US20010034501A1 - Pressure sensor for therapeutic delivery device and method - Google Patents

Pressure sensor for therapeutic delivery device and method Download PDF

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Publication number
US20010034501A1
US20010034501A1 US09/816,708 US81670801A US2001034501A1 US 20010034501 A1 US20010034501 A1 US 20010034501A1 US 81670801 A US81670801 A US 81670801A US 2001034501 A1 US2001034501 A1 US 2001034501A1
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transducer
contact
apparatus
pressure
tool
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US09/816,708
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Curtis Tom
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Boston Scientific Scimed Inc
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MicroHeart Inc
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Priority to US09/816,708 priority patent/US20010034501A1/en
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Publication of US20010034501A1 publication Critical patent/US20010034501A1/en
Assigned to SCIMED LIFE SYSTEMS, INC. reassignment SCIMED LIFE SYSTEMS, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: BOSTON SCIENTIFIC CORPORATION
Assigned to BOSTON SCIENTIFIC CORPORATION reassignment BOSTON SCIENTIFIC CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: MICROHEART, INC.
Assigned to SCIMED LIFE SYSTEMS, INC. reassignment SCIMED LIFE SYSTEMS, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: BOSTON SCIENTIFIC CORPORATION, INC.
Assigned to BOSTON SCIENTIFIC CORPORATION reassignment BOSTON SCIENTIFIC CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: MICROHEART, INC.
Assigned to SCIMED LIFE SYSTEMS, INC. reassignment SCIMED LIFE SYSTEMS, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: BOSTON SCIENTIFIC CORPORATION, INC.
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    • 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
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/68Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6852Catheters
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/68Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6885Monitoring or controlling sensor contact pressure
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/34Trocars; Puncturing needles
    • A61B17/3478Endoscopic needles, e.g. for infusion
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/34Trocars; Puncturing needles
    • A61B17/3494Trocars; Puncturing needles with safety means for protection against accidental cutting or pricking, e.g. limiting insertion depth, pressure sensors
    • 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
    • A61B2017/00247Making holes in the wall of the heart, e.g. laser Myocardial revascularization
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B2017/22072Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an instrument channel, e.g. for replacing one instrument by the other
    • A61B2017/22074Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an instrument channel, e.g. for replacing one instrument by the other the instrument being only slidable in a channel, e.g. advancing optical fibre through a channel
    • A61B2017/22077Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an instrument channel, e.g. for replacing one instrument by the other the instrument being only slidable in a channel, e.g. advancing optical fibre through a channel with a part piercing the tissue
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/34Trocars; Puncturing needles
    • A61B2017/348Means for supporting the trocar against the body or retaining the trocar inside the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00345Vascular system
    • A61B2018/00351Heart
    • A61B2018/00392Transmyocardial revascularisation
    • 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
    • A61B90/06Measuring instruments not otherwise provided for
    • A61B2090/062Measuring instruments not otherwise provided for penetration depth
    • 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
    • A61B90/06Measuring instruments not otherwise provided for
    • A61B2090/064Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178Syringes
    • A61M5/31Details
    • A61M5/32Needles; Details of needles pertaining to their connection with syringe or hub; Accessories for bringing the needle into, or holding the needle on, the body; Devices for protection of needles

Abstract

The present invention is an apparatus for treating a selected patient tissue or organ region, at the surface of such region. The apparatus has an accessing tool for accessing the patient region, the tool having a distal end, and a proximal end at which the tool can be manipulated to place the distal end adjacent to the patient region. The apparatus also has a probe carried on the distal end and defining a contact surface that may be urged against the patient region thereby creating contact pressure. A pressure transducer is operatively coupled to the probe and is capable of producing a measurable response to the contact pressure. A monitoring device is operatively connected to the pressure transducer, for determining the contact pressure. An effector is operatively disposed on the probe for producing a given effect on the patient region when the effector is activated, and an activator operatively connected to the effector, by which the effector can be activated.

