WO2002058549A1 - Implant endoluminal extensible à ensemble de capteurs intégré - Google Patents

Implant endoluminal extensible à ensemble de capteurs intégré Download PDF

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Publication number
WO2002058549A1
WO2002058549A1 PCT/DE2002/000234 DE0200234W WO02058549A1 WO 2002058549 A1 WO2002058549 A1 WO 2002058549A1 DE 0200234 W DE0200234 W DE 0200234W WO 02058549 A1 WO02058549 A1 WO 02058549A1
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WO
WIPO (PCT)
Prior art keywords
film
electrodes
implant
electronics
semiconductor chip
Prior art date
Application number
PCT/DE2002/000234
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German (de)
English (en)
Inventor
Hagen Thielecke
Andrea Robitzki
Alexandra REININGER-MACK
Thomas Stieglitz
Oliver Scholz
Karl Konstantin Haase
Tim SÜSELBECK
Original Assignee
Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V.
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Publication of WO2002058549A1 publication Critical patent/WO2002058549A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6867—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive specially adapted to be attached or implanted in a specific body part
    • A61B5/6876—Blood vessel
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0031—Implanted circuitry
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/02007—Evaluating blood vessel condition, e.g. elasticity, compliance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6862—Stents

Definitions

  • the present invention relates to an endoluminal expandable implant, in particular a stent, made of a cylindrical, radially expandable implant body, which is at least largely enclosed on its inner or outer circumference by a flexible film, in which sensor elements and a thinned semiconductor chip with integrated
  • the implant can in particular be designed as a stent, the integrated sensor technology of which provides data for risk stratification, for therapy control and, if appropriate, for controlling a controlled release of active substance in the body.
  • PTCA percutaneous transluminal coronary balloon angoplasty
  • an expandable balloon is inserted into the vessel and inflated there for a certain period of time so that it expands the vessel at this point.
  • An essential limitation of the PTCA is the occurrence of a relapse stenosis within a period of 3-6 months after the intervention. The occurrence of a relapse stenosis is essentially due to the following factors. Very early after balloon dilatation, the elastic bevels in the vessel wall perform a return movement that reduces the vessel lumen that was initially reached.
  • the mechanism of balloon dilation also leads to severe damage to the endotelial cell layer, which results in unmasking of the subendothelial localized vascular wall structures.
  • Thrombocytic adhesion, thrombocytic aggregation, further platelet activation and thrombus formation are consequences of this vascular wall injury.
  • Activated platelets lead to the activation of proliferation-active cell systems through the release of growth factors, but on the other hand they can also result in early complications of PTCA, the thrombotic vascular occlusion, by promoting thrombus formation.
  • the compression and dissection of the stenosing plaque caused by the expansion of the balloon leads to a proliferation of smooth muscle cells in the media. These smooth muscle cells migrate from the media into the intima and cause a further, so-called late lumen loss, several weeks after the initial balloon expansion.
  • vascular prostheses are implanted either after prior balloon expansion of the vessel or directly via a balloon dilatation catheter.
  • the stent consists of a cylindrical, radially expandable implant body which supports the expanded vessel lumen after the implantation and, if appropriate, subsequent radial expansion.
  • the reduction in the incidence of restenosis after stent placement is essentially explained by an additional lumen gain.
  • the implanted stent Parallel to this endothelial lining of the vessel lumen, the implanted stent induces a proliferation stimulus on the vessel wall and leads to a lumen reduction in this area, which in some of the treated patients can lead to focal or diffuse, the entire stent length regarding in-stent stenosis. Due to non-invasive parameters, it is currently not possible to carry out a secure risk stratification that allows individual predictability for the development of restenosis after stent implantation.
  • stents with integrated sensors are currently known, which are designed to measure flow parameters.
  • the measured values acquired via the sensors are transmitted wirelessly to a receiver outside the vessel in which the stent is implanted or outside the body.
  • No. 6,053,873 shows such a stent with integrated electronics and sensors for flow measurement.
  • An elastic coil is placed around the stent, which serves as an antenna for data transmission and for energy consumption for the operation of the electronics.
  • the publication shows an embodiment of a stent in which the impedance of the blood flowing through the stent lumen is detected and for determining the Flow rate is used.
