecg-assisted catheter tip placement.
WO2012027722A2 (en) 2010-08-27 2012-03-01 Ekos Corporation Method and apparatus for treatment of intracranial hemorrhages
CN103348069B (en) 2010-10-15 2018-01-16 赛普里安·埃米卡·尤佐 Method and substrate for materials application
EP2632360A4 (en) 2010-10-29 2014-05-21 Bard Inc C R Bioimpedance-assisted placement of a medical device
US11458290B2 (en) 2011-05-11 2022-10-04 Ekos Corporation Ultrasound system
WO2012158530A1 (en) 2011-05-13 2012-11-22 Broncus Technologies, Inc. Methods and devices for ablation of tissue
US8709034B2 (en) 2011-05-13 2014-04-29 Broncus Medical Inc. Methods and devices for diagnosing, monitoring, or treating medical conditions through an opening through an airway wall
CN105662402B (en) 2011-07-06 2019-06-18 C·R·巴德股份有限公司 Needle length for being inserted into guidance system is determining and calibrates
USD699359S1 (en) 2011-08-09 2014-02-11 C. R. Bard, Inc. Ultrasound probe head
USD724745S1 (en) 2011-08-09 2015-03-17 C. R. Bard, Inc. Cap for an ultrasound probe
US9211107B2 (en) 2011-11-07 2015-12-15 C. R. Bard, Inc. Ruggedized ultrasound hydrogel insert
WO2013078235A1 (en) 2011-11-23 2013-05-30 Broncus Medical Inc Methods and devices for diagnosing, monitoring, or treating medical conditions through an opening through an airway wall
AU2012362524B2 (en) 2011-12-30 2018-12-13 Relievant Medsystems, Inc. Systems and methods for treating back pain
WO2013109269A1 (en) 2012-01-18 2013-07-25 Bard Peripheral Vascular, Inc. Vascular re-entry device
WO2013177577A2 (en) 2012-05-25 2013-11-28 Eberle Michael J Optical fiber pressure sensor
US10820885B2 (en) 2012-06-15 2020-11-03 C. R. Bard, Inc. Apparatus and methods for detection of a removable cap on an ultrasound probe
US9955946B2 (en) 2014-03-12 2018-05-01 Cibiem, Inc. Carotid body ablation with a transvenous ultrasound imaging and ablation catheter
US9283033B2 (en) 2012-06-30 2016-03-15 Cibiem, Inc. Carotid body ablation via directed energy
US10238895B2 (en) 2012-08-02 2019-03-26 Flowcardia, Inc. Ultrasound catheter system
US10070846B2 (en) 2012-09-01 2018-09-11 Koninklijke Philips N.V. Ultrasonic volume flow measurement for ablation therapy
JP6099748B2 (en) * 2012-09-01 2017-03-22 コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. Ultrasonic volume flow measurement for ablation planning
US10588691B2 (en) 2012-09-12 2020-03-17 Relievant Medsystems, Inc. Radiofrequency ablation of tissue within a vertebral body
WO2014055729A1 (en) 2012-10-04 2014-04-10 Vascular Imaging Corporatoin Polarization scrambling for intra-body fiber optic sensor
EP2914186B1 (en) 2012-11-05 2019-03-13 Relievant Medsystems, Inc. Systems for creating curved paths through bone and modulating nerves within the bone
WO2014099244A1 (en) * 2012-12-19 2014-06-26 Muffin Incorporated Apparatus and method for the retrieval of an intravascular filter
US10175421B2 (en) 2013-03-14 2019-01-08 Vascular Imaging Corporation Optical fiber ribbon imaging guidewire and methods
JP6479753B2 (en) 2013-03-14 2019-03-06 エコス コーポレーション Method and apparatus for delivering a drug to a target location
WO2014172396A2 (en) 2013-04-16 2014-10-23 Transmed7, Llc Methods, devices and therapeutic platform for automated, selectable, soft tissue resection
CN103417249B (en) * 2013-07-15 2015-06-03 南京航空航天大学 Ultrasonic detection and treatment integrating endoscope