Description

  • This application claims priority of U.S. Provisional Patent Application No. 60/191,610 filed Mar. 23, 2000, which is incorporated in its entirety herein by reference.[0001]
  • FIELD OF THE INVENTION
  • The present invention relates to an apparatus and method for affecting a body tissue, such as the heart, at the tissue surface, for purposes of injecting material into the tissue or otherwise stimulating a desired therapeutic effect on the tissue. [0002]
  • BACKGROUND OF THE INVENTION
  • Percutaneous catheter-based treatments of cardiovascular disease require that navigation of the catheter within the body be done with a mode of visualizing the catheter as it is moved within the body. The most popular mode of visualization is X-ray fluoroscopy, where an operator is able to monitor a radiopaque device as it travels within a body lumen, such as the cardiovascular system. [0003]
  • Recently, interventional procedures that require catheter navigation within the chambers of the heart have been developed; these include electrophysiological mapping and ablation and transmyocardial revascularization. These procedures also often require that the tip of the catheter be placed in contact with a wall of the beating heart in order to deliver the desired treatment safely. Potential complications of this procedure may be perforation of the wall when excessive force is applied or ineffective treatment due to poor tip contact. Under fluoroscopic guidance it is often difficult to assess when the catheter tip has reached the wall because live fluoroscopy does not visualize that wall itself, since it is not radiopaque. For the same reason, even after the catheter tip has reached the wall, it is difficult to determine whether the tip consistently remains in contact with the wall or if excessive force is applied to the wall. Finally, it is also difficult to determine whether the catheter tip is substantially perpendicular to the wall because fluoroscopy yields a two-dimensional image of the device in three-dimensional space. [0004]
  • Thus, for procedures where a medical instrument must be placed in firm but not excessive contact with anatomical surface, there is an apparent need for a device which is able to provide information to the user of the instrument that is indicative of the existence and magnitude of the contact force. Furthermore, for procedures where the medical instrument must also be placed either perpendicular or at some selected angle to the anatomical surface, there is an apparent need for a device which is able to provide information to the user of the instrument that is indicative of the incident angle of the contact force with respect to the anatomical surface. [0005]
  • SUMMARY OF THE INVENTION
  • It is therefore an object of this invention to provide such a device for overcoming the above-mentioned problems. [0006]
  • It is another object of this invention to provide information to the user of a medical instrument, such as a catheter, that must be placed in contact with the surface of an anatomical structure, to increase the likelihood of safely delivering the desired treatment while reducing the possibility of inflicting perforation type injuries or providing inadequate treatment. [0007]
  • It is further an object of this invention to provide a method for generating information regarding whether the tip of a medical instrument, such as a catheter or probe, is in contact with a surface of a tissue or organ, and, if so, the magnitude of the contact force and the incident angle of the contact force with respect to the anatomical surface. [0008]
  • In summary, the present invention is an apparatus for treating a selected patient tissue or organ region, at the surface of such region. The apparatus has an accessing tool for accessing the patient region, the tool having a distal end, and a proximal end at which the tool can be manipulated to place the distal end adjacent to the patient region. [0009]
  • The apparatus also has a probe carried on the distal end and defining a contact surface that may be urged against the patient region thereby creating contact pressure. At least one pressure transducer, wherein each pressure transducer is operatively coupled to the probe and is capable of producing a measurable response to the contact pressure experienced adjacent to the pressure transducer. A monitoring device is operatively connected to each pressure transducer, for determining contact pressure. At least one effector, wherein each effector is operatively disposed on the probe for producing a given effect on the patient region when the effector is activated, and an activator operatively connected to the effector, by which the effector can be activated.[0010]
  • BRIEF DESCRIPTION OF THE FIGURES
  • FIG. 1 illustrates the force contact transducer attached to a probing tool and monitoring circuitry; [0011]
  • FIG. 2 is an exploded view of a force contact transducer constructed in accordance with embodiments of the invention; [0012]
  • FIG. 3 illustrates a view of the cap and base of the force contact transducer; [0013]
  • FIG. 4 illustrates a view of the cap region of the force contact transducer; [0014]
  • FIG. 5 illustrates a detailed exploded view of contact elements of the invention; [0015]
  • FIG. 6 illustrates one embodiment of the invention that employs a thin film transducer array disposed around a tool shaft; [0016]
  • FIGS. [0017] 7A-7D illustrate embodiments of a transducer array and a single transducer;
  • FIG. 8 illustrates, in simplified view, the cap region of a transducer capable of detecting both axial and lateral force components applied to the sensor; and [0018]
  • FIG. 9 illustrates an embodiment of the invention of the invention that measures force movement by electrical inductance, rather than by resistance.[0019]
  • DETAILED DESCRIPTION OF THE INVENTION
  • FIG. 1 shows an apparatus [0020] 44 constructed according to the invention. The apparatus provides an assembly or tool 46, for accessing a patient tissue or organ region 47, and a sensor device 20, detailed below, for determining the pressure of the probe against the target tissue and, in some embodiments, the angle of contact between the probe and target tissue.
  • In general application, the assembly is used to access an internal target region, and to provide a therapeutic stimulus, such as injection of a therapeutic compound or gene, forming a laser channel, or introducing an injury, e.g., by ultrasonic waves, infrared radiation, or mechanical injury on below the surface of the target region. E.g., to stimulate an angiogenic response in the target region. The therapeutic stimulus is preferably administered/provided through the assembly probe. The sensor device operates, in accordance with the invention, to provide information to the user about the position of the probe with respect to the target region, since the target region is generally not directly viewable by the user, e.g., physician. [0021]
  • In the embodiment shown, the medical instrument includes a rigid shaft [0022] 46, which may have a curved section, as shown in FIG. 1. Alternatively, the medical instrument is a flexible catheter, e.g., for delivery of a therapeutic stimulus to a target site within the vasculature or heart. The distal end of the shaft may be the base of the transducer, as shown in FIG. 1, or a separate element securely affixed to base. A handle 48 is attached to the proximal end of the shaft or base. In one embodiment, the shaft is pivotally attached to the transducer base to permit the tip of the medical instrument to bend. The handle includes a control panel 50 having for control of the instrument by the user. Also shown are a bridge divider, an output device 54, such as a display device, and signal processing circuitry 56 whose operation is described below.
  • While not detailed here, handle [0023] 48 is designed to produce a selected therapeutic effect on target tissue, when a desired pressure and/or pressure contact angle is sensed between the probe and target tissue. The therapeutic effect may be the injection, by a needle or needleless injection system, of a solution or suspension of a therapeutic compound or gene, or a radiation or ultrasound injury produced by an light-carrying fiber or sonic device on the probe, or a mechanical injury produced by a mechanical tool on the probe, as in conventional. The apparatus is therefore equipped, according to well-known devices, to provide an extendable needle, a light fiber, an extendable mechanical-injury device, or the like to produce the desired therapeutic effect, in response to a signal applied by the user to handle 48. That is, handle 48 includes structure for activating the therapeutic receptor at the distal end of the apparatus. In one embodiment, the therapeutic response is activated when the distal end of the apparatus is positioned against the target tissue with a desired pressure, that is, above a selected pressure threshold or within a desired pressure range, as determined from the pressure sensor device of the invention. In addition, angle of contact as sensed by the device may be employed as a variable to be considered in an automated triggering.
  • FIG. 2 is an exploded view of a force contact transducer or device [0024] 20 constructed in accordance with embodiments of the invention. Device 20 includes an elongate, cylindrical base 22 that may be constructed of non-conductive material such as polycarbonate or a metallic conductive material such as surgical steel or similar material. The base has a larger diameter portion 24 that may serve as, or be attached to, a shaft of an associated medical instrument, such as needle-delivery device or light fiber, in which the transducer is incorporated. Extending from the distal end of the larger diameter portion is a reduced diameter portion 26.
  • Attached to, or formed integrally with, the reduced diameter portion is a flange [0025] 28 that has a central opening 28 a and one or more notches, such as notch 28 c, formed in its outer edge. An upper surface 28 b of the flange is electrically conductive (by placement of a not shown conductive layer and serves as one of the electrical conductors of the transducer. The details of the base are illustrated in FIG. 4.
  • Device [0026] 20 further includes a cap 30, which is generally cylindrical in shape and has an axial bore extending therethrough to define an inner wall. A plurality of rectangular feet 30 b are formed on one end surface 30 c of the cap, which surface acts as the second electrical conductor of the transducer. The cap is shown in more detail in FIG. 4.