  • a plurality of axially spaced-apart electrode pairs, each of electrodes lying opposite one another, are arranged together with the electronics in a thin flexible film which is attached to the stent.
  • the stent of US Pat. No. 6,053,873 cannot be used for safe risk stratification, since knowledge of the proliferation parameters is necessary for this. These cannot be reliably determined from the measured flow parameters.
  • US 5,967,986 also describes a stent with integrated electronics and sensors for measuring various physical or biological parameters, in particular for flow measurement.
  • two electrodes run approximately helically along the length of the stent at a constant distance, via which tissue growth in the stent can be detected.
  • the sensors or electrodes as well as the associated electronics are arranged on a thin flexible film, which for the most part encloses the stent on its inner surface.
  • the invention has for its object an endoluminal expandable implant with integrated sensor technology, in particular a stent, which enables safe risk stratification after implantation.
  • the present endoluminal expandable implant hereinafter also referred to as a stent according to the preferred embodiment, consists in a known manner of a cylindrical, radially expandable implant body.
  • the structure of such an implant body is known to the person skilled in the art.
  • the implant body is at least largely enclosed on its inner or outer circumference by a thin and flexible first film.
  • Sensor elements, a thinned semiconductor chip with integrated electronics and conductor tracks for connecting the integrated electronics to the sensor elements are arranged in the film.
  • the film is attached to the implant body in a suitable manner.
  • the first film with the integrated sensor elements and the semiconductor chip is designed to be stretchable, so that it can follow a radial expansion of the implant at any time.
  • the sensor elements are formed by a multiplicity of first electrodes arranged in an array-like manner distributed over the film surface.
  • the integrated electronics is for
  • conductor tracks which produce an electrical connection transversely to the longitudinal axis or axial direction of the implant body on the first film, are optionally formed from an expandable material and / or run in a meandering shape. If the electrodes and the at least one semiconductor chip are arranged in such a way that no electrical connections transverse to the longitudinal axis of the implant body on the first film are required, the latter measure is of course not necessary.
  • this implant which is preferably designed as a stent
  • a plurality of electrodes preferably at least 6 electrodes, are thus arranged on the first film in such a way that they are coated with the tissue or plaque material that surrounds the inner or outer wall of the stent , have electrical contact.
  • the electrodes are electrically connected to the electronics of the semiconductor chip, which drives the electrodes to record the spatially resolved impedance spectra.
  • the electronics are preferably for evaluation and / or transmission of the detected ones
  • the impedance spectra are arranged at different locations of the stent between them.
  • Electrodes added. From the impedance spectra of a pair of electrodes, the parameters of the tissue or plaque material can be determined, which are between the ⁇ co 4-> TJ g ⁇ ⁇ ß co N ß ⁇ ) ⁇ ⁇ -H ⁇ ⁇ o 4-> ⁇ rd 4-) 3 ß 4J ß -ä 1 J ⁇ s 4-1 rH o rd ⁇ l T ß ß ⁇ -rl ß. i3 1 ⁇ rH
  • the stent can be implanted in a conventional manner and expanded within the vessel without endangering the electronic components and the measurement properties.
  • a second thin film is provided, which optionally bears against the first film via a thin intermediate layer.
  • the second film is designed to be elastic and stretchable.
  • the second film carries a capacitor array and conductor tracks for connecting the capacitors of the capacitor array to one another and connects the capacitor array via an electrical contact to the first film for energy supply with the electronics of the semiconductor chip.
  • the conductor tracks on the second film which establish an electrical connection transversely, in particular perpendicularly, to the longitudinal axis of the implant body, are formed from an expandable material and / or run in a meandering shape.
  • This second film with the capacitor array provides an energy store which stores the energy which may be transmitted wirelessly from an external energy source or which is obtained by internal energy conversion and, if required, makes it available to the electronics of the semiconductor chip.
  • the second film like the first film, is designed to be electrically insulating and carries a multiplicity of microcapacitors which are connected to one another by the conductor tracks.
  • the dimensions of the implant with the two foils differ only insignificantly from a conventional implant without due to the small thickness of the foils integrated sensors.
  • Such a capacitor array, the capacitors of which are distributed over the full inner or outer surface of the stent enables a high storage capacity without noticeably reducing the lumen of the stent.