US9724151B2 (en) 2013-08-08 2017-08-08 Relievant Medsystems, Inc. Modulating nerves within bone using bone fasteners
WO2015051003A1 (en) 2013-10-04 2015-04-09 Vascular Imaging Corporation Imaging techniques using an imaging guidewire
US11890025B2 (en) 2013-11-18 2024-02-06 Philips Image Guided Therapy Corporation Guided thrombus dispersal catheter
WO2015077515A1 (en) 2013-11-20 2015-05-28 Naumann Michael T Intravascular ultrasound needle guide
US10537255B2 (en) 2013-11-21 2020-01-21 Phyzhon Health Inc. Optical fiber pressure sensor
AU2014355072A1 (en) 2013-11-26 2016-06-02 Alliqua Biomedical, Inc. Systems and methods for producing and delivering ultrasonic therapies for wound treatment and healing
FR3016525B1 (en) 2014-01-22 2021-08-27 Centre Hospitalier Univ Bordeaux CATHETER FOR INTERVENTIONS UNDER VISUAL CONTROL ON THE HEART
JP6303557B2 (en) * 2014-02-06 2018-04-04 ニプロ株式会社 catheter
US10405881B2 (en) 2014-02-06 2019-09-10 Nipro Corporation Catheter
WO2015120256A2 (en) 2014-02-06 2015-08-13 C.R. Bard, Inc. Systems and methods for guidance and placement of an intravascular device
US10092742B2 (en) 2014-09-22 2018-10-09 Ekos Corporation Catheter system
US10258240B1 (en) 2014-11-24 2019-04-16 Vascular Imaging Corporation Optical fiber pressure sensor
US10973584B2 (en) 2015-01-19 2021-04-13 Bard Access Systems, Inc. Device and method for vascular access
EP3307388B1 (en) 2015-06-10 2022-06-22 Ekos Corporation Ultrasound catheter
US10349890B2 (en) 2015-06-26 2019-07-16 C. R. Bard, Inc. Connector interface for ECG-based catheter positioning system
US11660073B2 (en) * 2015-10-30 2023-05-30 Georgia Tech Research Corporation Foldable 2-D CMUT-on-CMOS arrays
US11000207B2 (en) 2016-01-29 2021-05-11 C. R. Bard, Inc. Multiple coil system for tracking a medical device
US20180140321A1 (en) 2016-11-23 2018-05-24 C. R. Bard, Inc. Catheter With Retractable Sheath And Methods Thereof
US10765410B2 (en) * 2016-12-07 2020-09-08 Boston Scientific Scimed, Inc. Systems and methods for real-time biopsy needle and target tissue visualization
US11596726B2 (en) 2016-12-17 2023-03-07 C.R. Bard, Inc. Ultrasound devices for removing clots from catheters and related methods
US10758256B2 (en) 2016-12-22 2020-09-01 C. R. Bard, Inc. Ultrasonic endovascular catheter
US10582983B2 (en) 2017-02-06 2020-03-10 C. R. Bard, Inc. Ultrasonic endovascular catheter with a controllable sheath
US10188368B2 (en) 2017-06-26 2019-01-29 Andreas Hadjicostis Image guided intravascular therapy catheter utilizing a thin chip multiplexor
US10492760B2 (en) 2017-06-26 2019-12-03 Andreas Hadjicostis Image guided intravascular therapy catheter utilizing a thin chip multiplexor
US11109909B1 (en) 2017-06-26 2021-09-07 Andreas Hadjicostis Image guided intravascular therapy catheter utilizing a thin ablation electrode
US10973461B2 (en) 2018-01-10 2021-04-13 Biosense Webster (Israel) Ltd. Mapping of intra-body cavity using a distributed ultrasound array on basket catheter
WO2020081373A1 (en) 2018-10-16 2020-04-23 Bard Access Systems, Inc. Safety-equipped connection systems and methods thereof for establishing electrical connections
EP4027912A4 (en) 2019-09-12 2023-08-16 Relievant Medsystems, Inc. Systems and methods for tissue modulation

Family Cites Families (164)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
NL169956C (en) 1971-03-31 1982-09-16 Univ Erasmus DEVICE FOR DIAGNOSTIC EXAMINATION WITH ULTRA-SOUND BUNDLES.