  • Sandwiched between conducting surfaces [0027] 30 c and 28 b are: (i) a conductive or semi-conductive elastomer 32 that is preferably made of carbon loaded silicone rubber or other material with similar characteristics, and (ii) a thin, non-conducting insulating layer 34 that is preferably made of mylar, polyimide or other material which exhibits similar insulating or dielectric properties. Each of these components 32 and 34 has an opening 32 a and 34 a respectively formed therein so that these components may be received on the reduced diameter portion 26 of base 22. A lower surface 34 b of the insulating layer abuts against, but does not completely cover, conductor surface 28 b, so that a lower surface 32 b of the conductive elastomer is able to selectively make contact with conductor surface 28 b based on a force applied to the transducer, as will be explained in more detail below.
  • In the illustrated embodiment, this is accomplished by making opening [0028] 34 b in the form of a slot, as seen best in FIG. 5. However, this is merely one example; other arrangements are possible. For example, the insulator may have a central opening a plurality of radial arms providing a plurality of circumferential slots through which electrical contact between in the elastomer and the confronting conductive surface 28 b of flange 28.
  • Formed along the outer edge of insulator [0029] 34 is a notch 34 c, which is aligned with notch 32 c in elastomer 32 and slot 28 c in flange 28, as seen particularly in FIGS. 3 and 4. The notches accommodate a pair of electrical leads 36 a and 36 b that are in electrical contact with conducting surfaces 28 b and 30 c, respectively, as shown in FIGS. 2 and 3.
  • Formed in an upper surface [0030] 32 c of the conductive elastomer is a plurality of indents or footprints that correspond to the feet 30 b formed on conductive surface 30 c of the cap. Each one of the feet 30 b is adapted to fit securely within its complementary footprint to maintain constant contact between the conductive surface of cap 30 and the upper surface of conductive elastomer 32.
  • It is desirable to seal the components of the contact force transducer apparatus to prevent ingress of bodily or other fluids into the electrical regions of the apparatus. Furthermore, it is highly desired to seal the invention to prevent the egress of components from the contact force transducer apparatus. Accordingly, one skilled in the art would realize that numerous means for sealing the apparatus are possible. For example, a potting material may be introduced at component junctions so as to seal the device without interfering with its intended function. Alternatively and as discussed in detail below, a shroud or tip may be employed to seal the apparatus. Such sealing means may be preformed or formed in place, for example, by dipping an appropriately masked apparatus in a sealing compound to create a tip or shroud in place. [0031]
  • A tip element [0032] 38 may be employed to protect the cap. In one embodiment, the tip has a lower end 38 a that is securely attached to an upper end of the cap, as shown in FIG. 2. In another embodiment, the tip extends over the cap-conductive elastomer-insulator assembly (not shown). In either case, when the tip is used, its outer surface 38 b acts as the contact surface of the transducer. When the tip is not employed, the upper end of the cap is the contact surface. The transducer components including the tip in assembled form are shown in FIG. 2. When the tip is not used, upper end 30 d serves as the contact surface of the transducer. The assembled transducer excluding the tip is shown in FIG. 3.
  • If desired, a suitable biologically compatible coating or cover [0033] 40 may be applied to the cap-conductive elastomer-insulator-flange assembly (and tip if included) to protect it and to prevent fluid ingress. Such a cover or coating, with portions broken away, is shown in FIG. 2.
  • A second embodiment of the invention (not shown) is similar to the first except that it further includes a thin insulator which fits between cap [0034] 30 and tip 38 to reduce the friction between these components and enable them to move relative to each other as the force applied to the contact surface of the transducer is varied.
  • In operation, an electrical excitation signal is generated in a bridge or divider circuit [0035] 52 (FIG. 1) and applied to the conductive surfaces or other electrical elements of the sensor described below. If a force below a predetermined threshold is applied to the contact surface of the transducer, the excitation signal will remain the same. However, if the applied force is just above the predetermined threshold, conductive elastomer 32, which is in constant contact with conductive surface 30 c, will extend or be pushed through the openings or perforations in insulating layer 34 to make contact with conductive surface 28 b. This causes the impedance between the two conductive surfaces to decrease, producing a change in the excitation signal which indicates that minimum contact has been made. As the applied force is further increased, the conductive elastomer compresses causing a further proportional drop in the impedance that, in turn, produces corresponding change in the excitation signal. Thus, the impedance and therefore the excitation signal varies with the magnitude of the applied force.
  • The bridge/divider circuit is in electrical communication with an output device [0036] 54 which may be in the form of audio or visual device adapted to provide an information signal to the user indicative of whether the outer surface of the transducer has made contact, and, if so, the magnitude of the contact. The output device may take a variety of different forms. For example, an LED bar graph or other display capable of rendering a graphical or visual representation may be used to provide a continuous, quasi-continuous or discrete indication of the magnitude of a force applied to the contact surface of the transducer, from a minimum applied force indicative of minimum contact to a predetermined maximum. Alternatively, or in addition to, a speaker or other audio device may be used to emit a sound when minimum contact is made and emit proportionally louder sounds as the firmness of the contact increases.
  • The sensitivity of the excitation signal and hence the information signal may be adjusted in a number of different ways. One way is by using an elastomer with a different conductivity and/or compressibility. Another way is with electronic signal processing circuitry with adjustable amplification and filtering. Such a signal processing circuit ([0037] 56) may be physically integrated with the bridge/divider circuit, or may be a separate circuit that is in electrical communication with the bridge/divider circuit, as illustrated in FIG. 1. The sensitivity of the signals (excitation and information) may also be adjusted by varying the size of the openings or perforations in the insulating layer, or by varying the thickness of the insulating layer. Larger perforations increase the sensitivity. In any case, the sensitivity of the transducer is set based on the desired contact force threshold and the minimum magnitude of change to be detected.
  • A flat transducer contact surface will generate less of an output signal if the tip is in contact with tissue surface at an oblique angle. On the other hand, a rounded or tapered contact surface will generate a greater output signal at an oblique angle of contact. Thus, the geometry of the contact surface may be tailored to provide feedback about the perpendicularity of the contact between the medical instrument tip and the tissue surface. Optionally, the friction coefficient of the tip or exposed cap material at the contact surface may be altered to provide for shear force as the probe is situated upon a tissue surface in a way that a lateral force vector component manifests, assuming at least some of the thrust force applies creates a later force component. The less the friction between the contact surface and the tissue surface, the less the shear or lateral force component realized. [0038]
  • In another embodiment, a plurality of discrete transducers can be distributed on the tip of a medical instrument to provide further information regarding the perpendicularity of the contact. In the case of two transducers, each covers 180 degrees of the tip surface; in the case of three transducers, each covers 120 degrees, etc. The combined signal from the multiple transducers may be processed to provide, in addition to contact and magnitude information, angle of contact of information as well. [0039]
  • In another particularly preferred embodiment, a transducer, or transducers if contact angle sensing is sought, may comprise a thin double mylar film layered sandwich as described in Krivopal, U.S. Pat. No. 5,989700, herein incorporated in its entirety by reference. Looking at FIG. 6, the instant invention differs from Krivopal in that sensor [0040] 60 has sensor elements 68 on a support 70 having an aperture 76 disposed in the center to permit tool shaft 64 to be disposed at a normal angle through the sensor or sensor array. Each individual sensor area is electrically accessible by leads 66.
  • The sensor support [0041] 70 which can either be rigid, or elastic depending on the degree of flexibility sought in the device. Disposed above the sensor support is a resilient or elastomeric cap 72 which mechanically communicates the probe tip contact surface incident angle and total contact force downward to sensor 60. Cap 72 may further include protuberances 78 to focus the communicated force onto sensors 68.
  • The entire probe tip may be covered by a sheath, not shown. Alternatively, a transducer, such as a thin film transducer, may be positioned directly on the contact surface, thereby creating a superior contact surface. Alternatively, the probe may lack a cap element and thus directly expose a transducer, such as a thin film transducer, to a tip surface opposite the tip contact surface, or the transducer may itself comprise the tip surface, and thus the contact surface as well. Each of these embodiments just described may include one or more transducers so that incident angle as well as force may be detected. [0042]