  • this energy storage enables reliable operation of the integrated electronics. Due to the stretchable configuration of the second film and the stretchability of the conductor tracks due to the special material or meandering course, the stent can be expanded in the usual way after the implantation.
  • the electrical components arranged in the second film i.e. the capacitor array and the conductor tracks can, for the same purpose, also be integrated directly in the first film and can be electrically insulated from the other components of the first film. In such an embodiment, no separate second film is required, but only a layer-like structure of the first film.
  • the substrate film (first film) of the electrode array consists of a piezoelectric material.
  • Second electrodes for example as a correspondingly structured electrode layer, are arranged on both sides of this film. These electrodes are separated from the first electrodes thereon, the sensor elements, by an insulation layer.
  • This configuration enables a continuous power supply and thus continuous monitoring to be implemented independently of external energy sources. Due to pressure changes inside the stent, for example as a result of the pulse beat, the piezoelectric film is stretched, so that a change in the voltage between the second electrodes of the two film sides results. The converted energy is stored in the capacitor array after an AC / DC conversion or is used directly to supply energy to the semiconductor electronics.
  • the energy is also managed by the electronics integrated in the semiconductor chip.
  • the second electrodes which extend perpendicular to the longitudinal axis of the implant body, ie in the direction of expansion, are in turn either designed to be stretchable and / or run in a meandering manner in this direction.
  • the first electrodes are preferably arranged on the first film in such a way that they are equidistant after the intended expansion of the stent. This enables a simplified evaluation of the measurement data with regard to the spatial distribution of the tissue parameters.
  • the person skilled in the art knows the relationships for deriving these parameters from the spectral impedance measurements. The result of this is that biological tissues have characteristic electrical and dielectric properties that can be determined using impedance spectroscopy.
  • a semiconductor chip with an approximately rectangular shape is preferably applied or integrated into the first film, which has a greater longitudinal than transverse dimension.
  • the semiconductor chip is oriented on the film in such a way that its longitudinal axis runs approximately parallel to the longitudinal axis of the implant body. This will create a Stress on the semiconductor chip is minimized by stretching the film transversely to the axial direction. If necessary, the stretchability of this film in the region of the semiconductor chip can also be reduced.
  • all electrodes lie on the film in each case on straight lines running parallel to the longitudinal axis of the implant body, a separate semiconductor chip with integrated electronics for controlling the electrodes on the respective line being provided for each of the lines.
  • a separate semiconductor chip with integrated electronics for controlling the electrodes on the respective line being provided for each of the lines.
  • All conductor tracks run parallel to the longitudinal axis of the implant, so that the electrical components are not stressed by an expansion of the film due to the expansion of the implant.
  • the electronics are preferably designed to evaluate and / or transmit measurement data to an external unit.
  • a transmitting and receiving coil is wound helically or double helically around the implant body and connected to the electronics.
  • the electronics can furthermore have outputs for controlling a microsystem, optionally arranged on the implant body, for releasing the active substance.
  • a microsystem for drug release is disclosed in the parallel German patent application 100 63 612.8, the design features of which are preferably also implemented in the present implant.
  • the electronics include Here is a program that controls the release of the active ingredient depending on the measured parameters.
  • the microsystem of 100 63 612.8 which is arranged above an active substance reservoir which is preferably integrated in the implant, consists of a thin carrier substrate which consists of a material impermeable to the active substance and has one or more through openings for the active substance.
  • a plurality of electrodes are arranged in the area of the through openings and are controlled via electronics integrated in the carrier substrate or directly via the electronics in the present first film.
  • the through openings are designed as microgaps and / or microchannels, each with electrodes arranged on both sides, and covered on one side of the carrier substrate by a layer of an electroporous material.
  • a second stent body is arranged coaxially around the first stent body, the first and optionally second film lying between the two stent bodies.