US3817089A (en) 1971-06-30 1974-06-18 Interscience Res Inst Rotating probe high data acquistion rate apparatus
US3938502A (en) 1972-02-22 1976-02-17 Nicolaas Bom Apparatus with a catheter for examining hollow organs or bodies with the ultrasonic waves
AT343783B (en) 1974-03-27 1978-06-12 Siemens Ag ULTRASONIC DEVICE FOR MEDICAL DIAGNOSIS
US4028934A (en) 1975-11-04 1977-06-14 Yeda Research & Development Co. Ltd. Ultrasonic stereoscopic imaging device
US4162282A (en) * 1976-04-22 1979-07-24 Coulter Electronics, Inc. Method for producing uniform particles
US4142412A (en) 1976-05-12 1979-03-06 Sutures Inc. Doppler flow meter and method
US4141347A (en) 1976-09-21 1979-02-27 Sri International Real-time ultrasonic B-scan imaging and Doppler profile display system and method
US4276885A (en) * 1979-05-04 1981-07-07 Rasor Associates, Inc Ultrasonic image enhancement
US4313444A (en) 1979-05-14 1982-02-02 New York Institute Of Technology Method and apparatus for ultrasonic Doppler detection
US4354502A (en) 1979-08-28 1982-10-19 The Board Of Regents Of The University Of Washington Intravascular catheter including untrasonic transducer for use in detection and aspiration of air emboli
US4327738A (en) 1979-10-19 1982-05-04 Green Philip S Endoscopic method & apparatus including ultrasonic B-scan imaging
GB2063474B (en) 1979-10-24 1984-06-06 Olympus Optical Co Coeliac cavity ultrasonic diagnosis apparatus
US4310505A (en) * 1979-11-08 1982-01-12 California Institute Of Technology Lipid vesicles bearing carbohydrate surfaces as lymphatic directed vehicles for therapeutic and diagnostic substances
JPS56152635A (en) 1980-04-28 1981-11-26 Olympus Optical Co Ultrasonic diagnosis apparatus
AU545866B2 (en) * 1980-11-17 1985-08-01 Schering Aktiengesellschaft Microbubble precursors and methods for their production and use
US4657756A (en) * 1980-11-17 1987-04-14 Schering Aktiengesellschaft Microbubble precursors and apparatus for their production and use
US4533254A (en) * 1981-04-17 1985-08-06 Biotechnology Development Corporation Apparatus for forming emulsions
JPS57190552A (en) 1981-05-20 1982-11-24 Olympus Optical Co Ultrasonic diagnostic apparatus
EP0068961A3 (en) * 1981-06-26 1983-02-02 Thomson-Csf Apparatus for the local heating of biological tissue
DE3141022A1 (en) * 1981-10-15 1983-04-28 Siemens AG, 1000 Berlin und 8000 München ULTRASONIC PROBE INSERTABLE INTO A BODY
US4546771A (en) * 1982-03-04 1985-10-15 Indianapolis Center For Advanced Research, Inc. (Icfar) Acoustic microscope
US4462408A (en) * 1982-05-17 1984-07-31 Advanced Technology Laboratories, Inc. Ultrasonic endoscope having elongated array mounted in manner allowing it to remain flexible
US4467779A (en) * 1982-09-15 1984-08-28 Vsesojuzny Nauchnoissledovatelsky Institut Ispolzovania Gaza V Narodnom Khozyaistve Radiation tube
DE3374522D1 (en) * 1982-10-26 1987-12-23 University Of Aberdeen
US4509526A (en) 1983-02-08 1985-04-09 Lawrence Medical Systems, Inc. Method and system for non-invasive ultrasound Doppler cardiac output measurement
US4582067A (en) * 1983-02-14 1986-04-15 Washington Research Foundation Method for endoscopic blood flow detection by the use of ultrasonic energy
US4543960A (en) 1983-04-11 1985-10-01 Advanced Technology Laboratories, Inc. Transesophageal echo cardiography scanhead
US4900540A (en) * 1983-06-20 1990-02-13 Trustees Of The University Of Massachusetts Lipisomes containing gas for ultrasound detection
FR2563725B1 (en) * 1984-05-03 1988-07-15 Dory Jacques APPARATUS FOR EXAMINING AND LOCATING ULTRASONIC TUMORS WITH A LOCALIZED HYPERTHERMAL TREATMENT DEVICE
DE3346405A1 (en) * 1983-12-22 1985-07-04 Kernforschungszentrum Karlsruhe Gmbh, 7500 Karlsruhe METHOD FOR THE IMPROVED SEPARATION OF THE RECOVERY OF THE URAN AND PLUTONIUM FUELS AND THE IMPROVED SEPARATION OF THE FUELS TO BE RECOVERED FROM HIM IN A REPROCESSING PROCESS
GB8407557D0 (en) * 1984-03-23 1984-05-02 Hayward J A Polymeric lipsomes
US4728575A (en) * 1984-04-27 1988-03-01 Vestar, Inc. Contrast agents for NMR imaging