  • Considering now the embodiments shown in FIGS. [0043] 7A-77D, a sandwich 112 has a top mylar film 112 a, an upper conductive ink layer 112 b applied to the lower surface region of the top mylar film 112 a, an upper semiconductive ink 112 c applied to the upper conductive ink layer 112 b, an air gap 112 d, a lower semiconductive ink layer 112 e disposed upon a lower conductive ink layer 112 f which is disposed on the upper surface of a bottom mylar film 112 g.
  • There may be an insulting ring or sections surrounding the above described ink sandwich to separate the upper mylar layer from the lower mylar layer thus creating the air-gap between the upper and lower semi-conductive ink layers. In the case of a multiple transducer array [0044] 100, several sandwich regions 102, 104, 106 may be arranged upon the plane created by the mylar film, each region being in electrical communication with the monitoring unit, and each region is independently responsive to the contact force present at the corresponding region of the contact surface of the probe thus providing a means of determining the incident angle of the contact force with respect to the tissue surface by comparing the individual responses of each transducer sandwich region.
  • Alternatively, each sandwich region [0045] 114 may be a separate mylar film sandwich 116, with each electrode 118, 120 individually in electrical communication with the monitor device.
  • In another embodiment, the pressure transducers may be a combination to of a purely mechanical resilient device such as an elastomeric spacer, and a mechanical or electrical device for measuring the effect of the force upon the resilient device. Measurement may include a mechanical deflection of mechanically communicated information to a portion of the tool distal from the patient surface, or may be a switch or potentiometer mechanically operating is above its inherent mechanical (frictional) resistance. Mechanically communicated deflection may be monitored and displayed to a user as described below. [0046]
  • FIG. 8 shows another embodiment of a sensor device [0047] 80 for use in the apparatus of the invention. The device shown here is designed to measure both axial pressure, along an axis normal to the contact face of the probe, and lateral direction, i.e., force applied to a side region of the probe. The device includes a rigid mechanical support 81 which is attached at its lower end in the figure to the distal end of the accessing tool, and which provides a central opening 82 through which the therapeutic effector, e.g., needle or optical fiber is received.
  • The device has a flexible cap [0048] 83 that is rigidly attached to a radially extending annular ring 91 in the support. The cap is formed of a flexible polymer or elastomer material or other flexible material that permits the cap to deform when pressure is applied to the cap, when the probe is in contact with the target tissue. Carried on inner, upper surface of the cap is a preferably segments annular electrode ring 84 positioned to contact an annular conductive elastomer member 86 of the type described above, when an axial pressure acts and distorts the upper surface of the cap. The elastomer member, in turn, is seated on a insulative spacer 85 that provides an electrical barrier between the elastomer and support, but which provides openings or notches through which the elastomer can be pressed, when an axial force acts on it, as described with reference to FIGS. 1-4.
  • In operation, when an axial force is applied to the cap, the cap is distorted to bring electrode ring [0049] 84 into contact with elastomer member 86, pushing the elastomer through spaces in the insulative spacer 85. This changes the resistance of a circuit containing the two electrodes and the elastomer member in proportion to the total contact area that the elastomer makes with the support electrode, and this change in resistance is recorded and displayed to the user.
  • Carried on the annular side region of the support is a plurality of insulative members, such as elastomeric members [0050] 88 a, 88 b, arranged circumferentially about the support. Typically, the device includes three such members, each member being carried on an insulative spacer, such as spacers 89 a, 89 b. Similarly, carried on the inner confronting surface of the cap is a segmented electrode 87 which is disposed to make contact with individual elastomer members 84 when side regions of the cap are distorted by side pressure and brought against the confronting elastomeric segments. Thus, side-directed pressure is detected, as above, by a change in the resistance in one or more or the side elastomer members, as the cap electrodes push against the elastomer member(s), forcing surface portions of the member(s) through openings in the spacers, and lowering the resistance of each associated circuit containing the affected elements. The user thus has information about axial pressure, from the change in resistance (impedance) in the upper-cap circuit, and information about angle of contact by the extent of asymmetry in measured resistances of the three side circuits.
  • In a purely mechanical device there may be disposed between the probe and the proximal end of the tool an elastic resilient support. Absent any surface contact, the probe's contact surface remains perpendicular to the thrust axis of the tool because of the elastic resilient support. Attached to the tool side of the probe are the ends of at least 3 or more flexible shafts running parallel or coherently through the tool length. These shafts run slidably through and protrude beyond lumens within the tool body beginning at the probe facing side of the proximal end of the tool and terminating as openings at the distal or user end of the tool. As the contact surface is deflected away from the thrust axis of the tool, the distance between the probe contact surface and the tool varies depending on the angle of deflection. The shaft, beneath where the distance between the contact surface of the probe and the proximal end of the tool is least, will protrude out more from the distal or user end of the tool, whereas the shafts opposite will recede into the tool at the distal or user end. Consequently, a user will be able to observe angular relation of the probe to the tool by observing the protrusion or withdrawal of the shafts, thereby the user could adjust the incident angle of the tool to achieve a balanced shaft display. One skilled in the art would readily recognize that many variations of this embodiment are possible, especially with respect to how the angular information is displayed to the user. [0051]
  • In another multi-transducer embodiment, each pressure transducer is independently elastically and resiliently related to the contact surface, and another embodiment provides for each pressure transducer being mutually elastically and resiliently related to the contact surface. [0052]
  • In yet another embodiment, the monitor is operatively connected to the activator such that at a pre-selected measurement, the activator is activated thus causing the effector to activate. In a related embodiment, the monitor is operatively connected to the activator such that the activator can only be manually activated by the user when the monitor measures a predetermined measurement from the pressure transducer. In yet another related embodiment, the monitor does not affect the operability of the activator. [0053]
  • In yet another embodiment, the pressure transducer may respond to deflection by varying capacitance rather than resistance. Capacitance can be varied by sandwiching a pressure sensitive dielectric material between two electrodes. Alternatively, changes in pressure can be measured by varying inductance with inductor transducer device [0054] 90 illustrated in FIG. 90. As seen, the device includes a cap 94 which can move in an axial direction (the direction of arrow 100) toward and away from the relaxed (no-pressure) position shown in the figure, mounted for such axial movement on a support 92 which is carried on the distal end of the apparatus tool. The support provides an induction coil 99 formed of conductive wire windings 98 which are positioned adjacent a cylindrical permanent magnet 96 mounted on the cap.
  • Movement of the cap in the direction of arrow [0055] 100 caries magnet 96 past the inductive wires, producing a change in the inductance of the coil. Such changes can be monitored by incorporating the inductor into a LC or inductor-capacitor oscillating circuit and monitoring the change in the resonant frequency of the LC circuit.
  • In yet another embodiment, any transducer described herein may be combined with an ultrasonic transducer capable of detecting tissue density or thickness. For example, the ultrasonic transducer of Zanelli, et al., U.S. Pat. No. 6,024,703, herein incorporated in its entirety by reference, discloses an ultrasound device for axial ranging. This would provide for the ability to limit the throw or depth that an effector element is permitted to penetrate into the patient tissue underlying the tissue surface thus avoiding either to shallow, thus ineffective penetration, or to deep and thus harmful penetration of the effector element. [0056]
  • As should be apparent from the foregoing description, the present invention, unlike fluoroscopic methods provides force information such as but not limited to, force contact, magnitude and direction or incident angle with respect to the patient tissue surface, for catheter-based surgical procedures or other medical procedures where the degree of contact between the medical instrument and a surface of an anatomical structure is useful to know. In addition, such information may be provided in real-time and in a variety of formats using a low cost, disposable force contact transducer of the type disclosed herein. Such a transducer may be easily integrated into existing catheter tools, eliminating the need for extensive hardware/software interfaces. [0057]
  • While various embodiments of the invention have been illustrated and described, it will be evident to those skilled in the art in light of the foregoing disclosure that many further alternatives, modifications and variations are possible. For example, the insulator need not be a separate element but may be in the form of an insulative coating that is selectively applied to the conductive surface of the flange to permit the lower surface of the conductive elastomer to make contact with that conductive surface in accordance with the teachings of the invention. The invention disclosed herein is intended to embrace all such alternatives, modifications, and variations as may fall within the spirit and scope of the appended claims. [0058]