  • the inner stent body is expanded in such a way that it is pressed against the outer stent body, so that the entire system is under mechanical tension.
  • the first and optionally the second film are preferably perforated.
  • these foils can be provided with a layer that is under tensile stress, so that the foils are always on the surface due to the tensile stress of the implant body. It goes without saying that the direction of the tensile stress must be selected appropriately for this, depending on whether the film is applied to the inner or the outer circumference of the stent body.
  • widened sensor elements can also be arranged on the first film and connected to the electronics in order to be able to detect further biological or physical parameters if necessary.
  • Fig. 1 shows a schematic representation of a
  • Fig. 2 is a schematic representation of a flexible, stretchable film with an electrode array and integrated
  • FIG. 3 shows a schematic illustration of a flexible and stretchable film with a stretchable capacitor array
  • Fig. 4 is a block diagram of the integrated
  • FIG. 5 is a schematic representation of a
  • FIG. 6a shows an example of a piezoelectric film for energy conversion in a top view
  • FIG. 6b shows a schematic sectional illustration of a sensor structure with a piezoelectric film according to FIG. 6a as substrate material
  • Fig. 7 shows an example of an arrangement of the
  • Electrodes, conductor tracks and IC's on a stretchable film Electrodes, conductor tracks and IC's on a stretchable film
  • FIG. 8 shows an example of a stent with an applied sensor system that is under internal stress before and after radial stent expansion.
  • FIG. 1 schematically shows an illustration of a possible embodiment of a stent with integrated sensors for continuously recording the spatial distribution of tissue and plaque parameters after implantation of the stent.
  • the stent has a radially expandable cylindrical stent body 1, on the outer surface of which, in this example, a stretchable, flexible thin film 2 is applied, which carries an electrode array, an integrated circuit and conductor tracks.
  • a second flexible and stretchable film 3 is applied, which is a microcapacitor array with conductor tracks for the corresponding connection of the individual capacitors wearing.
  • the individual electrodes 4 of the electrode array of the film 2 which come into contact with tissue growing into the stent, can be seen very well in the figure.
  • the stent itself is constructed in the usual way and consists, for example, of a wire mesh.
  • the two foils 2 and 3 enclose the stent body 1 almost completely in this example.
  • the attachment to the stent body and the connection between the foils can be carried out using adhesives known to the person skilled in the art.
  • the two films applied expand in the same way as the stent, without damaging the electrical components which are integrated in or on the films.
  • a flexible, elastic electrode array i. H. the first film 2 with the electrode array of the electrodes 4, 2 metal layers for the electrodes 4 and conductor tracks 5 are deposited and structured on an elastomer film.
  • An ultra-thin flexible silicon chip 6 is produced using semiconductor technology and is connected to the elastomer film 2 by a known connection technology for flexible chips on flexible substrates.
  • the chip 6 is designed as a narrow rectangle and is preferably applied to the electrode substrate 2 such that the edges of the narrow sides of the rectangle lie in the direction in which the electrode substrate 2 is stretched when the stent body 1 expands.
  • FIG. 2 shows a schematic representation of an example of an electrode array applied to a film 2 with associated conductor tracks 5 and the semiconductor chip 6.
  • the film 2 is an elastic and electrically non-conductive elastomer film which can be stretched at least in one direction (indicated by the arrows).
  • the exposed electrodes 4 of the electrode array can be seen on the film and are connected via conductor tracks 5 to the semiconductor chip 6, which controls the electrodes.
  • the extensibility of the film 2 in the region in which the chip 6 is located can be reduced. This can vary depending
  • Elastomer material can be achieved, for example, by local light or heat treatment (e.g. using a laser).
  • the electrodes 4 are arranged so that they are equidistant after stent expansion. Furthermore, the conductor tracks 5, in areas in which they extend in the direction of expansion of the film 2, are meandering. This meandering course of the conductor tracks 5 enables the film 2 to be stretched in the specified direction without the conductor tracks 5 being damaged or interrupted thereby. The meandering course thus enables an elastic electrical connection of the electrodes 4 to the Semiconductor chip 6. Connections 7 for a system for drug release and connections 8 for supplying energy to semiconductor chip 6 can also be seen in the figure.
  • the semiconductor chip 6 has electronics or an integrated circuit (IC) which controls the electrodes 4 of the electrode array for impedance spectroscopic measurement. The control takes place in such a way that a spatially resolved measurement of the impedance is achieved as a function of the wavelength.