US4550607A (en) 1984-05-07 1985-11-05 Acuson Phased array acoustic imaging system
US4620546A (en) * 1984-06-30 1986-11-04 Kabushiki Kaisha Toshiba Ultrasound hyperthermia apparatus
US4880635B1 (en) * 1984-08-08 1996-07-02 Liposome Company Dehydrated liposomes
US4921706A (en) * 1984-11-20 1990-05-01 Massachusetts Institute Of Technology Unilamellar lipid vesicles and method for their formation
US4671295A (en) 1985-01-15 1987-06-09 Applied Biometrics, Inc. Method for measuring cardiac output
US4689986A (en) * 1985-03-13 1987-09-01 The University Of Michigan Variable frequency gas-bubble-manipulating apparatus and method
JPH0653120B2 (en) 1985-05-10 1994-07-20 オリンパス光学工業株式会社 Ultrasonic diagnostic equipment
US4733669A (en) 1985-05-24 1988-03-29 Cardiometrics, Inc. Blood flow measurement catheter
US4957111A (en) * 1985-09-13 1990-09-18 Pfizer Hospital Products Group, Inc. Method of using a doppler catheter
US4699009A (en) 1985-11-05 1987-10-13 Acuson Dynamically focused linear phased array acoustic imaging system
US4865836A (en) * 1986-01-14 1989-09-12 Fluoromed Pharmaceutical, Inc. Brominated perfluorocarbon emulsions for internal animal use for contrast enhancement and oxygen transport
US4737323A (en) * 1986-02-13 1988-04-12 Liposome Technology, Inc. Liposome extrusion method
US4794931A (en) * 1986-02-28 1989-01-03 Cardiovascular Imaging Systems, Inc. Catheter apparatus, system and method for intravascular two-dimensional ultrasonography
US5000185A (en) 1986-02-28 1991-03-19 Cardiovascular Imaging Systems, Inc. Method for intravascular two-dimensional ultrasonography and recanalization
JPS62258676A (en) 1986-05-01 1987-11-11 小林製薬株式会社 Catheter
US4799931A (en) * 1986-05-14 1989-01-24 Lindstrom Richard L Intracorneal lens
US4771788A (en) 1986-07-18 1988-09-20 Pfizer Hospital Products Group, Inc. Doppler tip wire guide
US4728578A (en) * 1986-08-13 1988-03-01 The Lubrizol Corporation Compositions containing basic metal salts and/or non-Newtonian colloidal disperse systems and vinyl aromatic containing polymers
US4781871A (en) * 1986-09-18 1988-11-01 Liposome Technology, Inc. High-concentration liposome processing method
US4756313A (en) 1986-11-05 1988-07-12 Advanced Diagnostic Medical Systems, Inc. Ultrasonic probe
US4757821A (en) 1986-11-12 1988-07-19 Corazonix Corporation Omnidirectional ultrasonic probe
ATE64487T1 (en) 1986-12-05 1991-06-15 Siemens Ag INTRACAVITARY ULTRASOUND SCANNING DEVICE.
US5148610A (en) * 1986-12-15 1992-09-22 Gte Valenite Corporation Precision parallel mechanical float
US4802487A (en) 1987-03-26 1989-02-07 Washington Research Foundation Endoscopically deliverable ultrasound imaging system
US4869256A (en) 1987-04-22 1989-09-26 Olympus Optical Co., Ltd. Endoscope apparatus
US4841977A (en) * 1987-05-26 1989-06-27 Inter Therapy, Inc. Ultra-thin acoustic transducer and balloon catheter using same in imaging array subassembly
US4917097A (en) 1987-10-27 1990-04-17 Endosonics Corporation Apparatus and method for imaging small cavities
GB2212267B (en) 1987-11-11 1992-07-29 Circulation Res Ltd Methods and apparatus for the examination and treatment of internal organs
US4841979A (en) 1988-01-25 1989-06-27 Capistrano Labs, Inc. Ultrasonic prostate probe assembly
US4887605A (en) * 1988-02-18 1989-12-19 Angelsen Bjorn A J Laser catheter delivery system for controlled atheroma ablation combining laser angioplasty and intra-arterial ultrasonic imagining
US4951677A (en) * 1988-03-21 1990-08-28 Prutech Research And Development Partnership Ii Acoustic imaging catheter and the like
US4893624A (en) * 1988-06-21 1990-01-16 Massachusetts Institute Of Technology Diffuse focus ultrasound hyperthermia system
US4911170A (en) * 1988-08-22 1990-03-27 General Electric Company High frequency focused ultrasonic transducer for invasive tissue characterization
US5140558A (en) 1988-08-29 1992-08-18 Acoustic Imaging Technologies Corporation Focused ultrasound imaging system and method