Claims (16)

what is claimed:
1. Apparatus for treating a selected patient tissue or organ region, at the surface of such region, comprising
an accessing tool for accessing the patient region, said tool having a distal end and a proximal end at which the tool can be manipulated to place the distal end adjacent such patient region,
a probe carried on said distal end and defining a contact surface that may be urged against said patient region thereby creating contact pressure,
a pressure transducer operatively coupled to said probe and capable of producing a measurable response to the contact pressure,
a monitoring device operatively connected to said pressure transducer, for determining the contact pressure,
an effector operatively disposed on said probe for producing a given effect on the patient region when effector is activated,
an activator operatively connected to said effector, by which said effector can be activated.
2. The apparatus of
claim 1
, wherein said monitor is operatively connected to a user readable display.
3. The apparatus of
claim 1
, wherein said activator is operatively connected to said monitor and activates said effector at a pre-selected range.
4. The apparatus of
claim 1
, wherein said monitoring device is operable to measure the range over which the pressure transducer is responsive to changes in the force applied to the transducer, and to determine from such range, a contact-pressure range within which activation of the effector is optimized for treatment effect.
5. The apparatus of
claim 1
, wherein said pressure transducer is responsive to the magnitude and direction of force applied to the transducer, and said monitor is operable to determine both the contact pressure and the approximate incidence angle of said tool with respect to the surface of the patient region.
6. The apparatus of
claim 5
, wherein said pressure transducer includes a plurality of pressure-transducer units, each carried on the probe's contact surface, and said monitoring device is operable to determine from the force applied to each unit, the orientation of the said tool with respect to the surface of patient tissue with which said is in contact.
7. The apparatus of
claim 5
, wherein said pressure transducer defines an axis of least strain along which force can be applied to the tool's head, and the transducer is responsive to force components applied along the axis and off axis.
8. The apparatus of
claim 5
, wherein said probe is movably mounted on the distal end of said tool, and the pressure transducer includes position-sensing means for sensing the position of the probe with respect to the distal end of the tool.
9. The apparatus of
claim 1
, wherein said pressure transducer includes (i) first and second conductors, (ii) an insulating layer adjacent the first conductor, said layer having perforations therein, and (iii) a conductive elastomer disposed between the insulating layer and the second conductor and in constant contact with the second conductor; wherein, during operation of the transducer, an electrical excitation signal applied to the two conductors and the impedance therebetween varies with a force applied to the contact surface of the transducer to generate an information signal indicative of whether or not the force applied to the contact surface is above a predetermined threshold, and, if so, the magnitude of the applied force.
10. The apparatus of
claim 9
, wherein said conductive elastomer temporarily flows through the perforations in the non-conductive layer and makes contact with the first conductor, when the applied force is above the predetermined threshold.
11. The apparatus of
claim 1
, wherein said monitoring device is operably connected to said activator, to activate said effector when such contact pressure is within a selected pressure range.
12. The apparatus of
claim 1
, for use in promoting angiogenesis in an under-oxygenated region of a patient's heart, wherein the accessing tool is designed to access an exterior or interior surface of such heart region from an external body site, and said effector is designed to produce an angiogenic stimulus in the myocardial layer of such region, upon activation of the effector.
13. A pressure transducer comprising
means defining a contact surface,
first and second conductors;
an insulating layer having perforations therein, the non-conductive material being adjacent to the first conductor; and
a conductive elastomer between the insulating layer and the second conductor and in constant contact with the second conductor;
wherein, during operation of the transducer, an electrical excitation signal applied to the two conductors and the impedance therebetween varies with a force applied to the contact surface of the transducer to generate an information signal indicative of (i) whether or not the force applied to the contact surface is above a predetermined threshold, and, if so, (ii) the magnitude of the applied force.
14. The transducer of
claim 13
, wherein the information signal is provided continuously and in real-time.
15. The transducer of
claim 13
, wherein the conductive elastomer temporarily flows through the perforations in the non-conductive layer and makes contact with the first conductor, when the applied force is above the predetermined threshold.
16. The transducer of
claim 15
, wherein the electrical excitation signal remains substantially unchanged when the applied force is below the predetermined threshold.
US09/816,708 2000-03-23 2001-03-23 Pressure sensor for therapeutic delivery device and method Abandoned US20010034501A1 (en)

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US10/749,327 US7211063B2 (en) 2000-03-23 2003-12-30 Pressure sensor for therapeutic delivery device and method

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Cited By (31)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050065408A1 (en) * 2003-09-18 2005-03-24 Theodore Benderev Systems and methods for determining pressure and spacing relating to anatomical structures
US20070100332A1 (en) * 2005-10-27 2007-05-03 St. Jude Medical, Atrial Fibrillation Division, Inc. Systems and methods for electrode contact assessment
US20070123764A1 (en) * 2005-10-13 2007-05-31 Chou Thao Systems and Methods For Assessing Tissue Contact
US20080015568A1 (en) * 2005-10-13 2008-01-17 Saurav Paul Dynamic contact assessment for electrode catheters
EP1962708A2 (en) * 2005-12-06 2008-09-03 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US20090125007A1 (en) * 2007-11-09 2009-05-14 Spectranetics Intra-Vascular Device With Pressure Detection Capabilities Using Pressure Sensitive Material
US20090163904A1 (en) * 2005-12-06 2009-06-25 St. Jude Medical, Atrial Fibrillation Division, Inc. System and Method for Assessing Coupling Between an Electrode and Tissue
US20090177111A1 (en) * 2006-12-06 2009-07-09 Miller Stephan P System and method for displaying contact between a catheter and tissue
US7588554B2 (en) 2000-06-26 2009-09-15 Boston Scientific Scimed, Inc. Method and apparatus for treating ischemic tissue
US20090275827A1 (en) * 2005-12-06 2009-11-05 Aiken Robert D System and method for assessing the proximity of an electrode to tissue in a body
US20100069921A1 (en) * 2006-12-06 2010-03-18 Miller Stephan P System and method for assessing lesions in tissue
US20100168735A1 (en) * 2005-12-06 2010-07-01 Don Curtis Deno System and method for assessing coupling between an electrode and tissue
US20100286690A1 (en) * 2005-12-06 2010-11-11 Saurav Paul Assessment of electrode coupling for tissue ablation
US20100298823A1 (en) * 2005-12-06 2010-11-25 Hong Cao Assessment of electrode coupling for tissue ablation
US20110118727A1 (en) * 2005-12-06 2011-05-19 Fish Jeffrey M System and method for assessing the formation of a lesion in tissue
US8187251B2 (en) 1999-06-02 2012-05-29 Boston Scientific Scimed, Inc. Methods of treating cardiac arrhythmia
US20140336453A1 (en) * 2011-05-09 2014-11-13 Japan Micro System Co., Ltd. Pressure sensor, endoscope and endoscope device
EP2445421A4 (en) * 2009-12-15 2015-06-03 St Jude Medical Atrial Fibrill Self-aiming directable acoustic transducer assembly for invasive medical device applications
US20150216612A1 (en) * 2005-03-04 2015-08-06 St. Jude Medical Luxembourg Holding S.à.r.I. Medical apparatus system having optical fiber sensing capability
US9204927B2 (en) 2009-05-13 2015-12-08 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for presenting information representative of lesion formation in tissue during an ablation procedure
US20150374449A1 (en) * 2014-06-26 2015-12-31 Covidien Lp Adapter assemblies for interconnecting electromechanical handle assemblies and surgical loading units
US9254163B2 (en) 2005-12-06 2016-02-09 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9339337B2 (en) 2008-07-21 2016-05-17 The Spectranetics Corporation Tapered liquid light guide
US20160228180A1 (en) * 2013-11-07 2016-08-11 St. Jude Medical, Cardiology Division, Inc. Medical device with contact force sensing tip
US20160270872A1 (en) * 2013-11-14 2016-09-22 Hera Med Ltd. Moveable medical device configured to operate only within a specific range of acceleration
US9492226B2 (en) 2005-12-06 2016-11-15 St. Jude Medical, Atrial Fibrillation Division, Inc. Graphical user interface for real-time RF lesion depth display
US20170095289A1 (en) * 2015-10-01 2017-04-06 General Electric Company System And Method For Representation And Visualization Of Catheter Applied Force And Power
US9855100B2 (en) 2008-04-02 2018-01-02 The Spectranetics Corporation Liquid light-guide catheter with optically diverging tip
US9949792B2 (en) 2006-12-29 2018-04-24 St. Jude Medical, Atrial Fibrillation Division, Inc. Pressure-sensitive flexible polymer bipolar electrode
US10085798B2 (en) 2006-12-29 2018-10-02 St. Jude Medical, Atrial Fibrillation Division, Inc. Ablation electrode with tactile sensor
US10350423B2 (en) 2016-02-04 2019-07-16 Cardiac Pacemakers, Inc. Delivery system with force sensor for leadless cardiac device