  • IC integrated circuit
  • the number of electrodes in this and the other examples can also be increased further, in order, for. B. to achieve a certain spatial resolution or to cover a larger area.
  • FIG. 4 An example of a block diagram of the integrated circuit is shown in FIG. 4.
  • the multiplexers each connect two adjacent electrodes 4 of a longitudinal axis with impedance analyzers, which determine impedance spectra for the electrode pairs.
  • the impedance spectra are either written into a memory located on chip 6 via a control circuit or sent telemetrically to a receiving unit outside the vessel.
  • An analysis circuit can be used to determine events from the impedance spectra in which control signals are sent to a system for the controlled release of active substance.
  • the circuit receives the energy inductively from an external energy source and / or from energy converters, which are located on the stent.
  • the energy is buffered in a capacitor array. Energy is taken from the capacitor array to operate the circuit.
  • the energy management is carried out by a power management module that is integrated in the semiconductor chip 6.
  • FIG. 3 shows an example of a film 3 with an array of metallized film capacitors 9.
  • the film 3 again consists of an elastomer substrate on which the film capacitors 9 are produced by combined deposition and structuring of metal and polymer layers.
  • Concepts for the deposition of materials for the production of monolithic film capacitors are described, for example, in Rzad et al. .
  • the individual film capacitors 9 are connected or connected to one another via conductor tracks 10 made of an elastic, electrically conductive material, preferably a polymer material.
  • the connections 11 of the capacitor array are connected to the connections for the energy storage on the film 2 with the electrode array.
  • the foils 2, 3 for the electrode and capacitor array are then placed together around the stent body 1.
  • a thin wire is wound around the stent with the sensor system in the form of a double helix, whereby a transmitting and receiving coil is formed. The ends of the coil are connected to the corresponding inputs on the semiconductor chip 6.
  • a separate integrated circuit (6a-6d) is used for the electrodes 4, which are located on a line or axis parallel to the longitudinal axis of the stent body 1, for control and data acquisition.
  • This arrangement makes it possible to dispense with stretchable conductor tracks within the electrode structure or to reduce the number thereof.
  • the ICs (6a - 6d) of each axis are connected, for example, to a common transmitting and receiving coil and communicate with an external unit.
  • Figure 7 shows one
  • FIG. 8 finally shows schematically an example of a stent in which the sensor system 18, consisting of the film 2 with the electrode array and optionally a further film with the capacitor array, is provided with a layer which is under tensile stress. This layer is deposited on the film 2 during the manufacture of the electrode array.
  • the film itself takes on a cuff shape.
  • the cuff is widened or compressed and placed around a stent body 1 or pushed into a stent body 1.
  • a cuff 18 (sensor system) pushed over the stent body 1 can be seen in the example in FIG. 8a.
  • the sensor system is stuck on the stent body due to its inherent tension.
  • the applied layer must of course cause an external tension.
  • the cuff expands, as can be seen in partial illustration b of FIG. 8. Due to the inherent tension, however, the cuff still lies securely on the stent body.
  • the electrodes are arranged in this sensor system so that they have the desired position in the expanded state.
  • detectors for tissue or plaque characterization can of course also be arranged on the film or films. It is also possible to arrange additional sensors for other biological or physical parameters. In this case, the electronics of the Semiconductor chips can be adapted accordingly to the measurement tasks.
  • both the capacitor array and the electrode array can be arranged on a common film, which can additionally consist of a piezoelectric material with corresponding electrodes for reducing the voltage.
  • the piezoelectric film, a film for the electrode array and a film for the capacitor array can also be used separately.
  • the arrangement of the electrodes of the electrode array is not restricted to specific patterns or distances. Rather, they depend on the desired spatial resolution.
  • the interconnection of the individual electrodes for recording the impedance spectra can be carried out in different ways, as is known to the person skilled in the art. Both two-pole, three-pole and four-pole arrangements are suitable for such a task.
  • Stent body first stretchable film second stretchable film first electrodes first conductor tracks semiconductor chip connections for a system for drug release connections for a system for energy supply film capacitor second conductor tracks connection surface second stent body piezoelectric film second electrodes connection surface rear connection surface front side passivation layer sensor system