DE3829603A1 (en) 1988-09-01 1990-03-15 Kontron Holding Ag ULTRASONIC DOSCOPE DEVICE
US5014710A (en) 1988-09-13 1991-05-14 Acuson Corporation Steered linear color doppler imaging
US5165413A (en) 1988-09-13 1992-11-24 Acuson Corporation Steered linear color doppler imaging
IL91664A (en) * 1988-09-28 1993-05-13 Yissum Res Dev Co Ammonium transmembrane gradient system for efficient loading of liposomes with amphipathic drugs and their controlled release
US4930515A (en) 1988-10-04 1990-06-05 Diasonics, Inc. Ultrasound probe with multi-orientation tip-mounted transducer
US4947852A (en) * 1988-10-05 1990-08-14 Cardiometrics, Inc. Apparatus and method for continuously measuring volumetric blood flow using multiple transducer and catheter for use therewith
US5159931A (en) 1988-11-25 1992-11-03 Riccardo Pini Apparatus for obtaining a three-dimensional reconstruction of anatomic structures through the acquisition of echographic images
JPH02177965A (en) 1988-12-29 1990-07-11 M & M:Kk Catheter of endoscope with balloon for blood vessel
US5199433A (en) 1989-02-06 1993-04-06 Arzco Medical Systems, Inc. Esophageal recording/pacing catheter with thermistor and cardiac imaging transceiver
US5033789A (en) * 1989-03-31 1991-07-23 Aisin Seiki Kabushiki Kaisha Convertible car body structure
US5107844A (en) 1989-04-06 1992-04-28 Olympus Optical Co., Ltd. Ultrasonic observing apparatus
US4936281A (en) * 1989-04-13 1990-06-26 Everest Medical Corporation Ultrasonically enhanced RF ablation catheter
DE3914619A1 (en) 1989-05-03 1990-11-08 Kontron Elektronik DEVICE FOR TRANSOESOPHAGEAL ECHOCARDIOGRAPHY
US5022399A (en) * 1989-05-10 1991-06-11 Biegeleisen Ken P Venoscope
GB2233094B (en) 1989-05-26 1994-02-09 Circulation Res Ltd Methods and apparatus for the examination and treatment of internal organs
US5029588A (en) 1989-06-15 1991-07-09 Cardiovascular Imaging Systems, Inc. Laser catheter with imaging capability
US5002059A (en) * 1989-07-26 1991-03-26 Boston Scientific Corporation Tip filled ultrasound catheter
US5115814A (en) 1989-08-18 1992-05-26 Intertherapy, Inc. Intravascular ultrasonic imaging probe and methods of using same
US5010886A (en) 1989-08-18 1991-04-30 Intertherapy, Inc. Medical probe assembly having combined ultrasonic imaging and laser ablation capabilities
US5038789A (en) * 1989-09-28 1991-08-13 Frazin Leon J Method and device for doppler-guided retrograde catheterization
US5125410A (en) 1989-10-13 1992-06-30 Olympus Optical Co., Ltd. Integrated ultrasonic diagnosis device utilizing intra-blood-vessel probe
JPH03151943A (en) 1989-11-08 1991-06-28 Matsushita Electric Ind Co Ltd Ultrasonic probe
US5070879A (en) 1989-11-30 1991-12-10 Acoustic Imaging Technologies Corp. Ultrasound imaging method and apparatus
DE69027284T2 (en) 1989-12-14 1996-12-05 Aloka Co Ltd Three-dimensional ultrasound scanner
US5148810A (en) 1990-02-12 1992-09-22 Acuson Corporation Variable origin-variable angle acoustic scanning method and apparatus
US5235986A (en) 1990-02-12 1993-08-17 Acuson Corporation Variable origin-variable angle acoustic scanning method and apparatus for a curved linear array
US5261408A (en) 1990-02-12 1993-11-16 Acuson Corporation Variable origin-variable acoustic scanning method and apparatus
US5161537A (en) 1990-03-26 1992-11-10 Matsushita Electric Industrial Co., Ltd. Ultrasonic diagnostic system
JPH03280939A (en) 1990-03-29 1991-12-11 Fujitsu Ltd Ultrasonic probe
US5100424A (en) 1990-05-21 1992-03-31 Cardiovascular Imaging Systems, Inc. Intravascular catheter having combined imaging abrasion head
JP2949783B2 (en) 1990-06-04 1999-09-20 オリンパス光学工業株式会社 Endoscopic treatment device
US5085221A (en) 1990-06-14 1992-02-04 Interspec, Inc. Ultrasonic imaging probe
JP3090718B2 (en) 1990-07-11 2000-09-25 株式会社東芝 Ultrasound diagnostic equipment
US5076279A (en) 1990-07-17 1991-12-31 Acuson Corporation Needle guide for assembly upon an ultrasound imaging transducer
NL9001755A (en) 1990-08-02 1992-03-02 Optische Ind De Oude Delft Nv ENDOSCOPIC SCANNER.