Families Citing this family (97)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8409167B2 (en) 2004-07-19 2013-04-02 Broncus Medical Inc Devices for delivering substances through an extra-anatomic opening created in an airway
US20030163111A1 (en) * 2002-02-26 2003-08-28 Daellenbach Keith K. End effector for needle-free injection system
US8308682B2 (en) 2003-07-18 2012-11-13 Broncus Medical Inc. Devices for maintaining patency of surgically created channels in tissue
US20050131513A1 (en) * 2003-12-16 2005-06-16 Cook Incorporated Stent catheter with a permanently affixed conductor
EP1552793B1 (en) * 2004-01-07 2007-02-28 Universite Pierre Et Marie Curie Trokar für die Durchführung eines chirurgischen Instrumentes
DE102004026307B4 (en) * 2004-05-31 2016-02-11 Novineon Healthcare Technology Partners Gmbh Tactile instrument
WO2006069257A2 (en) * 2004-12-20 2006-06-29 Stereotaxis, Inc. Contact over torque with three dimensional anatomical data
US8251907B2 (en) 2005-02-14 2012-08-28 Optiscan Biomedical Corporation System and method for determining a treatment dose for a patient
US8182433B2 (en) * 2005-03-04 2012-05-22 Endosense Sa Medical apparatus system having optical fiber load sensing capability
EP2363073B1 (en) 2005-08-01 2015-10-07 St. Jude Medical Luxembourg Holding S.à.r.l. Medical apparatus system having optical fiber load sensing capability
US20080195036A1 (en) * 2005-12-02 2008-08-14 Cabochon Aesthetics, Inc. Devices and methods for selectively lysing cells
US7967763B2 (en) 2005-09-07 2011-06-28 Cabochon Aesthetics, Inc. Method for treating subcutaneous tissues
US9358064B2 (en) 2009-08-07 2016-06-07 Ulthera, Inc. Handpiece and methods for performing subcutaneous surgery
US8518069B2 (en) 2005-09-07 2013-08-27 Cabochon Aesthetics, Inc. Dissection handpiece and method for reducing the appearance of cellulite
US20080200864A1 (en) * 2005-12-02 2008-08-21 Cabochon Aesthetics, Inc. Devices and methods for selectively lysing cells
US20080200863A1 (en) * 2005-12-02 2008-08-21 Cabochon Aesthetics, Inc. Devices and methods for selectively lysing cells
US9248317B2 (en) * 2005-12-02 2016-02-02 Ulthera, Inc. Devices and methods for selectively lysing cells
US9358033B2 (en) 2005-09-07 2016-06-07 Ulthera, Inc. Fluid-jet dissection system and method for reducing the appearance of cellulite
US20080014627A1 (en) * 2005-12-02 2008-01-17 Cabochon Aesthetics, Inc. Devices and methods for selectively lysing cells
US9486274B2 (en) 2005-09-07 2016-11-08 Ulthera, Inc. Dissection handpiece and method for reducing the appearance of cellulite
US9011473B2 (en) 2005-09-07 2015-04-21 Ulthera, Inc. Dissection handpiece and method for reducing the appearance of cellulite
CN101340943A (en) * 2005-12-23 2009-01-07 导管治疗有限公司 A pressure feedback unit for a catheter
US8567265B2 (en) 2006-06-09 2013-10-29 Endosense, SA Triaxial fiber optic force sensing catheter
US8048063B2 (en) * 2006-06-09 2011-11-01 Endosense Sa Catheter having tri-axial force sensor
JP5148092B2 (en) * 2006-09-11 2013-02-20 オリンパスメディカルシステムズ株式会社 Energy surgical device
US8282599B2 (en) * 2006-12-08 2012-10-09 Boston Scientific Scimed, Inc. Therapeutic catheter with displacement sensing transducer
US7885793B2 (en) 2007-05-22 2011-02-08 International Business Machines Corporation Method and system for developing a conceptual model to facilitate generating a business-aligned information technology solution
US8157789B2 (en) * 2007-05-24 2012-04-17 Endosense Sa Touch sensing catheter
US8622935B1 (en) 2007-05-25 2014-01-07 Endosense Sa Elongated surgical manipulator with body position and distal force sensing
WO2009023510A1 (en) * 2007-08-09 2009-02-19 Boston Scientific Scimed, Inc. Catheter devices for myocardial injections or other uses
US20100256489A1 (en) * 2007-09-28 2010-10-07 Nivasonix, Llc Handheld Transducer Scanning Speed Guides and Position Detectors
US8535308B2 (en) 2007-10-08 2013-09-17 Biosense Webster (Israel), Ltd. High-sensitivity pressure-sensing probe
US8357152B2 (en) * 2007-10-08 2013-01-22 Biosense Webster (Israel), Ltd. Catheter with pressure sensing
US20090118673A1 (en) * 2007-11-07 2009-05-07 Jerett Creed Needle injection catheter
US20090312617A1 (en) * 2008-06-12 2009-12-17 Jerett Creed Needle injection catheter
WO2009070837A1 (en) * 2007-12-07 2009-06-11 Cathrx Ltd A force feedback catheter assembly
US9717896B2 (en) 2007-12-18 2017-08-01 Gearbox, Llc Treatment indications informed by a priori implant information
US20090287120A1 (en) 2007-12-18 2009-11-19 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Circulatory monitoring systems and methods
US8636670B2 (en) 2008-05-13 2014-01-28 The Invention Science Fund I, Llc Circulatory monitoring systems and methods
US8298227B2 (en) * 2008-05-14 2012-10-30 Endosense Sa Temperature compensated strain sensing catheter
US8437832B2 (en) 2008-06-06 2013-05-07 Biosense Webster, Inc. Catheter with bendable tip
US9101734B2 (en) 2008-09-09 2015-08-11 Biosense Webster, Inc. Force-sensing catheter with bonded center strut
US20100114063A1 (en) * 2008-11-04 2010-05-06 Angiodynamics, Inc. Catheter injection monitoring device
US9326700B2 (en) 2008-12-23 2016-05-03 Biosense Webster (Israel) Ltd. Catheter display showing tip angle and pressure
US8600472B2 (en) 2008-12-30 2013-12-03 Biosense Webster (Israel), Ltd. Dual-purpose lasso catheter with irrigation using circumferentially arranged ring bump electrodes
US8475450B2 (en) * 2008-12-30 2013-07-02 Biosense Webster, Inc. Dual-purpose lasso catheter with irrigation
EP2251662A1 (en) 2009-05-05 2010-11-17 ETH Zurich Combined force and ultrasound sensor and associated method
DE102009034249A1 (en) * 2009-07-22 2011-03-24 Siemens Aktiengesellschaft A method and apparatus for controlling ablation energy to perform an electrophysiology catheter application
WO2011022665A1 (en) * 2009-08-21 2011-02-24 Regents Of The University Of Minnesota Flexible sensors and related systems for determining forces applied to an object, such as a surgical instrument
US8920415B2 (en) 2009-12-16 2014-12-30 Biosense Webster (Israel) Ltd. Catheter with helical electrode
US8374819B2 (en) * 2009-12-23 2013-02-12 Biosense Webster (Israel), Ltd. Actuator-based calibration system for a pressure-sensitive catheter
US9962217B2 (en) 2009-12-23 2018-05-08 Biosense Webster (Israel) Ltd. Estimation and mapping of ablation volume
US8521462B2 (en) 2009-12-23 2013-08-27 Biosense Webster (Israel), Ltd. Calibration system for a pressure-sensitive catheter
US8926604B2 (en) * 2009-12-23 2015-01-06 Biosense Webster (Israel) Ltd. Estimation and mapping of ablation volume
US8529476B2 (en) 2009-12-28 2013-09-10 Biosense Webster (Israel), Ltd. Catheter with strain gauge sensor
US8608735B2 (en) * 2009-12-30 2013-12-17 Biosense Webster (Israel) Ltd. Catheter with arcuate end section
US8374670B2 (en) * 2010-01-22 2013-02-12 Biosense Webster, Inc. Catheter having a force sensing distal tip
US8906013B2 (en) 2010-04-09 2014-12-09 Endosense Sa Control handle for a contact force ablation catheter
US8798952B2 (en) 2010-06-10 2014-08-05 Biosense Webster (Israel) Ltd. Weight-based calibration system for a pressure sensitive catheter
US8226580B2 (en) 2010-06-30 2012-07-24 Biosense Webster (Israel), Ltd. Pressure sensing for a multi-arm catheter
US8380276B2 (en) 2010-08-16 2013-02-19 Biosense Webster, Inc. Catheter with thin film pressure sensing distal tip
US9872981B2 (en) 2010-09-28 2018-01-23 Biotrace Medical, Inc. Device and method for positioning an electrode in a body cavity
CA2812532A1 (en) 2010-09-28 2012-04-12 The Board Of Trustees Of The Leland Stanford Junior University Device and method for positioning an electrode in tissue
US8636519B2 (en) * 2010-10-05 2014-01-28 Biosense Webster (Israel) Ltd. Simulation of an invasive procedure
US8731859B2 (en) 2010-10-07 2014-05-20 Biosense Webster (Israel) Ltd. Calibration system for a force-sensing catheter
US8979772B2 (en) 2010-11-03 2015-03-17 Biosense Webster (Israel), Ltd. Zero-drift detection and correction in contact force measurements
US8439940B2 (en) 2010-12-22 2013-05-14 Cabochon Aesthetics, Inc. Dissection handpiece with aspiration means for reducing the appearance of cellulite
CN103607961B (en) * 2011-04-14 2016-12-14 圣犹达医疗用品卢森堡控股有限公司 Compact force sensor for conduit
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
US9345532B2 (en) 2011-05-13 2016-05-24 Broncus Medical Inc. Methods and devices for ablation of tissue
US9220433B2 (en) 2011-06-30 2015-12-29 Biosense Webster (Israel), Ltd. Catheter with variable arcuate distal section
US9662169B2 (en) 2011-07-30 2017-05-30 Biosense Webster (Israel) Ltd. Catheter with flow balancing valve
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
US20140364848A1 (en) * 2011-12-29 2014-12-11 St. Jude Medical, Atrial Fibrillation Division,Inc System for optimized coupling of ablation catheters to body tissues and evaulation of lesions formed by the catheters
US9687289B2 (en) 2012-01-04 2017-06-27 Biosense Webster (Israel) Ltd. Contact assessment based on phase measurement
US9168004B2 (en) 2012-08-20 2015-10-27 Biosense Webster (Israel) Ltd. Machine learning in determining catheter electrode contact
US20140100563A1 (en) 2012-10-10 2014-04-10 Biosense Webster (Israel), Ltd. Ablation power control based on contact force
US9486272B2 (en) 2013-03-12 2016-11-08 Biosense Webster (Israel) Ltd. Force feedback device and method for catheters
US9855404B2 (en) 2013-05-03 2018-01-02 St. Jude Medical International Holding S.À R.L. Dual bend radii steering catheter
US9949664B2 (en) 2013-08-27 2018-04-24 Biosense Webster (Israel) Ltd. Determining non-contact state for a catheter
US9974608B2 (en) 2013-08-27 2018-05-22 Biosense Webster (Israel) Ltd. Determining absence of contact for a catheter
US20150126995A1 (en) 2013-11-06 2015-05-07 Biosense Webster (Israel) Ltd. Using catheter position and temperature measurement to detect movement from ablation point
WO2015138734A1 (en) * 2014-03-12 2015-09-17 Zansors Llc Wireless ecg acquisition and monitoring device and system
CN103877664B (en) * 2014-03-28 2016-03-23 上海凯旦医疗科技有限公司 There is the intravascular intervention sense of touch probe of touch range and azimuth information feedback
US9833165B2 (en) 2014-04-29 2017-12-05 Biosense Webster (Israel) Ltd. Checking for perforation of the epicardium using magnetic resonance imaging
WO2015172023A2 (en) 2014-05-09 2015-11-12 Biotrace Medical, Inc. Device and method for positioning an electrode in a body cavity
US10327744B2 (en) 2014-06-26 2019-06-25 Biosense Webster (Israel) Ltd Assistive manual zeroing visualization
CN104825234A (en) * 2015-05-15 2015-08-12 四川锦江电子科技有限公司 Detecting method and device for attaching of multi-electrode ablation catheter to heart tissue
CN106308920B (en) * 2015-06-30 2019-05-28 四川锦江电子科技有限公司 A kind of ablation catheter
US20170035357A1 (en) * 2015-08-07 2017-02-09 Boston Scientific Scimed Inc. Catheter with inductive force sensing elements
US10327859B2 (en) 2015-09-21 2019-06-25 Biosense Webster (Israel) Ltd. Catheter stability indication
US10383543B2 (en) 2015-11-11 2019-08-20 Biosense Webster (Israel) Ltd. Symmetric short contact force sensor with four coils
CN108430365A (en) * 2015-12-20 2018-08-21 波士顿科学医学有限公司 Miniature inductance formula position sensor
US20180125382A1 (en) 2016-11-09 2018-05-10 Biosense Webster (Israel) Ltd. Coils formed in folded nitinol sheet
US20180256247A1 (en) 2017-03-08 2018-09-13 Biosense Webster (Israel) Ltd. Reduced size force sensor
US20180256110A1 (en) 2017-03-08 2018-09-13 Biosense Webster (Israel) Ltd. Low cost planar spring for force sensor
WO2018163129A1 (en) * 2017-03-10 2018-09-13 St. Jude Medical International Holding S.À R.L. Apparatuses, methods, and systems for contact force sensing