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Abstract

Implant endoluminal extensible à ensemble de capteurs intégré, en particulier stent. Le corps (1) de stent est entouré, au moins dans sa plus grande partie, sur sa périphérie interne ou externe, d'une feuille (2) souple et extensible. Ladite feuille (2) contient une pluralité d'électrodes (4) disposées de manière ordonnée, une puce à semi-conducteur (6) doté d'un système électronique intégré et des pistes conductrices (5) destinées à connecter le système électronique intégré (6) aux électrodes (4). Le système électronique intégré (6) est conçu pour commander les électrodes (4) en vue de la réception de spectres d'impédance afin d'obtenir des spectres d'impédance à résolution spatiale sur la surface de la feuille (2). Les pistes conductrices (5) qui créent une connexion électrique transversalement par rapport au corps (1) d'implant sur la feuille sont constituées d'une matière extensible et / ou présentent un parcours à méandres. Ledit implant, qui peut être implanté et étendu de manière classique, livre des paramètres de prolifération en vue d'une classification sure des risques.
PCT/DE2002/000234 2001-01-26 2002-01-24 Implant endoluminal extensible à ensemble de capteurs intégré WO2002058549A1 (fr)

Applications Claiming Priority (2)

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DE10103503.9 2001-01-26
DE2001103503 DE10103503A1 (de) 2001-01-26 2001-01-26 Endoluminales expandierbares Implantat mit integrierter Sensorik

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Cited By (25)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1865870A2 (fr) * 2005-03-28 2007-12-19 Minnow Medical, LLC Caracterisation de tissu electrique intraluminal et energie rf accordee destinee au traitement selectif d'atherome et d'autres tissus cibles
WO2009136167A1 (fr) * 2008-05-07 2009-11-12 University Of Strathclyde Système de caractérisation ou de surveillance de dispositifs implantés
DE102008045876A1 (de) 2008-09-06 2010-03-11 Robert Prof. Bauernschmitt Implantierbare medizinische Vorrichtung mit einer Gitterstruktur sowie Verfahren zum Herstellen und Verwenden derselben
WO2012048907A1 (fr) * 2010-10-15 2012-04-19 Fraunhofer-Gesellschaft Zur Förderung Der Angewandten Forschung E.V. . Système de détection destiné à être implanté dans un corps et procédé de fabrication du système de détection
US8396548B2 (en) 2008-11-14 2013-03-12 Vessix Vascular, Inc. Selective drug delivery in a lumen
US8401667B2 (en) 2008-11-17 2013-03-19 Vessix Vascular, Inc. Selective accumulation of energy with or without knowledge of tissue topography
US8496653B2 (en) 2007-04-23 2013-07-30 Boston Scientific Scimed, Inc. Thrombus removal
US8551096B2 (en) 2009-05-13 2013-10-08 Boston Scientific Scimed, Inc. Directional delivery of energy and bioactives
US8920414B2 (en) 2004-09-10 2014-12-30 Vessix Vascular, Inc. Tuned RF energy and electrical tissue characterization for selective treatment of target tissues
US9125666B2 (en) 2003-09-12 2015-09-08 Vessix Vascular, Inc. Selectable eccentric remodeling and/or ablation of atherosclerotic material
US9125667B2 (en) 2004-09-10 2015-09-08 Vessix Vascular, Inc. System for inducing desirable temperature effects on body tissue
US9277955B2 (en) 2010-04-09 2016-03-08 Vessix Vascular, Inc. Power generating and control apparatus for the treatment of tissue
US9636174B2 (en) 2002-04-08 2017-05-02 Medtronic Ardian Luxembourg S.A.R.L. Methods for therapeutic renal neuromodulation
US9713483B2 (en) 1995-10-13 2017-07-25 Medtronic Vascular, Inc. Catheters and related devices for forming passageways between blood vessels or other anatomical structures
US9814873B2 (en) 2002-04-08 2017-11-14 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for bilateral renal neuromodulation
EP3292885A1 (fr) 2016-09-06 2018-03-14 BIOTRONIK SE & Co. KG Système de conducteur d'électrode élastique et implant médical
US9919144B2 (en) 2011-04-08 2018-03-20 Medtronic Adrian Luxembourg S.a.r.l. Iontophoresis drug delivery system and method for denervation of the renal sympathetic nerve and iontophoretic drug delivery
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US9974607B2 (en) 2006-10-18 2018-05-22 Vessix Vascular, Inc. Inducing desirable temperature effects on body tissue
US10034708B2 (en) 2002-04-08 2018-07-31 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for thermally-induced renal neuromodulation
US10124195B2 (en) 2002-04-08 2018-11-13 Medtronic Ardian Luxembourg S.A.R.L. Methods for thermally-induced renal neuromodulation
US10130792B2 (en) 2002-04-08 2018-11-20 Medtronic Ardian Luxembourg S.A.R.L. Methods for therapeutic renal neuromodulation using neuromodulatory agents or drugs
US10350004B2 (en) 2004-12-09 2019-07-16 Twelve, Inc. Intravascular treatment catheters
WO2020114871A1 (fr) * 2018-12-06 2020-06-11 Universiteit Gent Procédé d'intégration d'un circuit électronique à l'intérieur ou sur une endoprothèse
US11116561B2 (en) 2018-01-24 2021-09-14 Medtronic Ardian Luxembourg S.A.R.L. Devices, agents, and associated methods for selective modulation of renal nerves

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7265298B2 (en) 2003-05-30 2007-09-04 The Regents Of The University Of California Serpentine and corduroy circuits to enhance the stretchability of a stretchable electronic device
DE102004023526A1 (de) * 2004-05-13 2005-12-08 Osypka, Peter, Dr.-Ing. Gefäßstütze
DE102007034042A1 (de) * 2007-07-20 2009-01-22 Biotronik Crm Patent Ag Implantierbares medizinisches Gerät
FR3026631B1 (fr) 2014-10-03 2016-12-09 Ecole Polytech Dispositif medical implantable muni de capteurs
FR3042873A1 (fr) 2015-10-23 2017-04-28 Ecole Polytech Procede et systeme de discrimination de cellules
FR3049843A1 (fr) * 2016-04-06 2017-10-13 Instent Dispositif medical muni de capteurs
JP7349727B2 (ja) 2016-11-21 2023-09-25 センサム 生体構造の特徴づけおよび同定

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5454377A (en) * 1993-10-08 1995-10-03 The Ohio State University Method for measuring the myocardial electrical impedance spectrum
US5941869A (en) * 1997-02-12 1999-08-24 Prolifix Medical, Inc. Apparatus and method for controlled removal of stenotic material from stents
US5967986A (en) 1997-11-25 1999-10-19 Vascusense, Inc. Endoluminal implant with fluid flow sensing capability
US6053873A (en) 1997-01-03 2000-04-25 Biosense, Inc. Pressure-sensing stent

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6206914B1 (en) * 1998-04-30 2001-03-27 Medtronic, Inc. Implantable system with drug-eluting cells for on-demand local drug delivery
US6092530A (en) * 1999-03-24 2000-07-25 The B.F. Goodrich Company Remotely interrogated implant device with sensor for detecting accretion of biological matter

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5454377A (en) * 1993-10-08 1995-10-03 The Ohio State University Method for measuring the myocardial electrical impedance spectrum
US6053873A (en) 1997-01-03 2000-04-25 Biosense, Inc. Pressure-sensing stent
US5941869A (en) * 1997-02-12 1999-08-24 Prolifix Medical, Inc. Apparatus and method for controlled removal of stenotic material from stents
US5967986A (en) 1997-11-25 1999-10-19 Vascusense, Inc. Endoluminal implant with fluid flow sensing capability

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9713483B2 (en) 1995-10-13 2017-07-25 Medtronic Vascular, Inc. Catheters and related devices for forming passageways between blood vessels or other anatomical structures
US10179027B2 (en) 2002-04-08 2019-01-15 Medtronic Ardian Luxembourg S.A.R.L. Catheter apparatuses having expandable baskets for renal neuromodulation and associated systems and methods
US10124195B2 (en) 2002-04-08 2018-11-13 Medtronic Ardian Luxembourg S.A.R.L. Methods for thermally-induced renal neuromodulation
US10850091B2 (en) 2002-04-08 2020-12-01 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for bilateral renal neuromodulation
US10441356B2 (en) 2002-04-08 2019-10-15 Medtronic Ardian Luxembourg S.A.R.L. Methods for renal neuromodulation via neuromodulatory agents
US10376516B2 (en) 2002-04-08 2019-08-13 Medtronic Ardian Luxembourg S.A.R.L. Methods and devices for renal nerve blocking
US9636174B2 (en) 2002-04-08 2017-05-02 Medtronic Ardian Luxembourg S.A.R.L. Methods for therapeutic renal neuromodulation
US10179235B2 (en) 2002-04-08 2019-01-15 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for bilateral renal neuromodulation
US10130792B2 (en) 2002-04-08 2018-11-20 Medtronic Ardian Luxembourg S.A.R.L. Methods for therapeutic renal neuromodulation using neuromodulatory agents or drugs
US9814873B2 (en) 2002-04-08 2017-11-14 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for bilateral renal neuromodulation
US10034708B2 (en) 2002-04-08 2018-07-31 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for thermally-induced renal neuromodulation
US9968611B2 (en) 2002-04-08 2018-05-15 Medtronic Ardian Luxembourg S.A.R.L. Methods and devices for renal nerve blocking
US9125666B2 (en) 2003-09-12 2015-09-08 Vessix Vascular, Inc. Selectable eccentric remodeling and/or ablation of atherosclerotic material
US9510901B2 (en) 2003-09-12 2016-12-06 Vessix Vascular, Inc. Selectable eccentric remodeling and/or ablation
US10188457B2 (en) 2003-09-12 2019-01-29 Vessix Vascular, Inc. Selectable eccentric remodeling and/or ablation
US8939970B2 (en) 2004-09-10 2015-01-27 Vessix Vascular, Inc. Tuned RF energy and electrical tissue characterization for selective treatment of target tissues
US9125667B2 (en) 2004-09-10 2015-09-08 Vessix Vascular, Inc. System for inducing desirable temperature effects on body tissue
US8920414B2 (en) 2004-09-10 2014-12-30 Vessix Vascular, Inc. Tuned RF energy and electrical tissue characterization for selective treatment of target tissues
US10350004B2 (en) 2004-12-09 2019-07-16 Twelve, Inc. Intravascular treatment catheters
US11272982B2 (en) 2004-12-09 2022-03-15 Twelve, Inc. Intravascular treatment catheters
EP1865870A2 (fr) * 2005-03-28 2007-12-19 Minnow Medical, LLC Caracterisation de tissu electrique intraluminal et energie rf accordee destinee au traitement selectif d'atherome et d'autres tissus cibles
US8364237B2 (en) 2005-03-28 2013-01-29 Vessix Vascular, Inc. Tuned RF energy for selective treatment of atheroma and other target tissues and/or structures
EP1865870A4 (fr) * 2005-03-28 2009-12-16 Minnow Medical Llc Caracterisation de tissu electrique intraluminal et energie rf accordee destinee au traitement selectif d'atherome et d'autres tissus cibles
US9974607B2 (en) 2006-10-18 2018-05-22 Vessix Vascular, Inc. Inducing desirable temperature effects on body tissue
US10213252B2 (en) 2006-10-18 2019-02-26 Vessix, Inc. Inducing desirable temperature effects on body tissue
US10413356B2 (en) 2006-10-18 2019-09-17 Boston Scientific Scimed, Inc. System for inducing desirable temperature effects on body tissue
US8496653B2 (en) 2007-04-23 2013-07-30 Boston Scientific Scimed, Inc. Thrombus removal
WO2009136167A1 (fr) * 2008-05-07 2009-11-12 University Of Strathclyde Système de caractérisation ou de surveillance de dispositifs implantés
DE102008045876A1 (de) 2008-09-06 2010-03-11 Robert Prof. Bauernschmitt Implantierbare medizinische Vorrichtung mit einer Gitterstruktur sowie Verfahren zum Herstellen und Verwenden derselben
US8396548B2 (en) 2008-11-14 2013-03-12 Vessix Vascular, Inc. Selective drug delivery in a lumen
US9327100B2 (en) 2008-11-14 2016-05-03 Vessix Vascular, Inc. Selective drug delivery in a lumen
US8401667B2 (en) 2008-11-17 2013-03-19 Vessix Vascular, Inc. Selective accumulation of energy with or without knowledge of tissue topography
US8551096B2 (en) 2009-05-13 2013-10-08 Boston Scientific Scimed, Inc. Directional delivery of energy and bioactives
US9277955B2 (en) 2010-04-09 2016-03-08 Vessix Vascular, Inc. Power generating and control apparatus for the treatment of tissue
WO2012048907A1 (fr) * 2010-10-15 2012-04-19 Fraunhofer-Gesellschaft Zur Förderung Der Angewandten Forschung E.V. . Système de détection destiné à être implanté dans un corps et procédé de fabrication du système de détection
US9919144B2 (en) 2011-04-08 2018-03-20 Medtronic Adrian Luxembourg S.a.r.l. Iontophoresis drug delivery system and method for denervation of the renal sympathetic nerve and iontophoretic drug delivery
EP3292885A1 (fr) 2016-09-06 2018-03-14 BIOTRONIK SE & Co. KG Système de conducteur d'électrode élastique et implant médical
US11116561B2 (en) 2018-01-24 2021-09-14 Medtronic Ardian Luxembourg S.A.R.L. Devices, agents, and associated methods for selective modulation of renal nerves
WO2020114871A1 (fr) * 2018-12-06 2020-06-11 Universiteit Gent Procédé d'intégration d'un circuit électronique à l'intérieur ou sur une endoprothèse

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