US5076278A (en) 1990-10-15 1991-12-31 Catheter Technology Co. Annular ultrasonic transducers employing curved surfaces useful in catheter localization
US5135001A (en) 1990-12-05 1992-08-04 C. R. Bard, Inc. Ultrasound sheath for medical diagnostic instruments
JPH04282141A (en) 1991-03-12 1992-10-07 Fujitsu Ltd Ultrasonic wave probe
US5438997A (en) 1991-03-13 1995-08-08 Sieben; Wayne Intravascular imaging apparatus and methods for use and manufacture
US5243988A (en) 1991-03-13 1993-09-14 Scimed Life Systems, Inc. Intravascular imaging apparatus and methods for use and manufacture
DE4209394C2 (en) 1991-03-26 1996-07-18 Hitachi Ltd Ultrasound imaging device
JPH06292669A (en) 1991-04-17 1994-10-21 Hewlett Packard Co <Hp> Ultrasonic probe
GB9109881D0 (en) 1991-05-08 1991-07-03 Advanced Tech Lab Transesophageal echocardiography scanner with rotating image plane
US5167537A (en) * 1991-05-10 1992-12-01 Amphenol Corporation High density mlv contact assembly
US5193546A (en) 1991-05-15 1993-03-16 Alexander Shaknovich Coronary intravascular ultrasound imaging method and apparatus
US5181514A (en) 1991-05-21 1993-01-26 Hewlett-Packard Company Transducer positioning system
US5183048A (en) 1991-06-24 1993-02-02 Endosonics Corporation Method and apparatus for removing artifacts from an ultrasonically generated image of a small cavity
US5199437A (en) 1991-09-09 1993-04-06 Sensor Electronics, Inc. Ultrasonic imager
US5325860A (en) 1991-11-08 1994-07-05 Mayo Foundation For Medical Education And Research Ultrasonic and interventional catheter and method
US5713363A (en) 1991-11-08 1998-02-03 Mayo Foundation For Medical Education And Research Ultrasound catheter and method for imaging and hemodynamic monitoring
US5704361A (en) * 1991-11-08 1998-01-06 Mayo Foundation For Medical Education And Research Volumetric image ultrasound transducer underfluid catheter system
US5186177A (en) 1991-12-05 1993-02-16 General Electric Company Method and apparatus for applying synthetic aperture focusing techniques to a catheter based system for high frequency ultrasound imaging of small vessels
US5211168A (en) 1991-12-20 1993-05-18 Hewlett-Packard Company Moving electrode transducer for real time ultrasound imaging for use in medical applications
US5269307A (en) * 1992-01-31 1993-12-14 Tetrad Corporation Medical ultrasonic imaging system with dynamic focusing
US5222501A (en) 1992-01-31 1993-06-29 Duke University Methods for the diagnosis and ablation treatment of ventricular tachycardia
US5215002A (en) 1992-02-14 1993-06-01 Fmc Corporation Single vessel rotary processor
US5215092A (en) 1992-02-25 1993-06-01 Interspec, Inc. Ultrasonic probe assembly
US5329496A (en) 1992-10-16 1994-07-12 Duke University Two-dimensional array ultrasonic transducers
US5373845A (en) 1992-05-22 1994-12-20 Echo Cath, Ltd. Apparatus and method for forward looking volume imaging
US5361768A (en) 1992-06-30 1994-11-08 Cardiovascular Imaging Systems, Inc. Automated longitudinal position translator for ultrasonic imaging probes, and methods of using same
US5236408A (en) * 1992-07-21 1993-08-17 International Paper Box Machine Company, Inc. Method and apparatus for forming carton blanks with hemmed edges
US5297553A (en) 1992-09-23 1994-03-29 Acuson Corporation Ultrasound transducer with improved rigid backing
US5383460A (en) 1992-10-05 1995-01-24 Cardiovascular Imaging Systems, Inc. Method and apparatus for ultrasound imaging and atherectomy
US5291893A (en) 1992-10-09 1994-03-08 Acoustic Imaging Technologies Corporation Endo-luminal ultrasonic instrument and method for its use
US5285788A (en) 1992-10-16 1994-02-15 Acuson Corporation Ultrasonic tissue imaging method and apparatus with doppler velocity and acceleration processing
US5335663A (en) 1992-12-11 1994-08-09 Tetrad Corporation Laparoscopic probes and probe sheaths useful in ultrasonic imaging applications