Family Cites Families (96)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3773034A (en) 1971-11-24 1973-11-20 Itt Research Institute Steerable catheter
US3952742A (en) 1974-06-12 1976-04-27 Taylor Duane F Needle-carried, transthoracic, cannula-type cardiac resuscitation instrument
JPS5824921B2 (en) * 1977-12-30 1983-05-24 Shinetsu Polymer Co
US4657536A (en) 1979-04-13 1987-04-14 Regents Of The University Of Minnesota Check valve catheter
IT1165233B (en) 1979-09-25 1987-04-22 Fiat Ricerche Transducer in six degrees of freedom, particularly for robots
US4296100A (en) 1980-06-30 1981-10-20 Franco Wayne P Method of treating the heart for myocardial infarction
US4469091A (en) * 1980-08-28 1984-09-04 Slanetz Jr Charles A Tactile control device for a remote sensing device
US4531936A (en) 1981-01-29 1985-07-30 Gordon Robert T Device and method for the selective delivery of drugs to the myocardium
US4763534A (en) 1985-01-31 1988-08-16 Robert G. Fulks Pressure sensing device
US4857057A (en) 1985-06-28 1989-08-15 Olympus Optical Co., Ltd. Endoscope treatment device
US4736640A (en) 1986-08-14 1988-04-12 Hooks Mark M Compact six-degree-of-freedom motion detecting apparatus and associated methods
US4770653A (en) 1987-06-25 1988-09-13 Medilase, Inc. Laser angioplasty
US4847586A (en) * 1987-11-23 1989-07-11 Kokoku Rubber Industry Company Limited Pressure detector
JPH0256903A (en) * 1988-08-23 1990-02-26 Fine Rubber Kenkyusho:Kk Variable resistance device
US5203772A (en) 1989-01-09 1993-04-20 Pilot Cardiovascular Systems, Inc. Steerable medical device
US4904184A (en) 1989-01-17 1990-02-27 Murphy Gordon J Periodontal probe instrument
US4911148A (en) 1989-03-14 1990-03-27 Intramed Laboratories, Inc. Deflectable-end endoscope with detachable flexible shaft assembly
US5698531A (en) 1989-03-31 1997-12-16 The Regents Of The University Of Michigan Treatment of diseases by site-specific instillation of cells or site-specific transformation of cells and kits therefor
US4994033A (en) 1989-05-25 1991-02-19 Schneider (Usa) Inc. Intravascular drug delivery dilatation catheter
US5061273A (en) 1989-06-01 1991-10-29 Yock Paul G Angioplasty apparatus facilitating rapid exchanges
US5499971A (en) 1990-06-15 1996-03-19 Cortrak Medical, Inc. Method for iontophoretically delivering drug adjacent to a heart
US5885272A (en) 1990-10-30 1999-03-23 Aita; Michael System and method for percutaneous myocardial revascularization
US5339799A (en) * 1991-04-23 1994-08-23 Olympus Optical Co., Ltd. Medical system for reproducing a state of contact of the treatment section in the operation unit
US5185004A (en) 1991-06-03 1993-02-09 Danforth Biomedical, Inc. Turn-limiting proximal adaptor for steerable catheter systems
SE468516B (en) 1991-06-14 1993-02-01 Kabigen Ab Novel polypeptides which can be extracted FROM the small intestine and their anvaendning
US5661133B1 (en) 1991-11-12 1999-06-01 Univ Michigan Collateral blood vessel formation in cardiac muscle by injecting a dna sequence encoding an angiogenic protein
US5244460A (en) 1991-11-27 1993-09-14 The United States Of America As Represented By The Department Of Health And Human Services Method to foster myocardial blood vessel growth and improve blood flow to the heart
JPH0758234B2 (en) 1992-04-16 1995-06-21 株式会社エニックス Semiconductor matrix type fine surface pressure distribution sensor
AU682003B2 (en) 1992-06-26 1997-09-18 Schneider (Usa) Inc. Catheter with expandable wire mesh tip
US5507724A (en) 1992-07-01 1996-04-16 Genetronics, Inc. Electroporation and iontophoresis apparatus and method for insertion of drugs and genes into cells
US5526703A (en) 1992-08-21 1996-06-18 Smiths Industries Aerospace & Defense Systems, Inc. Force detecting sensor and method of making
US5431064A (en) 1992-09-18 1995-07-11 Home Row, Inc. Transducer array
US5341687A (en) 1992-11-16 1994-08-30 The Goodyear Tire & Rubber Company 3-dimensional pressure sensor
US6161543A (en) 1993-02-22 2000-12-19 Epicor, Inc. Methods of epicardial ablation for creating a lesion around the pulmonary veins
US6311692B1 (en) 1996-10-22 2001-11-06 Epicor, Inc. Apparatus and method for diagnosis and therapy of electrophysiological disease
US5797960A (en) 1993-02-22 1998-08-25 Stevens; John H. Method and apparatus for thoracoscopic intracardiac procedures
US5571215A (en) 1993-02-22 1996-11-05 Heartport, Inc. Devices and methods for intracardiac procedures
US6237605B1 (en) 1996-10-22 2001-05-29 Epicor, Inc. Methods of epicardial ablation
US5414940A (en) 1993-05-19 1995-05-16 Hughes Aircraft Company Contact position sensor using constant contact force control system
US5645531A (en) * 1993-05-26 1997-07-08 Quest Medical, Inc. Constant pressure blood mixture delivery system and method
US5840031A (en) 1993-07-01 1998-11-24 Boston Scientific Corporation Catheters for imaging, sensing electrical potentials and ablating tissue
EP0706345B1 (en) 1993-07-01 2003-02-19 Boston Scientific Limited Imaging, electrical potential sensing, and ablation catheters
EP0888150B1 (en) 1996-01-08 2004-03-24 Biosense Inc. Apparatus for myocardial revascularization
US5385148A (en) 1993-07-30 1995-01-31 The Regents Of The University Of California Cardiac imaging and ablation catheter
US5467762A (en) 1993-09-13 1995-11-21 United States Surgical Corporation Optical trocar
US5396887A (en) * 1993-09-23 1995-03-14 Cardiac Pathways Corporation Apparatus and method for detecting contact pressure
US5403283A (en) 1993-10-28 1995-04-04 Luther Medical Products, Inc. Percutaneous port catheter assembly and method of use
DE4408108A1 (en) 1994-03-10 1995-09-14 Bavaria Med Tech A catheter for injecting a fluid or a Arneimittelns
JP2536446B2 (en) 1994-04-05 1996-09-18 日本電気株式会社 The power of detection and display apparatus
US5553500A (en) 1994-10-26 1996-09-10 Bonneville Scientific Incorporated Triaxial normal and shear force sensor
US5604314A (en) 1994-10-26 1997-02-18 Bonneville Scientific Incorporated Triaxial normal and shear force sensor
US5520188A (en) 1994-11-02 1996-05-28 Focus Surgery Inc. Annular array transducer
US5830993A (en) 1995-04-10 1998-11-03 Kansas State University Research Foundation Synthetic antimicrobial peptide
US5695859A (en) * 1995-04-27 1997-12-09 Burgess; Lester E. Pressure activated switching device
US5797870A (en) 1995-06-07 1998-08-25 Indiana University Foundation Pericardial delivery of therapeutic and diagnostic agents
US5840059A (en) 1995-06-07 1998-11-24 Cardiogenesis Corporation Therapeutic and diagnostic agent delivery
US5827216A (en) 1995-06-07 1998-10-27 Cormedics Corp. Method and apparatus for accessing the pericardial space
US5857464A (en) 1995-06-07 1999-01-12 Desai; Jawahar M. Catheter for media injection
US6224584B1 (en) 1997-01-14 2001-05-01 Eclipse Surgical Technologies, Inc. Therapeutic and diagnostic agent delivery
US5693029A (en) 1995-07-10 1997-12-02 World Medical Manufacturing Corporation Pro-cell intra-cavity therapeutic agent delivery device
US5591195A (en) 1995-10-30 1997-01-07 Taheri; Syde Apparatus and method for engrafting a blood vessel
US5840062A (en) 1995-11-08 1998-11-24 Gumaste; Anand V. Solid state fluid delivery system
US5843050A (en) 1995-11-13 1998-12-01 Micro Therapeutics, Inc. Microcatheter
US5733280A (en) 1995-11-15 1998-03-31 Avitall; Boaz Cryogenic epicardial mapping and ablation
US5860953A (en) 1995-11-21 1999-01-19 Catheter Imaging Systems, Inc. Steerable catheter having disposable module and sterilizable handle and method of connecting same
PL183728B1 (en) * 1995-12-13 2002-07-31 Sherwood Medical Company Lauer-type adapter
AU1057097A (en) 1995-12-22 1997-07-17 Beth Israel Deaconess Medical Center Localized intravascular delivery of growth factors for promotion of angiogenesis
US5989700A (en) 1996-01-05 1999-11-23 Tekscan Incorporated Pressure sensitive ink means, and methods of use
US5891133A (en) 1996-03-29 1999-04-06 Eclipse Surgical Technologies, Inc. Apparatus for laser-assisted intra-coronary transmyocardial revascularization and other applications
US5725523A (en) 1996-03-29 1998-03-10 Mueller; Richard L. Lateral-and posterior-aspect method and apparatus for laser-assisted transmyocardial revascularization and other surgical applications
US5833658A (en) 1996-04-29 1998-11-10 Levy; Robert J. Catheters for the delivery of solutions and suspensions
DE19621099C2 (en) 1996-05-24 1999-05-20 Sulzer Osypka Gmbh Device having a catheter and a pierceable from the inside into the heart wall as the high frequency needle electrode
AU3308597A (en) 1996-06-14 1998-01-07 Kriton Medical, Inc. Methods and devices for reducing angina, enhancing myocardial perfusion and increasing cardiac function
US5662124A (en) 1996-06-19 1997-09-02 Wilk Patent Development Corp. Coronary artery by-pass method
US5931831A (en) 1996-07-09 1999-08-03 Linder; Gerald S. Dual-lumen suction catheter with smaller diameter vent lumen having multiple apertures therein
US5820592A (en) 1996-07-16 1998-10-13 Hammerslag; Gary R. Angiographic and/or guide catheter
US5871495A (en) 1996-09-13 1999-02-16 Eclipse Surgical Technologies, Inc. Method and apparatus for mechanical transmyocardial revascularization of the heart
US5755714A (en) 1996-09-17 1998-05-26 Eclipse Surgical Technologies, Inc. Shaped catheter for transmyocardial revascularization
US5855577A (en) 1996-09-17 1999-01-05 Eclipse Surgical Technologies, Inc. Bow shaped catheter
US5925012A (en) 1996-12-27 1999-07-20 Eclipse Surgical Technologies, Inc. Laser assisted drug delivery
PT1491139E (en) 1997-01-03 2007-09-25 Biosense Webster Inc Bend-responsive catheter
US5993443A (en) 1997-02-03 1999-11-30 Eclipse Surgical Technologies, Inc. Revascularization with heartbeat verification
US6133233A (en) 1997-02-18 2000-10-17 Kansas State University Research Foundation Peptide modulation of reperfusion injury
US5876373A (en) 1997-04-04 1999-03-02 Eclipse Surgical Technologies, Inc. Steerable catheter
US6024703A (en) 1997-05-07 2000-02-15 Eclipse Surgical Technologies, Inc. Ultrasound device for axial ranging
US5971983A (en) 1997-05-09 1999-10-26 The Regents Of The University Of California Tissue ablation device and method of use
US5882332A (en) 1997-06-06 1999-03-16 Wijay; Bandula Drug infusion catheter and method
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
US5941845A (en) 1997-08-05 1999-08-24 Irvine Biomedical, Inc. Catheter having multiple-needle electrode and methods thereof
US6171276B1 (en) * 1997-08-06 2001-01-09 Pharmacia & Upjohn Ab Automated delivery device and method for its operation
US6179809B1 (en) 1997-09-24 2001-01-30 Eclipse Surgical Technologies, Inc. Drug delivery catheter with tip alignment
US5935063A (en) 1997-10-29 1999-08-10 Irvine Biomedical, Inc. Electrode catheter system and methods thereof
US6309370B1 (en) * 1998-02-05 2001-10-30 Biosense, Inc. Intracardiac drug delivery
WO1999039624A1 (en) * 1998-02-05 1999-08-12 Biosense Inc. Intracardiac drug delivery
US6183444B1 (en) 1998-05-16 2001-02-06 Microheart, Inc. Drug delivery module
AU4013200A (en) 1999-03-26 2000-10-16 Beth Israel Deaconess Medical Center Method for pr-39 peptide regulated stimulation of angiogenesis

Cited By (70)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8187251B2 (en) 1999-06-02 2012-05-29 Boston Scientific Scimed, Inc. Methods of treating cardiac arrhythmia
US7588554B2 (en) 2000-06-26 2009-09-15 Boston Scientific Scimed, Inc. Method and apparatus for treating ischemic tissue
US20050065408A1 (en) * 2003-09-18 2005-03-24 Theodore Benderev Systems and methods for determining pressure and spacing relating to anatomical structures
US7485099B2 (en) 2003-09-18 2009-02-03 Theodore Benderev Systems and methods for determining pressure and spacing relating to anatomical structures
US20150216612A1 (en) * 2005-03-04 2015-08-06 St. Jude Medical Luxembourg Holding S.à.r.I. Medical apparatus system having optical fiber sensing capability
US9907618B2 (en) * 2005-03-04 2018-03-06 St Jude Medical International Holding S.À R.L. Medical apparatus system having optical fiber sensing capability
US8679109B2 (en) 2005-10-13 2014-03-25 St. Jude Medical, Atrial Fibrillation Division, Inc. Dynamic contact assessment for electrode catheters
US8672936B2 (en) * 2005-10-13 2014-03-18 St. Jude Medical, Atrial Fibrillation Division, Inc. Systems and methods for assessing tissue contact
US20070123764A1 (en) * 2005-10-13 2007-05-31 Chou Thao Systems and Methods For Assessing Tissue Contact
US20080015568A1 (en) * 2005-10-13 2008-01-17 Saurav Paul Dynamic contact assessment for electrode catheters
US20070100332A1 (en) * 2005-10-27 2007-05-03 St. Jude Medical, Atrial Fibrillation Division, Inc. Systems and methods for electrode contact assessment
US8021361B2 (en) * 2005-10-27 2011-09-20 St. Jude Medical, Atrial Fibrillation Division, Inc. Systems and methods for electrode contact assessment
US20080275465A1 (en) * 2005-12-06 2008-11-06 Saurav Paul Design of Handle Set for Ablation Catheter with Indicators of Catheter and Tissue Parameters
US10182860B2 (en) 2005-12-06 2019-01-22 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US20090163904A1 (en) * 2005-12-06 2009-06-25 St. Jude Medical, Atrial Fibrillation Division, Inc. System and Method for Assessing Coupling Between an Electrode and Tissue
US20090275827A1 (en) * 2005-12-06 2009-11-05 Aiken Robert D System and method for assessing the proximity of an electrode to tissue in a body
EP1962708A4 (en) * 2005-12-06 2009-12-16 St Jude Medical Atrial Fibrill Assessment of electrode coupling for tissue ablation
US10201388B2 (en) 2005-12-06 2019-02-12 St. Jude Medical, Atrial Fibrillation Division, Inc. Graphical user interface for real-time RF lesion depth display
US20100168735A1 (en) * 2005-12-06 2010-07-01 Don Curtis Deno System and method for assessing coupling between an electrode and tissue
US20100228247A1 (en) * 2005-12-06 2010-09-09 Saurav Paul Assessment of electrode coupling of tissue ablation
US20100241117A1 (en) * 2005-12-06 2010-09-23 Saurav Paul Assessment of Electrode Coupling for Tissue Ablation
US20100286690A1 (en) * 2005-12-06 2010-11-11 Saurav Paul Assessment of electrode coupling for tissue ablation
US20100298823A1 (en) * 2005-12-06 2010-11-25 Hong Cao Assessment of electrode coupling for tissue ablation
US20110118727A1 (en) * 2005-12-06 2011-05-19 Fish Jeffrey M System and method for assessing the formation of a lesion in tissue
US9254163B2 (en) 2005-12-06 2016-02-09 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US20080300589A1 (en) * 2005-12-06 2008-12-04 Saurav Paul Assessment of Electrode Coupling for Tissue Ablation
AU2006321574B2 (en) * 2005-12-06 2012-07-19 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
WO2007067941A3 (en) * 2005-12-06 2008-11-20 St Jude Medical Atrial Fibrill Assessment of electrode coupling for tissue ablation
US8317783B2 (en) 2005-12-06 2012-11-27 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US8369922B2 (en) 2005-12-06 2013-02-05 St. Jude Medical Atrial Fibrillation Division, Inc. Method for displaying catheter electrode-tissue contact in electro-anatomic mapping and navigation system
US8406866B2 (en) 2005-12-06 2013-03-26 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing coupling between an electrode and tissue
US9610119B2 (en) 2005-12-06 2017-04-04 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing the formation of a lesion in tissue
US8449535B2 (en) 2005-12-06 2013-05-28 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing coupling between an electrode and tissue
CN103251451A (en) * 2005-12-06 2013-08-21 圣朱德医疗有限公司房颤分公司 Assessment of electrode coupling for tissue ablation
US8603084B2 (en) 2005-12-06 2013-12-10 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing the formation of a lesion in tissue
US20080281319A1 (en) * 2005-12-06 2008-11-13 Saurav Paul Assessment of Electrode Coupling For Tissue Ablation
US9271782B2 (en) 2005-12-06 2016-03-01 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling of tissue ablation
US8728077B2 (en) 2005-12-06 2014-05-20 St. Jude Medical, Atrial Fibrillation Division, Inc. Handle set for ablation catheter with indicators of catheter and tissue parameters
US8755860B2 (en) 2005-12-06 2014-06-17 St. Jude Medical, Atrial Fibrillation Division, Inc. Method for displaying catheter electrode-tissue contact in electro-anatomic mapping and navigation system
US9492226B2 (en) 2005-12-06 2016-11-15 St. Jude Medical, Atrial Fibrillation Division, Inc. Graphical user interface for real-time RF lesion depth display
US8998890B2 (en) 2005-12-06 2015-04-07 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
EP1962708A2 (en) * 2005-12-06 2008-09-03 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9283025B2 (en) 2005-12-06 2016-03-15 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US8267926B2 (en) 2005-12-06 2012-09-18 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9173586B2 (en) 2005-12-06 2015-11-03 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing coupling between an electrode and tissue
US9283026B2 (en) 2005-12-06 2016-03-15 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9339325B2 (en) 2005-12-06 2016-05-17 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing lesions in tissue
US20080288038A1 (en) * 2005-12-06 2008-11-20 Saurav Paul Method for Displaying Catheter Electrode-Tissue Contact in Electro-Anatomic Mapping and Navigation System
US10362959B2 (en) 2005-12-06 2019-07-30 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing the proximity of an electrode to tissue in a body
US8403925B2 (en) 2006-12-06 2013-03-26 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing lesions in tissue
US20100069921A1 (en) * 2006-12-06 2010-03-18 Miller Stephan P System and method for assessing lesions in tissue
US20090177111A1 (en) * 2006-12-06 2009-07-09 Miller Stephan P System and method for displaying contact between a catheter and tissue
US10085798B2 (en) 2006-12-29 2018-10-02 St. Jude Medical, Atrial Fibrillation Division, Inc. Ablation electrode with tactile sensor
US9949792B2 (en) 2006-12-29 2018-04-24 St. Jude Medical, Atrial Fibrillation Division, Inc. Pressure-sensitive flexible polymer bipolar electrode
US9289173B2 (en) 2007-11-09 2016-03-22 The Spectranetics Corporation Intra-vascular device with pressure detection capabilities using pressure sensitive material
US20090125007A1 (en) * 2007-11-09 2009-05-14 Spectranetics Intra-Vascular Device With Pressure Detection Capabilities Using Pressure Sensitive Material
US9066742B2 (en) * 2007-11-09 2015-06-30 The Spectranetics Corporation Intra-vascular device with pressure detection capabilities using pressure sensitive material
US9855100B2 (en) 2008-04-02 2018-01-02 The Spectranetics Corporation Liquid light-guide catheter with optically diverging tip
US10092357B2 (en) 2008-07-21 2018-10-09 The Spectranetics Corporation Tapered liquid light guide
US9339337B2 (en) 2008-07-21 2016-05-17 The Spectranetics Corporation Tapered liquid light guide
US9204927B2 (en) 2009-05-13 2015-12-08 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for presenting information representative of lesion formation in tissue during an ablation procedure
EP2445421A4 (en) * 2009-12-15 2015-06-03 St Jude Medical Atrial Fibrill Self-aiming directable acoustic transducer assembly for invasive medical device applications
US9907534B2 (en) 2009-12-15 2018-03-06 St. Jude Medical, Atrial Fibrillation Division, Inc. Self-aiming directable acoustic transducer assembly for invasive medical device applications
US20140336453A1 (en) * 2011-05-09 2014-11-13 Japan Micro System Co., Ltd. Pressure sensor, endoscope and endoscope device
US20160228180A1 (en) * 2013-11-07 2016-08-11 St. Jude Medical, Cardiology Division, Inc. Medical device with contact force sensing tip
US20160270872A1 (en) * 2013-11-14 2016-09-22 Hera Med Ltd. Moveable medical device configured to operate only within a specific range of acceleration
US9987095B2 (en) * 2014-06-26 2018-06-05 Covidien Lp Adapter assemblies for interconnecting electromechanical handle assemblies and surgical loading units
US20150374449A1 (en) * 2014-06-26 2015-12-31 Covidien Lp Adapter assemblies for interconnecting electromechanical handle assemblies and surgical loading units
US20170095289A1 (en) * 2015-10-01 2017-04-06 General Electric Company System And Method For Representation And Visualization Of Catheter Applied Force And Power
US10350423B2 (en) 2016-02-04 2019-07-16 Cardiac Pacemakers, Inc. Delivery system with force sensor for leadless cardiac device

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US7211063B2 (en) 2007-05-01
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US20030130615A1 (en) 2003-07-10
US20040225298A1 (en) 2004-11-11
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US6695808B2 (en) 2004-02-24

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