CA2110148C (en) 1992-12-24 1999-10-05 Aaron Fenster Three-dimensional ultrasound imaging system
US5311871A (en) 1993-01-12 1994-05-17 Yock Paul G Syringe with ultrasound emitting transducer for flow-directed cannulation of arteries and veins
US5373849A (en) 1993-01-19 1994-12-20 Cardiovascular Imaging Systems, Inc. Forward viewing imaging catheter
US5329927A (en) 1993-02-25 1994-07-19 Echo Cath, Inc. Apparatus and method for locating an interventional medical device with a ultrasound color imaging system
US5469852A (en) 1993-03-12 1995-11-28 Kabushiki Kaisha Toshiba Ultrasound diagnosis apparatus and probe therefor
US5305756A (en) 1993-04-05 1994-04-26 Advanced Technology Laboratories, Inc. Volumetric ultrasonic imaging with diverging elevational ultrasound beams
WO1994027501A1 (en) 1993-05-24 1994-12-08 Boston Scientific Corporation Medical acoustic imaging catheter and guidewire
US5465724A (en) 1993-05-28 1995-11-14 Acuson Corporation Compact rotationally steerable ultrasound transducer
US5460181A (en) 1994-10-06 1995-10-24 Hewlett Packard Co. Ultrasonic transducer for three dimensional imaging
US5398689A (en) 1993-06-16 1995-03-21 Hewlett-Packard Company Ultrasonic probe assembly and cable therefor
US5385148A (en) 1993-07-30 1995-01-31 The Regents Of The University Of California Cardiac imaging and ablation catheter
US5438998A (en) 1993-09-07 1995-08-08 Acuson Corporation Broadband phased array transducer design with frequency controlled two dimension capability and methods for manufacture thereof
US5415175A (en) 1993-09-07 1995-05-16 Acuson Corporation Broadband phased array transducer design with frequency controlled two dimension capability and methods for manufacture thereof
US5402793A (en) 1993-11-19 1995-04-04 Advanced Technology Laboratories, Inc. Ultrasonic transesophageal probe for the imaging and diagnosis of multiple scan planes
JP2833456B2 (en) 1993-11-22 1998-12-09 株式会社東芝 Insertable ultrasound system
US5474075A (en) 1993-11-24 1995-12-12 Thomas Jefferson University Brush-tipped catheter for ultrasound imaging
US5377685A (en) 1993-12-17 1995-01-03 Baylis Medical Company, Inc. Ultrasound catheter with mechanically steerable beam
US5425370A (en) 1994-03-23 1995-06-20 Echocath, Inc. Method and apparatus for locating vibrating devices
US5421336A (en) 1994-04-04 1995-06-06 Echo Cath, Inc. Method for attaching an interventional medical device to a vibratory member associated with visualization by an ultrasound imaging system
US5469930A (en) * 1994-06-17 1995-11-28 Harley-Davidson, Inc. Motorcycle rear wheel suspension
US5479929A (en) 1994-06-27 1996-01-02 Acuson Corporation Drive system with a multiturn rotary stop
US5467779A (en) 1994-07-18 1995-11-21 General Electric Company Multiplanar probe for ultrasonic imaging
US5549111A (en) 1994-08-05 1996-08-27 Acuson Corporation Method and apparatus for adjustable frequency scanning in ultrasound imaging
JPH0884732A (en) 1994-09-19 1996-04-02 Fujitsu Ltd Probe for ultrasonic diagnosis
US5503152A (en) 1994-09-28 1996-04-02 Tetrad Corporation Ultrasonic transducer assembly and method for three-dimensional imaging
US5487388A (en) 1994-11-01 1996-01-30 Interspec. Inc. Three dimensional ultrasonic scanning devices and techniques
US5749833A (en) 1995-08-15 1998-05-12 Hakki; A-Hamid Combined echo-electrocardiographic probe
US5697377A (en) 1995-11-22 1997-12-16 Medtronic, Inc. Catheter mapping system and method
US5699805A (en) 1996-06-20 1997-12-23 Mayo Foundation For Medical Education And Research Longitudinal multiplane ultrasound transducer underfluid catheter system
US5904651A (en) 1996-10-28 1999-05-18 Ep Technologies, Inc. Systems and methods for visualizing tissue during diagnostic or therapeutic procedures
US5876345A (en) 1997-02-27 1999-03-02 Acuson Corporation Ultrasonic catheter, system and method for two dimensional imaging or three-dimensional reconstruction

Cited By (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070182287A1 (en) * 2004-04-20 2007-08-09 Marc Lukacs Arrayed Ultrasonic Transducer
US7830069B2 (en) 2004-04-20 2010-11-09 Sunnybrook Health Sciences Centre Arrayed ultrasonic transducer
US7488288B2 (en) * 2004-07-29 2009-02-10 Fujinon Corporation Ultrasonic endoscope
US20060025691A1 (en) * 2004-07-29 2006-02-02 Fujinon Corporation Ultrasonic endoscope
USRE46185E1 (en) 2005-11-02 2016-10-25 Fujifilm Sonosite, Inc. High frequency array ultrasound system
US7901358B2 (en) 2005-11-02 2011-03-08 Visualsonics Inc. High frequency array ultrasound system
US8727993B2 (en) 2005-11-30 2014-05-20 General Electric Company Apparatuses comprising catheter tips, including mechanically scanning ultrasound probe catheter tip
US20070167825A1 (en) * 2005-11-30 2007-07-19 Warren Lee Apparatus for catheter tips, including mechanically scanning ultrasound probe catheter tip
US20070167813A1 (en) * 2005-11-30 2007-07-19 Warren Lee Apparatuses Comprising Catheter Tips, Including Mechanically Scanning Ultrasound Probe Catheter Tip
US20070167826A1 (en) * 2005-11-30 2007-07-19 Warren Lee Apparatuses for thermal management of actuated probes, such as catheter distal ends
US20070167824A1 (en) * 2005-11-30 2007-07-19 Warren Lee Method of manufacture of catheter tips, including mechanically scanning ultrasound probe catheter tip, and apparatus made by the method
US8316518B2 (en) 2008-09-18 2012-11-27 Visualsonics Inc. Methods for manufacturing ultrasound transducers and other components
US9173047B2 (en) 2008-09-18 2015-10-27 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components
US9184369B2 (en) 2008-09-18 2015-11-10 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components
US20100156244A1 (en) * 2008-09-18 2010-06-24 Marc Lukacs Methods for manufacturing ultrasound transducers and other components
US9555443B2 (en) 2008-09-18 2017-01-31 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components
US9935254B2 (en) 2008-09-18 2018-04-03 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components
US10596597B2 (en) 2008-09-18 2020-03-24 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components
US11094875B2 (en) 2008-09-18 2021-08-17 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components
US11845108B2 (en) 2008-09-18 2023-12-19 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components

Also Published As

Publication number Publication date
WO1993008738A1 (en) 1993-05-13
US20040068191A1 (en) 2004-04-08
US5345940A (en) 1994-09-13
US5325860A (en) 1994-07-05
US7156812B2 (en) 2007-01-02
US6306096B1 (en) 2001-10-23

Similar Documents

Publication Publication Date Title
US5704361A (en) Volumetric image ultrasound transducer underfluid catheter system
US6306096B1 (en) Volumetric image ultrasound transducer underfluid catheter system
US5713363A (en) Ultrasound catheter and method for imaging and hemodynamic monitoring
JP3972129B2 (en) Catheter device for transvascular, ultrasonic and hemodynamic evaluation
US11000185B2 (en) Devices, systems, and methods for visualizing an occluded vessel
US5699805A (en) Longitudinal multiplane ultrasound transducer underfluid catheter system
US6066096A (en) Imaging probes and catheters for volumetric intraluminal ultrasound imaging and related systems
EP2077760B1 (en) Image guided catheters
US8790262B2 (en) Method for implementing an imaging and navigation system
US6171247B1 (en) Underfluid catheter system and method having a rotatable multiplane transducer
US20160081656A1 (en) Image Guided Catheters and Methods of Use
US20090292204A1 (en) Method and device for recognizing tissue structure using doppler effect
JP2021536282A (en) Control and display of imaging surfaces for intraluminal ultrasonography, as well as related devices, systems and methods.

Legal Events

Date Code Title Description
STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION