US20060111632A1 - Wireless breach detection - Google Patents

Wireless breach detection Download PDF

Info

Publication number
US20060111632A1
US20060111632A1 US11282224 US28222405A US2006111632A1 US 20060111632 A1 US20060111632 A1 US 20060111632A1 US 11282224 US11282224 US 11282224 US 28222405 A US28222405 A US 28222405A US 2006111632 A1 US2006111632 A1 US 2006111632A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
device
breach
circuit
signal
wall
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US11282224
Inventor
Richard Chen
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Fulfillium Inc
Sensurtec Inc
Original Assignee
Fulfillium Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F5/00Orthopaedic methods or devices for non-surgical treatment of bones or joints; Nursing devices; Anti-rape devices
    • A61F5/0003Apparatus for the treatment of obesity; Anti-eating devices
    • A61F5/0013Implantable devices or invasive measures
    • A61F5/003Implantable devices or invasive measures inflatable
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/07Endoradiosondes
    • A61B5/076Permanent implantations
    • 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
    • A61B5/686Permanently implanted devices, e.g. pacemakers, other stimulators, biochips
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/72Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7271Specific aspects of physiological measurement analysis
    • A61B5/7282Event detection, e.g. detecting unique waveforms indicative of a medical condition
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/74Details of notification to user or communication with user or patient ; user input means
    • A61B5/746Alarms related to a physiological condition, e.g. details of setting alarm thresholds or avoiding false alarms
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/12Mammary prostheses and implants
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F5/00Orthopaedic methods or devices for non-surgical treatment of bones or joints; Nursing devices; Anti-rape devices
    • A61F5/0003Apparatus for the treatment of obesity; Anti-eating devices
    • A61F5/0013Implantable devices or invasive measures
    • A61F5/0036Intragastrical devices
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F5/00Orthopaedic methods or devices for non-surgical treatment of bones or joints; Nursing devices; Anti-rape devices
    • A61F5/0003Apparatus for the treatment of obesity; Anti-eating devices
    • A61F5/0013Implantable devices or invasive measures
    • A61F5/0036Intragastrical devices
    • A61F5/004Intragastrical devices remotely adjustable
    • A61F5/0046Intragastrical devices remotely adjustable with wireless means
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/02Details
    • A61N1/08Arrangements or circuits for monitoring, protecting, controlling or indicating
    • GPHYSICS
    • G08SIGNALLING
    • G08BSIGNALLING OR CALLING SYSTEMS; ORDER TELEGRAPHS; ALARM SYSTEMS
    • G08B21/00Alarms responsive to a single specified undesired or abnormal operating condition and not elsewhere provided for
    • G08B21/18Status alarms
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/26Penis implants
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0061Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof swellable
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0001Means for transferring electromagnetic energy to implants
    • A61F2250/0002Means for transferring electromagnetic energy to implants for data transfer
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0003Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having an inflatable pocket filled with fluid, e.g. liquid or gas
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/008Alarm means
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362Heart stimulators
    • A61N1/37Monitoring; Protecting
    • A61N1/3706Pacemaker parameters

Abstract

Methods and systems for detecting wall breach in inflatable prostheses rely on intrusion of a body fluid or inflation medium to electrically alter a signaling circuit. In one embodiment, an open portion of a circuit is closed to enable or modify a transmitted signal. In another embodiment, electrical current is generated to power an electrical transmission.

Description

    CROSS-REFERENCES TO RELATED APPLICATIONS
  • [0001]
    The present application is a continuation-in-part of application Ser. No. 11/170,274 (Attorney Docket No. 022209-000400US), filed on Jun. 28, 2005, which was a continuation-in-part of application Ser. No. 11/122,315 (Attorney Docket No. 022209-000230US), filed on May 3, 2005, and claims the benefit under 35 USC § 119(e) of prior provisional application No. 60/629,800 (Attorney Docket No. 02209-000210US), filed on Nov. 19, 2004, the full disclosures of which are incorporated herein by reference.
  • BACKGROUND OF THE INVENTION
  • [0002]
    1. Field of the Invention
  • [0003]
    The present invention relates generally to medical apparatus and methods. More particularly, the present invention relates to implantable devices and methods and systems for detecting their malfunction or failure or impending malfunction or failure.
  • [0004]
    All implants of devices, especially those indicated for long term use, in the human body are highly regulated and must meet certain safety requirements. One such requirement is biocompatibility of the materials used in the construction of the device in the event they come into direct contact with body tissues and fluids. Even if the material is biocompatible, the contact with body tissues and fluid could result in diminished performance or malfunction esp. in devices with electronic components. It is known that when a device is implanted in the body, the materials forming the cover and structural elements of the device degrade and fatigue over time. It is also well known that excessive handling during implantation or even normal, repetitive movements could stress the structural integrity of the device. Failure of the structural integrity of the device or its covering, which eventually happens, causes the contents of the device, which heretofore were confined in the interior of the device, to be in contact with the surrounding tissues and their secretions. Therefore, it would be desirable to detect or to predict such an event before any potentially harmful contents come in contact with the surrounding tissues, before tissue secretions leak into the interior of the device resulting in malfunction, or before the content itself suffers a malfunction.
  • [0005]
    Prosthetic devices implanted in numerous locations in the body are prevalent in medical practice. Many of these prostheses are designed to assume the structural shape of the body part yet are soft and have similar flexibility to approximate the look and feel of normal human tissue. A common use has been for reconstructing the normal contour, improving the shape, and/or enlarging the size of the human breast. The most common breast prosthesis is a soft elastomeric container made of silicone rubber which is filled or “inflated” with a liquid or gel, typically a saline solution or a silicone gel, or a combination of such filling materials. Typically such prostheses are surgically implanted to fit underneath the skin of the body either between the chest wall and the mammary gland or in place of the mammary gland following a mastectomy. The ideal result after implantation is to achieve the contours and tissue characteristics of a natural breast, and prosthetic devices filled with silicone gel have been found to produce the best cosmetic result. Hence, silicone gel breast implants are the devices of choice in locations where they are approved.
  • [0006]
    Degradation and fatigue of the silicone rubber container of such breast implants, however, can lead to perforations, tears, ruptures, and seam separations, resulting in the leakage of filling materials to the surrounding tissues. Leakage from a saline filled device is usually harmless as the solution, if uncontaminated, is absorbed. Leakage from the preferred silicone gel filled device is much more problematic. Bleeding of gel at the surface is believed to contribute to the development of capsular contracture, a scarring condition that compresses the implanted device from a soft, natural profile into a rigid, spherical shape. More serious is the migration of leaked silicone gel to other parts of the body such as the lymph nodes and major organs where it becomes unremovable. Consequently, silicone gel has been implicated in many health problems including connective tissue diseases. This risk increases with the length of time the device is implanted.
  • [0007]
    The problem is exacerbated by the fact that leakage of silicone gel is not easily detected and the rupture of the device cannot be predicted. Unlike saline filled devices where rupture and leakage results in deflation over a short period of time and readily discovered by the patient, silicone gel tends to leak slowly and can go unnoticed for years. Often the rupture is discovered only upon removal of the device for another reason. The only noninvasive method currently sensitive enough to detect such an event reliably is an MRI scan. To monitor the integrity of a silicone gel device by regularly scheduled MRI scans is cost prohibitive. Consequently, the use of silicone gel filled breast prostheses is now highly restricted by regulatory authorities.
  • [0008]
    Gastric balloons are another type of implantable, inflatable prosthesis which is subject to failure from breach of the wall. Gastric balloons are typically introduced through the esophagus and inflated in situ in order to occupy a significant volume within the stomach. While gastric balloons are typically inflated with saline or other non-toxic materials which are benign if released into the stomach, the balloon structure itself is hazardous if accidentally deflated since it can pass and cause obstruction of the pyloric valve or the intestines distal to the pyloric valve. Any such obstruction is a medical emergency.
  • [0009]
    The problem is not limited to inflatable devices. Many implanted devices, e.g., cardiac pacemakers, contain electronic circuits and have insulated wires or leads that sense or deliver signals at certain points in the body. For example, the covering or insulation could deteriorate over time or tear in response to normal body movements. Body fluids from the surrounding could then leak into the circuitry, either as a liquid or vapor, causing disruption of signals. Or the lead could break at any point or detach from the connector to the device. Another class of implanted devices involves a closed vessel system conveying fluids leading from a part of the device or a part of the body to another part of the body, such as a shunt conveying blood or cerebrospinal fluid. The catheter or reservoir in the system could tear or break leading to the leakage of material out of the catheter to an unintended part of the body or leakage of body fluids into the catheter causing contamination. Yet another class of devices, which depend on solid objects for function or structural support, could fail from fracture or dislocation. These fractures can start as a hairline from repeated mechanical stress from use and progress to a complete fracture. Dislocations start with a loosening of the structure(s) holding an object in place and progress to a complete dislocation.
  • [0010]
    For these reasons, it would be desirable to provide apparatus and methods to detect or predict an actual or potential wall breach which can lead to leakage of the filling contents of breast implants, gastric balloons, catheters, reservoirs, and the like or an actual or potential disruption of an electronic circuit in cardiac pacemakers or neurostimulators or the like or an actual or potential stress fracture or dislocation in the case of solid components in prosthetic devices or the like. It would desirable further to monitor remotely the structural integrity and presumed functional status of a device without activating the function after device implantation in the case of cardiac defibrillators or without directly applying stress to the monitored part in the case of solid components. Prompt removal of such devices upon breach or imminent breach would avert most, if not all, of the ensuing problems including catastrophes. The methods and apparatus will preferably be adaptable for use in any structural design of the device without adversely affecting its structure or, in the case of breast implants, the final cosmetic result, and further be applicable to solid and rigid body implants containing electronic components such as pacemaker and defibrillator canisters and leads and to solid body implants such as prosthetic heart valves or orthopedic devices. It would be further desirable if the breach or imminent breach of the device were detectable to the patient in an easy, rapid, and reliable fashion outside of a medical facility or at home. Additionally, it would be beneficial if the system were able to monitor the device non-invasively on a frequent basis over the life of the device without incurring significant additional cost for each diagnostic event. At least some of these objectives will be met by the inventions described hereinafter.
  • [0011]
    2. Description of the Background Art
  • [0012]
    Leakage detection is described in U.S. Pat. No. 6,826,948 and published applications US 2004/0122526 and US 2004/0122527. Breast implants and methods for their use are described in U.S. Pat. Nos. 6,755,861; 5,383,929; 4,790,848; 4,773,909; 4,651,717; 4,472,226; and 3,934,274; and in U.S. Publ. Appln. 2003/163197. Gastric balloons and methods for their use in treating obesity are described in U.S. Pat. Nos. 6,746,460; 6,736,793; 6,733,512; 6,656,194; 6,579,301; 6,454,785; 5,993,473; 5,259,399; 5,234,454; 5,084,061; 4,908,011; 4,899,747; 4,739,758; 4,723,893; 4,694,827; 4,648,383; 4,607,618; 4,501,264; 4,485,805; 4,416,267; 4,246,893; 4,133,315; 3,055,371; and 3,046,988 and in the following publications: US 2005/0137636; US 2004/0215300; US 2004/0186503; US 2004/0186502; US 2004/0162593; US 2004/0106899; US 2004/0059289; US 2003/0171768; US 2002/0099430; US 2002/0055757; WO 03/095015; WO88/00027; WO87/00034; WO83/02888; EP 0103481; EP0246999; GB2090747; and GB2139902.
  • BRIEF SUMMARY OF THE INVENTION
  • [0013]
    The present invention provides systems and methods for detecting partial or complete breach in the exterior wall of an implantable device, such as an inflatable, implantable prosthesis of the type where a wall at least partially surrounds a fluid medium, liquid or air, in one or more inflatable compartments. The walls of inflatable devices will usually be non-rigid, either elastic or non-elastic. Other implantable devices subject to exterior structure breach include metal and plastic (polymer) devices which may comprise rigid-walled casings or housings, such as pacemakers, implantable defibrillators, neurostimulators, insulin pumps, reservoirs, devices having flexible housings such as elastomeric reservoirs containing with naturally collected or pre-filled fluids or insulation or other coverings formed over the electrically conductive core of electrical leads, electrical connectors (e.g., plugs), and the like. Implantable devices subject to stress fracture in solid functional components include artificial joints, prosthetic heart valves, and the like. These and other devices may contain potentially bioincompatible materials, such as batteries, circuitry, synthetic chemicals, and the like. While the implementation of these systems and methods will be described in detail in connection with inflatable devices such as breast implants and gastric balloons and with solid core devices such as electrical leads, it will be appreciated that the principles may be applied to other inflatable prostheses, such as penile implants, to vessel systems containing or conveying fluids, to electronic and other devices having solid internal structural or functional components. The systems of the present invention are incorporated into at least a portion of the wall of the wall or covering of the inflatable prosthesis or other device or coupled to the electronic circuitry or embedded in the solid component itself and provide for or enable the emission or transmission of a detectable radio-frequency or other electronic signal upon breach or partial breach of the wall or the structural integrity of the component. As used hereinafter, the term “breach” will refer to any partial or full penetration of the structure of the wall or covering as well as to other mechanical disruption of a solid part of the device which could initiate or lead to the contact of materials inside the wall or covering or the solid component itself with tissues or body fluids outside the device. Such breach signifies a compromise or a threatening compromise to the integrity of the device.
  • [0014]
    The signal emission system of the present invention preferably comprises a signaling circuit having one or more components which become exposed to an exterior or interior environment surrounding or within the prosthesis or other implantable device upon breach or partial breach of the wall or covering, wherein such exposure enables, disables, energizes, and/or changes a signal which is emitted by the system. In particular, the breach may act like a switch to close or open a region within the signaling circuit to cause, enable, disable, or alter the signal emission. Alternatively, the exposure of the circuit and/or internal structure to the interior or exterior environment may result in a change in impedance, capacitance, inductance or other detectable circuit characteristics that can trigger or modify the signal emitted.
  • [0015]
    In a first embodiment, the component of the signaling circuit will generate electrical current when exposed to a body fluid and/or an interior medium within the device upon breach or failure of the exterior structure. Body fluids such as blood, cerebrospinal fluid, lymph fluid, and the like, are naturally conductive, i.e., contain electrolytes. The interior medium, such as an inflation medium, can be selected to be electrically conductive, e.g., comprise or consist of saline or other biologically compatible electrolytes and salt solutions. In such cases, the generated electrical current can power an unpowered transmission component to emit the signal. Alternatively, the power can alter a signal which has already been continuously or periodically emitted by the signaling circuit. In the latter case, the signaling circuit may require a separate source of energy, such as a battery or circuit components which are placed on the exterior or interior of the wall so that they are always exposed to fluids to provide for current generation.
  • [0016]
    Alternatively, the circuit components may include spaced-apart conductors which are electrically coupled to the signaling circuit to “close” the signaling circuit to permit current flow when exposed to a body fluid and/or device contents by a wall breach. Alternatively, the circuit may be altered, enabled or otherwise modified by a sufficient flow of electrolytes to enable, interpret, disrupt, or modify a signal emission. The circuit components may include spaced apart conductors which are coupled to the signaling circuit to detect a change in resistance, capacitance, impedance, or voltage. Since the breach could be small and intermittent as it starts, it can be difficult to detect as a flow but the cumulative gain or loss of the electrolytes from the contents or surrounding body fluids could cause a change in the resistance, capacitance, or impedance across the conductors. Alternatively, the detection circuit is closed and the contact of the contents or the body fluids with the conductors could cause a break, disruption, or change in the functioning of the circuit. In the exemplary embodiments described below, the conductors may comprise meshes, films, or other relatively large surface areas covering most or all of the wall so that breach at any point in the wall will provide the intended electrically conductive bridging between the conductors. The coupling of the conductors may also cause, alter, or enable a signal emission to alert the patient of the breach or potential breach. The spaced-apart conductors can have any one of a variety of shapes or configurations, continuous configurations, such as plates and films, or discontinuous configurations, such as lattices, meshes, and the like, can be placed in various locations, preferably near interior portions of the device where body fluids will pool to enhance sensitivity and reliability of the detection.
  • [0017]
    Alternatively, the detection and signaling circuit may comprise at least two conductors coupled to a third conductor which is part of the functional circuitry or is embedded in the solid component of the device or is the solid component itself. In the event any of the conductors, and the third, functional conductor in particular, is fractured, even intermittently, a circuit is broken thereby causing a signal alteration by the signaling circuit to alert the patient of the breach or potential breach. The detecting conductors can have any one of a variety of shapes or configurations, including continuous configurations, such as plates and films, or discontinuous configurations, such as lattices, meshes, braids, fabrics, and the like, and can be placed in various locations, preferably spanning parts of the device where fractures are prone in order to enhance sensitivity and reliability of the detection. More than one of these couplings could be made in any configuration or location on a device to determine the site of the breach.
  • [0018]
    The signaling circuit can be active or passive. In a preferred embodiment, the signaling circuit will comprise a passive transponder and antenna which are adapted to be powered and interrogated by an external reader. Such transponder circuitry may conveniently be provided by using common radiofrequency identification (RFID) circuitry where the transponder and tuned antenna are disposed on or within a protected area in the prosthesis and connected to remaining portions of the signaling circuit. Passively powered circuitry is particularly preferred in devices with on board batteries where the amount of energy stored in the battery generally determines the functional product life. The antenna and transponder could be located in close proximity to the detection circuitry or placed elsewhere in the device or another part of the body. For example, by connecting the transponder circuitry to “open” conductors which is closed in the presence of body fluids and/or inflation medium, the signal emitted by the transponder upon interrogation by an external reader may be altered. Thus, the patient or medical professional may interrogate the prosthesis and determine whether or not the prosthesis remains intact or the threat of an impending breach exists. This is a particularly preferred approach since it allows the user to determine that the transponder circuitry is functional even when a breach has not occurred.
  • [0019]
    The present invention further provides methods for signaling breach of a wall or covering of an inflatable prosthesis, electronic prosthesis, solid prosthesis, electrical cable, or the like. Usually, signaling comprises generating an emission by closing a signaling circuit when the wall or part of the device is at least partially breached. Usually a flow of electrolytes occurs when the wall or part of the device is at least partially breached, thereby closing the signaling circuit. To detect a near complete or complete fracture in solid components, generating an emission may comprise opening a signaling circuit when the wall, covering, or other part is substantially breached or generating an electrical current when the part is substantially breached. The particular signaling circuits and transmission modes have been described above in connection with the methods of the present invention.
  • [0020]
    The signaling system of the present invention can be designed to function using any one of a variety of algorithms to notify the patient in a simple, unequivocal fashion. For example, in a toggle algorithm, the transmitter is either on in the static state or preferably off in order to reduce the need for power. Upon direct contact between the conductors and the body fluids and or device contents, the now closed circuit cause the transmitter to turn the signal off or preferably on to be able to send a wireless signal on a continuous basis. The wireless signal or lack thereof depending on the algorithm is recognized by the detector to notify the patient that the integrity of the device is compromised.
  • [0021]
    Alternatively, the algorithm could be based on time, amplitude, frequency, or some other parameter. For example, the transmitter may send a wireless signal at a predetermined time interval in its static state. The detector recognizes the length of the interval as normal and the existence of the signal as the system in working order. Upon direct contact with the body fluids or device contents by the probes, the transmitter is enabled to send the same signal at different time intervals or a different signal, which is recognized by the detector to notify the patient that the integrity of the device is compromised. The lack of a signal is recognized by the detector to notify the patient of a detection system malfunction and potential compromise of the integrity of the device.
  • [0022]
    Optionally, more than one probe or more than one type of probe may be placed internally in different parts or components in the device so that the particular part or component which failed may be identified based on which probe was activated. The transmitter would send different signals for the receiver to display the source of the failure.
  • [0023]
    The internal probe could be of any shape and is disposed in the interior or preferably in the wall or covering of the device. The preferred configuration is a fine lattice or continuous film of the detection material embedded in the wall or in between layers of the wall covering the entire device, thereby conforming to the shape of the device. Such a configuration optimizes the performance of the system in detecting failures early. As the site of the tear or rupture cannot be predicted, the probe would be unlikely to miss detecting the breach by covering the entire device.
  • [0024]
    Compromise of the device typically starts with a somewhat linear split or tear in surface of the device wall or covering from mechanical fatigue or handling damage. As the split propagates, it will expose more and more lines of the lattice or area of the film to the body fluids and or device contents. Consequently, as the size and seriousness of the breach increases, the probability of detection increases. Embedding the detection material in the covering such as the wall of the balloon further enables detection before a full breach of the entire thickness of the device wall.
  • [0025]
    The detection material could be any metal, polymer, fiber, ingredient, or combination thereof, with or without any coating that can generate an electrical charge or enable flow of electric current when in contact with the body fluids or device contents. For example, an electrical charge could be generated from a non-toxic chemical reaction when the lattice exposed underneath a tear comes in contact with the body secretions. Flow of electric current could be enabled when two ends of an electric circuit hitherto physically separated by electrically non-conductive material in the covering or a structural element of the device are in contact with electrolytes in the body secretions when the electrically non-conductive material is compromised. For example, a charged lattice is embedded in the wall separated by silicone rubber from the ground probe on the external surface of the device. When the lattice is exposed to the electrolytes in the body fluids in the event of a tear, the circuit is closed. Alternatively, the lattice and ground could be separate from each other but interlaced in the wall of the device. Preferred materials include non-corrosive, biocompatible metals and elastomers, inks, or the like which contain electrically conductive particles.
  • [0026]
    The transmitter can be a simple wireless signal generator triggered by an electric current or preferably a transponder using the well-established RFID technology, i.e., produces a wireless signal when triggered by an interrogating signal. The electric charge generated or the electric current enabled by the probe in contact with the body fluids or device contents changes the logic state thereby enabling the transmitter to emit or causes it to emit a wireless signal. Typically, the transponder is powered by the interrogating radio frequency signal so that no power source of its own is required. Alternatively, the transmitter could be powered by a micro battery or by the electrical power generated by a chemical reaction. For protection from degradation by an acidic and electrolyte solution and become potentially toxic, the transmitter or transponder circuit is encased in a highly resistant material, such as silicone rubber or stainless steel. The transmitter or transponder circuit can be placed on the exterior, embedded in the wall, or preferably in the interior of the device for shielding from chemical degradation and mechanical stress. It can be placed in any orientation, preferably in the plane where the antenna is most sensitive and the transmitter is most effective in sending and receiving signals through body tissue overlying the device.
  • [0027]
    The wireless signal from the transmitter is recognized by a separate detector, typically external to the body. The detector could be simply a receiver tuned to the transmitter's signal or, preferably, a combination of both a transmitter of a signal to interrogate the transponder and a receiver to distinguish the different signals from the transponder. The detector is preferably powered by batteries and portable enough to be worn on a wristband, necklace, or belt or can be placed conveniently near a place where the patient spends most of his time. Upon receiving a signal that a breach has occurred, the detector will alert the patient to seek medical assistance or alert medical professionals directly through other devices, such as Bluetooth linked to an autodial telephone. The alarm could be auditory, such as beeping sounds, visual, such as flashing LED's or a LCD display, sensory, such as vibrations, or preferably a combination of any or all of the above.
  • [0028]
    Optionally, the detector could have different auditory, visual, sensory, or different combinations to identify the source of the detected breach, especially with more than one probe or more than one type of probe. For example, LED's of different colors or different sounds could be used. The alarm could further indicate the seriousness of the breach. For example, when multiple probes detect a breach, the volume of the alarm would increase to a higher level.
  • [0029]
    In the case of electronic implantable devices, such as pacemakers and defibrillators, the devices will be subject to failure due to intrusion of body fluids through breaches, particularly at the seams and lead connections. Thus, the detector circuit components described above could be located within the device canister near those seams and connectors at risk of failure so that initial penetration of fluids could be detected before sufficient amount of fluids, liquid or vapor, has entered to cause failure of the device.
  • [0030]
    In the case of electrical leads used in electronic stimulation devices, a breach in the insulation and a breach in the conductor can both be detected. The embodiments described above are particularly suitable for detecting a breach in the covering insulation from wear and tear. Usually this breach will precede and can serve as a sentry for a breach in the conductor. A breach in the conductor without a breach in the insulation can be detected by a closed circuit formed by two conducting probes, one coupled to the conductor near its proximal end and the other at its distal end. Any fracture or disruption of the current flow in the conductor, whether made of a metal, elastomer, or gel, between the two points will result in “opening” the circuit. An opening will change the logic state of the detection circuit and enable the transmitter to emit or causes it to emit a wireless signal. The detection and transmitting circuitry could be attached to any part of the lead or is in its own separate housing connected to the lead by the conducting probes. Thus, the detection and transmitting circuitry could be placed in a preferred orientation where normal body movements would not cause any sharp angles in the conductors and an area away from sites where wear and tear are more prone.
  • [0031]
    In the case where electrical leads are coupled to another conductor such as the connector outside the canister containing the functioning hardware and software, the principles and methods can detect detachment of the lead. In this embodiment, one probe is electrically coupled to the male and another probe to the female side of the connection. When the lead is detached from the connector, the circuit is thereby “opened” and detected as a breach.
  • [0032]
    In the case of solid devices, such as artificial joints or heart valves, the conductors are embedded in the device components prone to failure. The detection and transmitting circuitry could also be embedded in the device or placed in an area away from sites where wear and tear are more prone or signal transmission could be adversely affected.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • [0033]
    FIG. 1 illustrates a gastric balloon having the wall breach detections system of the present invention incorporated therein.
  • [0034]
    FIG. 2 illustrates a breast implant having the wall breach detection system of the present invention incorporated therein.
  • [0035]
    FIG. 3 illustrates a multi-layer wall structure useful for the prostheses of the present invention.
  • [0036]
    FIG. 4 illustrates a passive transponder system which may be utilized in the wall breach detection systems of the present invention.
  • [0037]
    FIG. 5 illustrates a hand-held interrogation unit useful with the systems of the present invention.
  • [0038]
    FIG. 6 illustrate leads and connectors used in electronic stimulators having the covering breach detection system of the present invention incorporated therein.
  • [0039]
    FIG. 7 illustrate solid device components having the wall breach detection system of the present invention incorporated therein.
  • DETAILED DESCRIPTION OF THE INVENTION
  • [0040]
    Referring now to FIG. 1, the gastric balloon 100 includes two electric probes. Probe 130 is on the external surface in contact with the surrounding tissues, body fluids, and contents of the stomach. Probes 130 and 110 can have any of a variety of shapes or configurations, including circular plates, lattices, films, and the like, cover all or a portion of the balloon or other device. Probe 110, shown here in a lattice configuration, provides the second probe incorporated in the wall of the balloon. The probe material could be any metal, polymer, fiber, or combination thereof, with or without any coating that can generate an electrical charge or enable flow of electric current when in contact with the stomach contents. The probes are connected electronically to the wireless transmitter 140, but are separated from each other by at least one layer of non-conductive material in the balloon wall. The transmitter can be a simple wireless signal generator triggered by an electric current or preferably is an unpowered transponder using well-established RFID technology which produces a wireless signal in response to an interrogating signal. In the intact state when the wall is not breached, components 130, 110, and 140 comprise an open electrical circuit and the transmitter is inactive, disabled, or enabled to transmit a base signal.
  • [0041]
    Referring now to FIG. 2, a breast implant 200 may be similarly formed with a lattice 210 formed within the breast wall, an external electrically conductive probe 230 formed on or over the exterior surface of the implant, and a transmitter 240 connected to both the lattice and exterior probe. In the case of breast implants filled with low conductivity materials, such as silicone gel, it may be desirable to provide conductive materials to enhance conductivity upon leakage.
  • [0042]
    As magnified in FIG. 3, the second internal probe comprises both a fine lattice 110 and a thin film configuration 112 in the wall of the balloon in between, at the minimum two layers, an outermost layer 102 and innermost layer 104. The second internal probe can be also disposed in any enclosed space in the device (not shown). In the configuration described in FIG. 1, probes 130 and 110 and transponder 140 represent one open circuit and probes 130 and 112 and transponder 140 represent a second open circuit. Each open circuit is available to power or enable the transmitter or may enable the transponder to alter a base signal.
  • [0043]
    After the balloon is deployed in the stomach, the external probe 130 is in contact with the surrounding tissue and body fluids and stomach contents. Upon a breach in the integrity of the wall, such as a tear in the outermost layer 102, the leakage of physiologic fluid or stomach contents with electrolytes into the tear forms a salt bridge that closes the circuit formed probes 130 and 112 and transponder 140. Once the circuit is closed, a toggle is switched in the transponder, which will be enabled to transmit a “layer 102 breach” signal. Tears through layer 106 in the balloon wall will allow leakage of physiologic fluid or stomach contents with electrolytes into the tear forming a salt bridge that closes the circuit formed probes 130 and 110 and transmitter 140. Closing this circuit switches another toggle in the transponder, which will be enabled to transmit a “layer 106 breach” signal.
  • [0044]
    The preferred radiofrequency identification circuit is shown schematically in FIG. 4. The circuit comprises a transmitter component 300 which includes transponder circuitry 302, typically formed as an integrated circuit, and a tuned antenna-capacitor circuit 304. An interrogator reader 310 comprises circuitry 312 including the power supply (typically a battery) demodulator circuitry, decoder circuitry, and the like. An antenna 314 is tuned so that it can communicate wirelessly with the antenna 304 of the transponder 300. Operation of this circuitry is generally conventional and provides for energizing, demodulating, and decoding signals between the external and implanted components. The transponder circuitry, however, will be modified so that the conductive elements implanted in the wall, such as film 320 and lattice 330 may enable or alter the signal emitted by the transponder when the conductive elements are bridged by body fluids or inflation medium. In the preferred embodiments described above, electrical coupling of the conductors 320 and 330 will alter the signal that is produced by the transponder 302. In that way, the patient or other user will be able to interrogate the transponder and receive a base or “normal” response signal when no wall breach has occurred. In the event of a wall breach, the signal emitted by the transponder will be altered so that the breach will be made evident.
  • [0045]
    An exemplary reader module 120 is shown in FIG. 5 and includes LEDs to indicate normal or “on” function, failure, and emergency failure. An audible the alarm 126 could also be provided to alert with beeping sounds, or sensory, such as vibrations, or preferably a combination of any or all of the above. Optionally, the detector could have different auditory, visual, sensory, or different combinations to identify the source of the detected breach, especially with more than one chemical substance used. The alarm could further indicate the seriousness of the breach. For example, when breaches are detected, the volume of the alarm would increase to a higher level.
  • [0046]
    Referring now to FIG. 6A, an electrical lead 600 with a functional conductor 650 which is useful for cardiac or neuro stimulators may be similarly formed with an electrically conductive lattice 610 embedded within an insulating covering 605, an external electrically conductive cable coil 630 attached to the exterior surface of the implant, and a transmitter 640 connected to both the lattice 610 and external coil 630. As shown in the cross section FIG. 6B, the lattice 610 is preferably formed coaxial to the conductor 650 and separated from the conductor and the surrounding environment by inner and outer annular portions of the cover 605. The cross section of FIG. 6C shows conductive probes 610 and 620 in lattice form both embedded in the covering. The cross section of FIG. 6D shows a plurality of conducting probes 610 and 620 which are embedded coaxially in the insulating covering 605. In this embodiment, a current flow enabled by electrolytes between external probe 630 and 610 or 620 or the functional conductor 650 could indicate the extent of the breach. An alternative configuration is shown as lead 601 in FIG. 6E and FIG. 6F with two functional conductors 650 a and 650 b connected at their ends but electrically isolated from each other along their length so that each can serve as a backup for the other. In this configuration, the probes 610 and 620 do not have to be separated from but are in contact with the functional conductors.
  • [0047]
    In the case of detecting a breach of the functional conductor, a lead 602 is shown with two electrically conductive probes 660 and 670 coupled to two ends of the functional conductor 650, as shown in FIG. 6G.
  • [0048]
    In the case where the functional conductor 650 is connected to another functional electrical conductor 680, as shown in FIG. 6H, a lead 603 is shown with a transmitter 640 with two probes, 660 and 670. Probe 660 is coupled to the functional conductor 650 and 670 to the other functional conductor 680, in this embodiment an electrical connector. One or both of the probes 660 and 670 are attached after the connection is made. Both probes 660 and 670 can be embedded in the functional conductor connection housing in either the male or female side, as shown in FIG. 61. In this embodiment of a female connector 604, functional conductor 650 passes through and is electrically coupled to functional conductor 680. In this embodiment as electrically isolated rings inside the female connector 604, probe 670 is coupled to 680 and probes 660 a and 660 b coupled to 650. Such a configuration would enable detection of a partial detachment of the male member 649 when the circuit between 670 and 660 b is closed but that between 660 a and 660 b is open and a possible complete lead detachment when all the detection circuits are open. The placement and physical length of the probes 660 a and 660 b would determine the amount of detachment necessary to open the circuit and enable the system to signal a breach.
  • [0049]
    While the leads and connectors incorporating the detection system are illustrated independently above, they may be configured independent to each other in a device system or together in any combination using one or more common detecting or signaling circuits.
  • [0050]
    Referring now to FIG. 7, two solid prosthetic device forms are shown. Cylindrical shaped 701 and a flat triangular shaped 702 are shown with a transmitter 740, an electrically conductive lattice 710, and an external electrically conductive probe 730. 701 a and 702 a are cross sections of each respectively. Any wear and tear or fracture deep to the lattice 710 is detected as a breach. It can be appreciated that the principle can be applied to a solid object of any shape. In the case of an object holding other parts of the device in place or within a range of motion (not shown), such as functioning like a ligamentous or cartilagecartilaginous structure in the body, respectively, detecting a breach of the object would indicate a potential dislocation of the other parts.
  • [0051]
    While the above is a complete description of the preferred embodiments of the invention, various alternatives, modifications, and equivalents may be used. Therefore, the above description should not be taken as limiting the scope of the invention which is defined by the appended claims.

Claims (25)

  1. 1. An improved implantable device having an exterior structure, wherein the improvement comprises a system incorporated into said exterior structure, which system emits a detectable wireless signal upon breach of said exterior structure.
  2. 2. An improved implantable device as in claim 1, wherein the exterior structure comprises a wall which at least partially surrounds a compartment which is fillable with a fluid medium.
  3. 3. An improved device as in claim 2, wherein the exterior structure is inflatable and the liquid medium is an inflation medium.
  4. 4. An improved device as in claim 3, wherein the exterior structure is non-rigid.
  5. 5. An improved device as in claim 4, which comprises a breast implant, a gastric balloon, or a penile implant, or a reservoir.
  6. 6. An improved implantable device as in claim 1, wherein the exterior structure comprises a rigid housing.
  7. 7. An improved implantable device as in claim 6, wherein the device comprises a pacemaker, a defibrillator, a neurostimulator, or an insulin a biochemical delivery pump, or a reservoir.
  8. 8. An improved implantable device as in claim 1, wherein the exterior structure comprises a covering formed over an electrically conductive core.
  9. 9. An improved implantable device as in claim 8, wherein the device comprises an electrical cable or an electrical connector.
  10. 10. An improved device as in claim 1, wherein the signal emission system comprises a signaling circuit having one or more components which are exposed to an exterior or interior environment upon breach of the exterior structure, wherein exposure of the component energizes the circuit, closes the circuit or opens the circuit to cause, alter, disable, or enable signal emission.
  11. 11. An improved device as in claim 10, wherein the component generates electrical current when exposed to body fluid and/or an interior medium by a wall breach.
  12. 12. An improved device as in claim 10, wherein the component includes spaced-apart conductors which are electrically coupled to close and/or alter a capacitance or inductance of the signaling circuit when exposed to a body fluid and/or the fillable medium by a wall breach.
  13. 13. An improved device as in claim 10, wherein the signaling circuit comprises a transponder and an antenna, wherein the transponder is powered by an external reader which is tuned to the antenna of the transponder, wherein the transponder and antenna are inactive or operational in a first mode until a wall breach closes the control or signaling circuit, wherein closing of the control or signaling circuit activates or alters the transponder emission.
  14. 14. A method for signaling breach of an external structure of an implantable device, said method comprising emitting an externally detectable wireless signal when the external structure has been at least partially breached.
  15. 15. A method as in claim 14, wherein the exterior structure is inflatable and the liquid medium is an inflation medium.
  16. 16. A method as in claim 15, wherein the exterior structure is non-rigid.
  17. 17. A method as in claim 16, a breast implant, a gastric balloon, or a penile implant, or a reservoir.
  18. 18. A method as in claim 14, wherein the exterior structure comprises a rigid housing.
  19. 19. A method as in claim 18, wherein the device comprises a pacemaker, a defibrillator, a neurostimulator, a biochemical delivery an insulin pump, or a reservoir.
  20. 20. A method as in claim 14, wherein the exterior structure comprises a covering formed over an electrically conductive core.
  21. 21. A method as in claim 20, wherein the device comprises an electrical cable or an electrical connector.
  22. 22. A method as in claim 14, wherein emitting comprises closing or opening or signaling circuit when the exterior structure is at least partially breached.
  23. 23. A method as in claim 22, wherein the signaling circuit is unpowered and comprises an antenna and a transponder, further comprising directing an interrogation signal to the antenna and detecting a return signal from the transponder, wherein the returned signal is altered, present or ceases only when the control or signaling circuit has been closed or opened by a breach of the exterior structure.
  24. 24. A method as in claim 22, wherein the signaling circuit is powered and emitting comprises exposing a component of a signaling circuit to an internal or external environment when the exterior structure is at least partially breached wherein the control or signaling circuit is closed and transmits a signal.
  25. 25. A method as in claim 14, wherein emitting comprises exposing a component of a signaling circuit to an internal or external environmental when the exterior structure is at least partially breached, wherein the control or signaling circuit generates energy and transmits a signal.
US11282224 2004-05-03 2005-11-18 Wireless breach detection Abandoned US20060111632A1 (en)

Priority Applications (5)

Application Number Priority Date Filing Date Title
US62980004 true 2004-11-19 2004-11-19
US11122315 US8066780B2 (en) 2004-05-03 2005-05-03 Methods for gastric volume control
US11121704 US20050267596A1 (en) 2004-05-03 2005-05-03 Devices and systems for gastric volume control
US11170274 US8070807B2 (en) 2004-11-19 2005-06-28 Wireless breach detection
US11282224 US20060111632A1 (en) 2004-11-19 2005-11-18 Wireless breach detection

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
US11282224 US20060111632A1 (en) 2004-11-19 2005-11-18 Wireless breach detection
US14971845 US9456915B2 (en) 2004-11-19 2015-12-16 Methods, devices, and systems for obesity treatment
US14971795 US9445930B2 (en) 2004-11-19 2015-12-16 Methods, devices, and systems for obesity treatment
US15231167 US20170035593A1 (en) 2004-11-19 2016-08-08 Methods, devices, and systems for obesity treatment
US15232485 US20170119566A1 (en) 2004-11-19 2016-08-09 Methods, devices, and systems for obesity treatment
US15621795 US9808367B2 (en) 2004-11-19 2017-06-13 Methods, devices, and systems for obesity treatment

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US11170274 Continuation-In-Part US8070807B2 (en) 2004-05-03 2005-06-28 Wireless breach detection

Related Child Applications (2)

Application Number Title Priority Date Filing Date
US14971845 Continuation US9456915B2 (en) 2004-05-03 2015-12-16 Methods, devices, and systems for obesity treatment
US14971795 Continuation US9445930B2 (en) 2004-05-03 2015-12-16 Methods, devices, and systems for obesity treatment

Publications (1)

Publication Number Publication Date
US20060111632A1 true true US20060111632A1 (en) 2006-05-25

Family

ID=38190991

Family Applications (3)

Application Number Title Priority Date Filing Date
US11170274 Active 2028-04-02 US8070807B2 (en) 2004-05-03 2005-06-28 Wireless breach detection
US11282224 Abandoned US20060111632A1 (en) 2004-05-03 2005-11-18 Wireless breach detection
US14971795 Active US9445930B2 (en) 2004-05-03 2015-12-16 Methods, devices, and systems for obesity treatment

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US11170274 Active 2028-04-02 US8070807B2 (en) 2004-05-03 2005-06-28 Wireless breach detection

Family Applications After (1)

Application Number Title Priority Date Filing Date
US14971795 Active US9445930B2 (en) 2004-05-03 2015-12-16 Methods, devices, and systems for obesity treatment

Country Status (4)

Country Link
US (3) US8070807B2 (en)
EP (1) EP1811920A4 (en)
JP (1) JP4839321B2 (en)
WO (1) WO2006055839A3 (en)

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060111777A1 (en) * 2004-11-19 2006-05-25 Fulfillium, Inc. Wireless breach detection
US20060271118A1 (en) * 2005-05-25 2006-11-30 Cardiac Pacemakers, Inc. Implantable neural stimulator with mode switching
WO2007128133A1 (en) * 2006-05-09 2007-11-15 David James Haddon Hair sequestered tracer for prosthesis leak detection
US20080109027A1 (en) * 2006-08-01 2008-05-08 Fulfillium, Inc. Method and system for gastric volume control
WO2008055229A2 (en) 2006-10-31 2008-05-08 Novalert, Inc. External sensing for implant rupture
US20110015666A1 (en) * 2005-03-01 2011-01-20 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
US20110098576A1 (en) * 2009-12-01 2011-04-28 Hollstien David S Non-invasive implant rupture detection system
WO2012097225A2 (en) 2011-01-13 2012-07-19 Sensurtec, Inc. Breach detection in solid structures
WO2013025299A1 (en) * 2011-08-12 2013-02-21 Cardiac Pacemakers, Inc. Medical device lead with conductor fracture prediction
WO2013188425A2 (en) 2012-06-13 2013-12-19 Elwha Llc Breast implant with analyte sensors and internal power source
US9326730B2 (en) 2012-06-13 2016-05-03 Elwha Llc Breast implant with covering and analyte sensors responsive to external power source
US9333071B2 (en) 2012-06-13 2016-05-10 Elwha Llc Breast implant with regionalized analyte sensors and internal power source
US9339372B2 (en) 2012-06-13 2016-05-17 Elwha Llc Breast implant with regionalized analyte sensors responsive to external power source
EP3298962A1 (en) 2016-09-23 2018-03-28 Biosense Webster (Israel), Ltd. Detection of leakage in implants
US9959739B1 (en) * 2016-10-28 2018-05-01 Nantin Enterprise Limited System, method and article for indicating a wet or dry condition to a user

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9456915B2 (en) 2004-11-19 2016-10-04 Fulfilium, Inc. Methods, devices, and systems for obesity treatment
JP5009158B2 (en) * 2004-09-21 2012-08-22 シャロン ヴェンチャーズ インコーポレイテッド Tissue expansion device
US9526584B2 (en) 2004-09-21 2016-12-27 Airxpanders, Inc. Tissue expanders, implants, and methods of use
US7699863B2 (en) 2005-03-01 2010-04-20 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
EP1895894A4 (en) * 2005-06-10 2009-12-30 Novalert Inc Method and apparatus for monitoring implants
EP3251631A3 (en) 2009-12-18 2018-03-28 Airxpanders, Inc. Tissue expanders

Citations (70)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2752590A (en) * 1954-03-01 1956-06-26 Specialties Dev Corp Insulation failure detector for electric cables
US2792568A (en) * 1955-03-04 1957-05-14 Specialties Dev Corp Network for detecting the failure of the insulation of electrically conductive cables
US3046988A (en) * 1958-12-01 1962-07-31 Davol Rubber Co Esophageal nasogastric tube
US3055371A (en) * 1958-12-23 1962-09-25 Kulick George Device for regulation and control of esophago-gastric balloons
US3906959A (en) * 1974-02-14 1975-09-23 American Optical Corp Liquid leak stop for an implantable heart pacer
US4133315A (en) * 1976-12-27 1979-01-09 Berman Edward J Method and apparatus for reducing obesity
US4246893A (en) * 1978-07-05 1981-01-27 Daniel Berson Inflatable gastric device for treating obesity
US4386231A (en) * 1980-04-30 1983-05-31 Canada Wire And Cable Limited Cable assembly for detecting the ingress of water inside a cable
US4416267A (en) * 1981-12-10 1983-11-22 Garren Lloyd R Method and apparatus for treating obesity
US4455691A (en) * 1979-10-03 1984-06-26 Minnesota Mining And Manufacturing Company Silicone gel filled prosthesis
US4485805A (en) * 1982-08-24 1984-12-04 Gunther Pacific Limited Of Hong Kong Weight loss device and method
US4501264A (en) * 1978-06-02 1985-02-26 Rockey Arthur G Medical sleeve
US4557640A (en) * 1978-03-13 1985-12-10 Rottler Donald B Combination boring and honing apparatus and method
US4607618A (en) * 1983-02-23 1986-08-26 Angelchik Jean P Method for treatment of morbid obesity
US4648383A (en) * 1985-01-11 1987-03-10 Angelchik Jean P Peroral apparatus for morbid obesity treatment
US4694827A (en) * 1986-01-14 1987-09-22 Weiner Brian C Inflatable gastric device for treating obesity and method of using the same
US4723893A (en) * 1985-07-10 1988-02-09 501 Komatsu Zenoah Company Portable blower
US4739758A (en) * 1986-05-19 1988-04-26 Criticare Systems, Inc. Apparatus for stomach cavity reduction
US4795463A (en) * 1984-10-03 1989-01-03 Baylor College Of Medicine Labeled breast prosthesis and methods for detecting and predicting rupture of the prosthesis
US4899747A (en) * 1981-12-10 1990-02-13 Garren Lloyd R Method and appartus for treating obesity
US4908011A (en) * 1986-05-22 1990-03-13 Ballobes Aps Method and device for performing a puncturing work on an inflated balloon-like object implanted in a patient
US5081422A (en) * 1990-09-07 1992-01-14 Ishiang Shih Methods for roof, wall or floor leak detection
US5084061A (en) * 1987-09-25 1992-01-28 Gau Fred C Intragastric balloon with improved valve locating means
US5234454A (en) * 1991-08-05 1993-08-10 Akron City Hospital Percutaneous intragastric balloon catheter and method for controlling body weight therewith
US5259399A (en) * 1992-03-02 1993-11-09 Alan Brown Device and method of causing weight loss using removable variable volume intragastric bladder
US5476005A (en) * 1993-07-09 1995-12-19 Siemens Elema Ab Method and apparatus for tracing leaks in vivo occurring in an electrode device of an implanted medical apparatus
US5579765A (en) * 1995-05-30 1996-12-03 Cox; Danny L. Monitor to detect bleeding
US5833603A (en) * 1996-03-13 1998-11-10 Lipomatrix, Inc. Implantable biosensing transponder
US5850144A (en) * 1997-09-03 1998-12-15 Serrot Corporation Method for detecting leaks in a membrane
US5993473A (en) * 1997-11-19 1999-11-30 Chan; Yung C. Expandable body device for the gastric cavity and method
US20010001314A1 (en) * 1997-06-13 2001-05-17 Arthrocare Corporation Electrosurgical systems and methods for recanalization of occluded body lumens
US6272914B1 (en) * 1998-08-05 2001-08-14 Freni Brembo, S.P.A. Device for indicating caliper pad wear in disc brakes
US20010051766A1 (en) * 1999-03-01 2001-12-13 Gazdzinski Robert F. Endoscopic smart probe and method
US20020011934A1 (en) * 2000-04-12 2002-01-31 Paul Cacioli Communicative glove containing embedded microchip
US20020055757A1 (en) * 2000-11-03 2002-05-09 Torre Roger De La Method and device for use in minimally invasive placement of intragastric devices
US6427089B1 (en) * 1999-02-19 2002-07-30 Edward W. Knowlton Stomach treatment apparatus and method
US6454785B2 (en) * 2000-02-24 2002-09-24 DE HOYOS GARZA ANDRéS Percutaneous intragastric balloon catheter for the treatment of obesity
US6579301B1 (en) * 2000-11-17 2003-06-17 Syntheon, Llc Intragastric balloon device adapted to be repeatedly varied in volume without external assistance
US20030171768A1 (en) * 2002-03-07 2003-09-11 Mcghan Jim J. Self-deflating intragastric balloon
US6634216B1 (en) * 1998-07-10 2003-10-21 Joven Denki Kabushiki Kaisha Inspection method for sealed package
US6647762B1 (en) * 1998-03-05 2003-11-18 Palmer Environmental Limited Detecting leaks in pipes
US6656194B1 (en) * 2002-11-05 2003-12-02 Satiety, Inc. Magnetic anchoring devices
US20040044357A1 (en) * 2002-08-30 2004-03-04 James Gannoe Stented anchoring of gastric space-occupying devices
US20040059289A1 (en) * 2001-03-09 2004-03-25 Jose Rafael Garza Alvarez Intragastric balloon assembly
US6736793B2 (en) * 1999-02-02 2004-05-18 Ams Research Corporation Self-sealing detachable balloon
US20040102712A1 (en) * 2002-11-25 2004-05-27 Andres Belalcazar Impedance monitoring for detecting pulmonary edema and thoracic congestion
US20040106899A1 (en) * 2002-11-30 2004-06-03 Mcmichael Donald J. Gastric balloon catheter with improved balloon orientation
US6746460B2 (en) * 2002-08-07 2004-06-08 Satiety, Inc. Intra-gastric fastening devices
US20040122526A1 (en) * 2002-12-23 2004-06-24 Imran Mir A. Stomach prosthesis
US20040122527A1 (en) * 2002-12-23 2004-06-24 Imran Mir A. Implantable digestive tract organ
US20040162593A1 (en) * 2000-01-19 2004-08-19 Medtronic, Inc. Implantable lead functional status monitor and method
US20040162613A1 (en) * 2003-02-06 2004-08-19 Thomas Roballey Cosmetic and reconstructive prosthesis containing a biologically compatible rupture indicator
US20040186503A1 (en) * 2003-03-17 2004-09-23 Delegge Rebecca Intragastric catheter
US20040186502A1 (en) * 2003-03-19 2004-09-23 Sampson Douglas C. Self-Inflating intragastric volume-occupying device
US20050033331A1 (en) * 2003-07-28 2005-02-10 Polymorfix, Inc., C/O Medventure Associates Pyloric valve obstructing devices and methods
US20050055039A1 (en) * 2003-07-28 2005-03-10 Polymorfix, Inc. Devices and methods for pyloric anchoring
US20050096719A1 (en) * 2003-10-31 2005-05-05 Eric Hammill Implantable leads permitting functional status monitoring
US20050107664A1 (en) * 2000-03-24 2005-05-19 Kalloo Anthony N. Methods and devices for diagnostic and therapeutic interventions in the peritoneal cavity
US20050149186A1 (en) * 2003-02-06 2005-07-07 Rfs Health Sciences, Inc. Cosmetic and reconstructive prosthesis containing a biologically compatible rupture indicator
US20050159800A1 (en) * 2004-01-16 2005-07-21 Medtronic, Inc. Novel implantable lead including sensor
US20050159801A1 (en) * 2004-01-16 2005-07-21 Medtronic, Inc. Novel implantable lead including sensor
US20050181977A1 (en) * 2003-11-10 2005-08-18 Angiotech International Ag Medical implants and anti-scarring agents
US20050192614A1 (en) * 2004-02-26 2005-09-01 Binmoeller Kenneth F. Method and apparatus for reducing obesity
US20050273060A1 (en) * 2004-06-03 2005-12-08 Mayo Foundation For Medical Education And Research Obesity treatment and device
US20050275553A1 (en) * 2004-06-10 2005-12-15 David Weekes Systems and apparatus for secure shipping
US20060004272A1 (en) * 2003-11-13 2006-01-05 Rajiv Shah Long term analyte sensor array
US20060020314A1 (en) * 2004-07-23 2006-01-26 Cardiac Pacemakers, Inc. Systems and methods for characterizing leads
US7066945B2 (en) * 2001-05-17 2006-06-27 Wilson-Cook Medical Inc. Intragastric device for treating obesity
US20060178691A1 (en) * 2004-02-26 2006-08-10 Binmoeller Kenneth F Methods and devices to curb appetite and/or reduce food intake
US8070807B2 (en) * 2004-11-19 2011-12-06 Fulfillium, Inc. Wireless breach detection

Family Cites Families (74)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3934274A (en) 1974-10-29 1976-01-27 Hartley Jr John H Deflatable mammary augmentation prosthesis
US4472226A (en) 1979-10-03 1984-09-18 Minnesota Mining And Manufacturing Company Silicone gel filled prosthesis
US4311146A (en) 1980-05-08 1982-01-19 Sorenson Research Co., Inc. Detachable balloon catheter apparatus and method
US4773909A (en) 1981-10-06 1988-09-27 Memorial Hospital For Cancer And Allied Diseases Multi-lumen high profile mammary implant
DK13881A (en) 1981-01-14 1982-07-15 O G Nien Procedure and device for setting down inflation and leaving a foreign object detached in mavesaekken on man
DE3206118A1 (en) 1982-02-19 1983-11-03 J J Mccloy K C Eicke Ltd Device for reducing the stomach reservoir having a intragastrically administered cushion
EP0103481A1 (en) 1982-09-14 1984-03-21 Ainsworth Nominees Proprietary Limited Treatment and reduction of obesity in humans
GB2139902B (en) 1983-05-17 1986-12-31 Louis Roger Celestin Balloon introducer apparatus
US4517979A (en) * 1983-07-14 1985-05-21 Cordis Corporation Detachable balloon catheter
US4577640A (en) 1984-03-20 1986-03-25 Hofmeister John F Method and apparatus for direct in vivo monitoring of uterine electrical activity
US4726893A (en) * 1984-04-27 1988-02-23 Phillips Petroleum Company Catalytic crackins process control
US4651717A (en) 1985-04-04 1987-03-24 Dow Corning Corporation Multiple envelope tissue expander device
US4824436A (en) * 1985-04-09 1989-04-25 Harvey Wolinsky Method for the prevention of restenosis
US4598699A (en) 1985-06-10 1986-07-08 Garren Lloyd R Endoscopic instrument for removing stomach insert
GB8517092D0 (en) 1985-07-05 1985-08-14 Taylor T V Artificial bezoar
EP0246999A1 (en) 1986-05-23 1987-11-25 Omikron Scientific Ltd. Device and method of making same for treating a patient for obesity
WO1988000027A1 (en) 1986-07-09 1988-01-14 Angelchik Jean P Method for treatment of morbid obesity
US4790848A (en) 1987-11-27 1988-12-13 Dow Corning Wright Breast prosthesis with multiple lumens
US5282856A (en) 1987-12-22 1994-02-01 Ledergerber Walter J Implantable prosthetic device
US6228116B1 (en) 1987-12-22 2001-05-08 Walter J. Ledergerber Tissue expander
US4925446A (en) 1988-07-06 1990-05-15 Transpharm Group Inc. Removable inflatable intragastrointestinal device for delivering beneficial agents
US4983167A (en) 1988-11-23 1991-01-08 Harvinder Sahota Balloon catheters
US5160321A (en) 1988-11-23 1992-11-03 Harvinder Sahota Balloon catheters
US5308317A (en) 1990-06-07 1994-05-03 Arch Development Corporation Protective tube laser endoscopy
US5400770A (en) 1992-01-15 1995-03-28 Nakao; Naomi L. Device utilizable with endoscope and related method
US5401241A (en) 1992-05-07 1995-03-28 Inamed Development Co. Duodenal intubation catheter
US5501667A (en) 1994-03-15 1996-03-26 Cordis Corporation Perfusion balloon and method of use and manufacture
US5653683A (en) 1995-02-28 1997-08-05 D'andrea; Mark A. Intracavitary catheter for use in therapeutic radiation procedures
US5865801A (en) 1995-07-18 1999-02-02 Houser; Russell A. Multiple compartmented balloon catheter with external pressure sensing
US6785576B2 (en) 1997-04-21 2004-08-31 Medtronic, Inc. Medical electrical lead
EP0973574B1 (en) 1997-04-07 2004-01-28 Cook Urological Inc. Back-up retention member drainage catheter
US5833693A (en) 1997-05-02 1998-11-10 Abrahami; Israel Drill guide
US20010020150A1 (en) 1998-02-06 2001-09-06 Biagio Ravo Inflatable intraluminal molding device
US7470228B2 (en) 2000-04-14 2008-12-30 Attenuex Technologies, Inc. Method of treating benign hypertrophy of the prostate
US6434785B1 (en) 2000-04-19 2002-08-20 Headwaters Research & Development, Inc Dual filter wet/dry hand-held vacuum cleaner
JP3977983B2 (en) 2000-07-31 2007-09-19 株式会社タニタ Dehydrated state determining apparatus according to the bioelectrical impedance measurement
US6605056B2 (en) 2001-07-11 2003-08-12 Scimed Life Systems, Inc. Conformable balloon
US6755869B2 (en) 2001-11-09 2004-06-29 Boston Scientific Corporation Intragastric prosthesis for the treatment of morbid obesity
US6755861B2 (en) 2001-10-16 2004-06-29 Granit Medical Innovation, Inc. Device for providing a portion of an organism with a desired shape
FR2834202B1 (en) 2001-12-28 2004-03-19 Cie Euro Etude Rech Paroscopie intra-gastric balloon has multiple pockets, surgical device for expansion of said balloon and method of manufacturing corresponding
US20030153905A1 (en) 2002-01-25 2003-08-14 Edwards Stuart Denzil Selective ablation system
GB2384993B (en) 2002-02-06 2004-05-12 David Alan Burt Medical surgeons detection aid
US20030163197A1 (en) 2002-02-28 2003-08-28 David Chen Detachable multi-chamber breast form with permanently grown adhesive
US20090048624A1 (en) 2004-11-02 2009-02-19 Alverdy John C Balloon system and methods for treating obesity
CA2484838C (en) 2002-05-09 2012-08-28 Applied Medical Resources Corporation Balloon system and methods for treating obesity
US8845672B2 (en) 2002-05-09 2014-09-30 Reshape Medical, Inc. Balloon system and methods for treating obesity
US20050261719A1 (en) 2002-11-25 2005-11-24 Israel Chermoni Catheter and method of its use
FR2852821B1 (en) 2003-03-31 2007-06-01 Cie Euro Etude Rech Paroscopie intragastric balloon parylene coating, method for making such a ball and use of parylene to upholster an intragastric balloon
US7065411B2 (en) 2003-04-23 2006-06-20 Medtronic, Inc. Electrical medical leads employing conductive aerogel
US6994095B2 (en) * 2003-07-28 2006-02-07 Medventure Associates Iv Pyloric valve corking device and method
US7041080B2 (en) 2003-08-01 2006-05-09 Medtronic Vascular, Inc. Rotary valve for balloon catheter
US7303574B2 (en) 2003-08-07 2007-12-04 Medtronic Vasculor, Inc. Occlusion catheter with frictional valve
US8192455B2 (en) 2003-08-13 2012-06-05 Board Of Supervisors Of Louisiana State University And Agricultural And Mechanical College Compressive device for percutaneous treatment of obesity
US20050070937A1 (en) 2003-09-30 2005-03-31 Jambor Kristin L. Segmented gastric band
US6826948B1 (en) 2003-10-09 2004-12-07 Delphi Technologies, Inc. Leak detection apparatus for a liquid circulation cooling system
US7758493B2 (en) 2003-10-23 2010-07-20 Proxy Biomedical Limited Gastric constriction device
US7135034B2 (en) 2003-11-14 2006-11-14 Lumerx, Inc. Flexible array
US7289851B2 (en) 2003-12-04 2007-10-30 Medtronic, Inc. Method and apparatus for identifying lead-related conditions using impedance trends and oversensing criteria
US8236023B2 (en) 2004-03-18 2012-08-07 Allergan, Inc. Apparatus and method for volume adjustment of intragastric balloons
EP1744804A4 (en) 2004-05-03 2009-11-04 Fulfillium Inc Method and system for gastric volume control
US20080262529A1 (en) 2004-05-14 2008-10-23 C.R. Bard, Inc. Gastric Balloon Devices and Methods of Use
US7112186B2 (en) 2004-05-26 2006-09-26 Shah Tilak M Gastro-occlusive device
US20060155259A1 (en) 2005-01-13 2006-07-13 Maclay Alistair Stomach balloon that can be inserted and removed via mouth
JP4777017B2 (en) 2005-08-24 2011-09-21 オリンパスメディカルシステムズ株式会社 Intragastric retention balloon and balloon medium
US20070100369A1 (en) 2005-10-31 2007-05-03 Cragg Andrew H Intragastric space filler
US20070100368A1 (en) 2005-10-31 2007-05-03 Quijano Rodolfo C Intragastric space filler
US8142469B2 (en) 2007-06-25 2012-03-27 Reshape Medical, Inc. Gastric space filler device, delivery system, and related methods
US20100100115A1 (en) 2008-10-20 2010-04-22 Wilson-Cook Medical Inc. Foam filled intragastric balloon for treating obesity
US20110060358A1 (en) 2009-09-04 2011-03-10 Stokes Michael J Methods and implants for inducing satiety in the treatment of obesity
US9149611B2 (en) 2010-02-08 2015-10-06 Reshape Medical, Inc. Materials and methods for improved intragastric balloon devices
WO2014055766A1 (en) 2012-10-04 2014-04-10 Apollo Endosurgery, Inc. Intragastric balloon for treating obesity
ES2566498T3 (en) 2010-10-18 2016-04-13 Apollo Endosurgery, Inc. intragastric implants with duodenal anchors
WO2013039412A1 (en) 2011-09-14 2013-03-21 PULSMED sp. zo.o. The method of filling an intragastric balloon
US9833350B2 (en) 2013-03-15 2017-12-05 Ez-Off Weightloss, Llc Anchorable size-varying gastric balloons for weight loss

Patent Citations (73)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2752590A (en) * 1954-03-01 1956-06-26 Specialties Dev Corp Insulation failure detector for electric cables
US2792568A (en) * 1955-03-04 1957-05-14 Specialties Dev Corp Network for detecting the failure of the insulation of electrically conductive cables
US3046988A (en) * 1958-12-01 1962-07-31 Davol Rubber Co Esophageal nasogastric tube
US3055371A (en) * 1958-12-23 1962-09-25 Kulick George Device for regulation and control of esophago-gastric balloons
US3906959A (en) * 1974-02-14 1975-09-23 American Optical Corp Liquid leak stop for an implantable heart pacer
US4133315A (en) * 1976-12-27 1979-01-09 Berman Edward J Method and apparatus for reducing obesity
US4557640A (en) * 1978-03-13 1985-12-10 Rottler Donald B Combination boring and honing apparatus and method
US4501264A (en) * 1978-06-02 1985-02-26 Rockey Arthur G Medical sleeve
US4246893A (en) * 1978-07-05 1981-01-27 Daniel Berson Inflatable gastric device for treating obesity
US4455691A (en) * 1979-10-03 1984-06-26 Minnesota Mining And Manufacturing Company Silicone gel filled prosthesis
US4386231A (en) * 1980-04-30 1983-05-31 Canada Wire And Cable Limited Cable assembly for detecting the ingress of water inside a cable
US4416267A (en) * 1981-12-10 1983-11-22 Garren Lloyd R Method and apparatus for treating obesity
US4899747A (en) * 1981-12-10 1990-02-13 Garren Lloyd R Method and appartus for treating obesity
US4485805A (en) * 1982-08-24 1984-12-04 Gunther Pacific Limited Of Hong Kong Weight loss device and method
US4607618A (en) * 1983-02-23 1986-08-26 Angelchik Jean P Method for treatment of morbid obesity
US4795463A (en) * 1984-10-03 1989-01-03 Baylor College Of Medicine Labeled breast prosthesis and methods for detecting and predicting rupture of the prosthesis
US4648383A (en) * 1985-01-11 1987-03-10 Angelchik Jean P Peroral apparatus for morbid obesity treatment
US4723893A (en) * 1985-07-10 1988-02-09 501 Komatsu Zenoah Company Portable blower
US4694827A (en) * 1986-01-14 1987-09-22 Weiner Brian C Inflatable gastric device for treating obesity and method of using the same
US4739758A (en) * 1986-05-19 1988-04-26 Criticare Systems, Inc. Apparatus for stomach cavity reduction
US4908011A (en) * 1986-05-22 1990-03-13 Ballobes Aps Method and device for performing a puncturing work on an inflated balloon-like object implanted in a patient
US5084061A (en) * 1987-09-25 1992-01-28 Gau Fred C Intragastric balloon with improved valve locating means
US5081422A (en) * 1990-09-07 1992-01-14 Ishiang Shih Methods for roof, wall or floor leak detection
US5234454A (en) * 1991-08-05 1993-08-10 Akron City Hospital Percutaneous intragastric balloon catheter and method for controlling body weight therewith
US5259399A (en) * 1992-03-02 1993-11-09 Alan Brown Device and method of causing weight loss using removable variable volume intragastric bladder
US5476005A (en) * 1993-07-09 1995-12-19 Siemens Elema Ab Method and apparatus for tracing leaks in vivo occurring in an electrode device of an implanted medical apparatus
US5579765A (en) * 1995-05-30 1996-12-03 Cox; Danny L. Monitor to detect bleeding
US5833603A (en) * 1996-03-13 1998-11-10 Lipomatrix, Inc. Implantable biosensing transponder
US20010001314A1 (en) * 1997-06-13 2001-05-17 Arthrocare Corporation Electrosurgical systems and methods for recanalization of occluded body lumens
US6855143B2 (en) * 1997-06-13 2005-02-15 Arthrocare Corporation Electrosurgical systems and methods for recanalization of occluded body lumens
US5850144A (en) * 1997-09-03 1998-12-15 Serrot Corporation Method for detecting leaks in a membrane
US5993473A (en) * 1997-11-19 1999-11-30 Chan; Yung C. Expandable body device for the gastric cavity and method
US6647762B1 (en) * 1998-03-05 2003-11-18 Palmer Environmental Limited Detecting leaks in pipes
US6634216B1 (en) * 1998-07-10 2003-10-21 Joven Denki Kabushiki Kaisha Inspection method for sealed package
US6272914B1 (en) * 1998-08-05 2001-08-14 Freni Brembo, S.P.A. Device for indicating caliper pad wear in disc brakes
US6736793B2 (en) * 1999-02-02 2004-05-18 Ams Research Corporation Self-sealing detachable balloon
US6427089B1 (en) * 1999-02-19 2002-07-30 Edward W. Knowlton Stomach treatment apparatus and method
US20010051766A1 (en) * 1999-03-01 2001-12-13 Gazdzinski Robert F. Endoscopic smart probe and method
US20040162593A1 (en) * 2000-01-19 2004-08-19 Medtronic, Inc. Implantable lead functional status monitor and method
US6454785B2 (en) * 2000-02-24 2002-09-24 DE HOYOS GARZA ANDRéS Percutaneous intragastric balloon catheter for the treatment of obesity
US20050107664A1 (en) * 2000-03-24 2005-05-19 Kalloo Anthony N. Methods and devices for diagnostic and therapeutic interventions in the peritoneal cavity
US20020011934A1 (en) * 2000-04-12 2002-01-31 Paul Cacioli Communicative glove containing embedded microchip
US7033373B2 (en) * 2000-11-03 2006-04-25 Satiety, Inc. Method and device for use in minimally invasive placement of space-occupying intragastric devices
US20020055757A1 (en) * 2000-11-03 2002-05-09 Torre Roger De La Method and device for use in minimally invasive placement of intragastric devices
US6579301B1 (en) * 2000-11-17 2003-06-17 Syntheon, Llc Intragastric balloon device adapted to be repeatedly varied in volume without external assistance
US20040059289A1 (en) * 2001-03-09 2004-03-25 Jose Rafael Garza Alvarez Intragastric balloon assembly
US7066945B2 (en) * 2001-05-17 2006-06-27 Wilson-Cook Medical Inc. Intragastric device for treating obesity
US6733512B2 (en) * 2002-03-07 2004-05-11 Mcghan Jim J. Self-deflating intragastric balloon
US20030171768A1 (en) * 2002-03-07 2003-09-11 Mcghan Jim J. Self-deflating intragastric balloon
US6746460B2 (en) * 2002-08-07 2004-06-08 Satiety, Inc. Intra-gastric fastening devices
US20040044357A1 (en) * 2002-08-30 2004-03-04 James Gannoe Stented anchoring of gastric space-occupying devices
US6656194B1 (en) * 2002-11-05 2003-12-02 Satiety, Inc. Magnetic anchoring devices
US20040102712A1 (en) * 2002-11-25 2004-05-27 Andres Belalcazar Impedance monitoring for detecting pulmonary edema and thoracic congestion
US20040106899A1 (en) * 2002-11-30 2004-06-03 Mcmichael Donald J. Gastric balloon catheter with improved balloon orientation
US20040122527A1 (en) * 2002-12-23 2004-06-24 Imran Mir A. Implantable digestive tract organ
US20040122526A1 (en) * 2002-12-23 2004-06-24 Imran Mir A. Stomach prosthesis
US20050149186A1 (en) * 2003-02-06 2005-07-07 Rfs Health Sciences, Inc. Cosmetic and reconstructive prosthesis containing a biologically compatible rupture indicator
US20040162613A1 (en) * 2003-02-06 2004-08-19 Thomas Roballey Cosmetic and reconstructive prosthesis containing a biologically compatible rupture indicator
US20040186503A1 (en) * 2003-03-17 2004-09-23 Delegge Rebecca Intragastric catheter
US20040186502A1 (en) * 2003-03-19 2004-09-23 Sampson Douglas C. Self-Inflating intragastric volume-occupying device
US20050055039A1 (en) * 2003-07-28 2005-03-10 Polymorfix, Inc. Devices and methods for pyloric anchoring
US20050033331A1 (en) * 2003-07-28 2005-02-10 Polymorfix, Inc., C/O Medventure Associates Pyloric valve obstructing devices and methods
US20050096719A1 (en) * 2003-10-31 2005-05-05 Eric Hammill Implantable leads permitting functional status monitoring
US20050181977A1 (en) * 2003-11-10 2005-08-18 Angiotech International Ag Medical implants and anti-scarring agents
US20060004272A1 (en) * 2003-11-13 2006-01-05 Rajiv Shah Long term analyte sensor array
US20050159800A1 (en) * 2004-01-16 2005-07-21 Medtronic, Inc. Novel implantable lead including sensor
US20050159801A1 (en) * 2004-01-16 2005-07-21 Medtronic, Inc. Novel implantable lead including sensor
US20060178691A1 (en) * 2004-02-26 2006-08-10 Binmoeller Kenneth F Methods and devices to curb appetite and/or reduce food intake
US20050192614A1 (en) * 2004-02-26 2005-09-01 Binmoeller Kenneth F. Method and apparatus for reducing obesity
US20050273060A1 (en) * 2004-06-03 2005-12-08 Mayo Foundation For Medical Education And Research Obesity treatment and device
US20050275553A1 (en) * 2004-06-10 2005-12-15 David Weekes Systems and apparatus for secure shipping
US20060020314A1 (en) * 2004-07-23 2006-01-26 Cardiac Pacemakers, Inc. Systems and methods for characterizing leads
US8070807B2 (en) * 2004-11-19 2011-12-06 Fulfillium, Inc. Wireless breach detection

Cited By (37)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8070807B2 (en) 2004-11-19 2011-12-06 Fulfillium, Inc. Wireless breach detection
US20060111777A1 (en) * 2004-11-19 2006-05-25 Fulfillium, Inc. Wireless breach detection
US20110015666A1 (en) * 2005-03-01 2011-01-20 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
US8267888B2 (en) 2005-03-01 2012-09-18 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
US8864784B2 (en) 2005-03-01 2014-10-21 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
US8845673B2 (en) 2005-03-01 2014-09-30 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants and methods for use thereof
US20110015665A1 (en) * 2005-03-01 2011-01-20 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
US20110022072A1 (en) * 2005-03-01 2011-01-27 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
US8858496B2 (en) 2005-03-01 2014-10-14 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
US20060271118A1 (en) * 2005-05-25 2006-11-30 Cardiac Pacemakers, Inc. Implantable neural stimulator with mode switching
US9486631B2 (en) 2005-05-25 2016-11-08 Cardiac Pacemakers, Inc. Vagal nerve stimulator with mode switching
US8768456B2 (en) 2005-05-25 2014-07-01 Cardiac Pacemakers, Inc. Implantable neural stimulator with mode switching
US8473049B2 (en) 2005-05-25 2013-06-25 Cardiac Pacemakers, Inc. Implantable neural stimulator with mode switching
WO2007128133A1 (en) * 2006-05-09 2007-11-15 David James Haddon Hair sequestered tracer for prosthesis leak detection
US20090012372A1 (en) * 2006-06-12 2009-01-08 Novalert, Inc. External sensing for implant rupture
US20080109027A1 (en) * 2006-08-01 2008-05-08 Fulfillium, Inc. Method and system for gastric volume control
WO2008055229A3 (en) * 2006-10-31 2008-08-07 Daniel Burnett External sensing for implant rupture
WO2008055229A2 (en) 2006-10-31 2008-05-08 Novalert, Inc. External sensing for implant rupture
US20110098576A1 (en) * 2009-12-01 2011-04-28 Hollstien David S Non-invasive implant rupture detection system
WO2011068906A1 (en) * 2009-12-01 2011-06-09 David Stuart Hollstien Non-invasive implant rupture detection system
US9113844B2 (en) 2009-12-01 2015-08-25 David S. Hollstien Non-invasive implant rupture detection system
US9504576B2 (en) 2011-01-13 2016-11-29 Sensurtec, Inc. Breach detection in solid structures
CN103619285A (en) * 2011-01-13 2014-03-05 森舒泰克公司 Breach detection in solid structures
WO2012097225A3 (en) * 2011-01-13 2013-11-14 Sensurtec, Inc. Breach detection in solid structures
WO2012097225A2 (en) 2011-01-13 2012-07-19 Sensurtec, Inc. Breach detection in solid structures
US8963708B2 (en) 2011-01-13 2015-02-24 Sensurtec, Inc. Breach detection in solid structures
EP2677975A4 (en) * 2011-01-13 2015-05-27 Sensurtec Inc Breach detection in solid structures
US9026213B2 (en) 2011-08-12 2015-05-05 Cardiac Pacemakers, Inc. Medical device lead with conductor fracture prediction
CN103732289A (en) * 2011-08-12 2014-04-16 心脏起搏器股份公司 Medical device lead with conductor fracture prediction
WO2013025299A1 (en) * 2011-08-12 2013-02-21 Cardiac Pacemakers, Inc. Medical device lead with conductor fracture prediction
WO2013188425A2 (en) 2012-06-13 2013-12-19 Elwha Llc Breast implant with analyte sensors and internal power source
US9333071B2 (en) 2012-06-13 2016-05-10 Elwha Llc Breast implant with regionalized analyte sensors and internal power source
US9339372B2 (en) 2012-06-13 2016-05-17 Elwha Llc Breast implant with regionalized analyte sensors responsive to external power source
US9326730B2 (en) 2012-06-13 2016-05-03 Elwha Llc Breast implant with covering and analyte sensors responsive to external power source
EP2861185A4 (en) * 2012-06-13 2015-12-16 Elwha Llc Breast implant with analyte sensors and internal power source
EP3298962A1 (en) 2016-09-23 2018-03-28 Biosense Webster (Israel), Ltd. Detection of leakage in implants
US9959739B1 (en) * 2016-10-28 2018-05-01 Nantin Enterprise Limited System, method and article for indicating a wet or dry condition to a user

Also Published As

Publication number Publication date Type
JP4839321B2 (en) 2011-12-21 grant
WO2006055839A3 (en) 2006-08-24 application
US20160100800A1 (en) 2016-04-14 application
JP2008520374A (en) 2008-06-19 application
US8070807B2 (en) 2011-12-06 grant
EP1811920A2 (en) 2007-08-01 application
WO2006055839A2 (en) 2006-05-26 application
US20060111777A1 (en) 2006-05-25 application
US9445930B2 (en) 2016-09-20 grant
EP1811920A4 (en) 2010-04-07 application

Similar Documents

Publication Publication Date Title
US3575158A (en) Method of controlling urine flow from the bladder with an inplantable pump
US3236240A (en) Implantable bladder stimulator
US7480532B2 (en) Baroreflex activation for pain control, sedation and sleep
US7371215B2 (en) Endoscopic instrument for engaging a device
US5565005A (en) Implantable growth tissue stimulator and method operation
US6432040B1 (en) Implantable esophageal sphincter apparatus for gastroesophageal reflux disease and method
US6210347B1 (en) Remote control food intake restriction device
US6659936B1 (en) Method and apparatus for treating incontinence
US7083578B2 (en) Device and method for examining a body lumen
US6821154B1 (en) Electrical device connector and method therefor
US5551953A (en) Electrotransport system with remote telemetry link
US20090082644A1 (en) Devices, Systems, Kits and Methods for Treatment of Obesity
US7899541B2 (en) Systems and methods for implantable leadless gastrointestinal tissue stimulation
US6733512B2 (en) Self-deflating intragastric balloon
US20070100368A1 (en) Intragastric space filler
US20070100367A1 (en) Intragastric space filler
US6486588B2 (en) Acoustic biosensor for monitoring physiological conditions in a body implantation site
US20050070974A1 (en) Obesity and eating disorder stimulation treatment with neural block
US6319191B1 (en) Implantable body fluid flow control device
EP1128871B1 (en) Monitoring treatment using implantable telemetric sensors
US20080065169A1 (en) Endoscopic Instrument for Engaging a Device
US20060074458A1 (en) Digestive organ retention device
US6475170B1 (en) Acoustic biosensor for monitoring physiological conditions in a body implantation site
US20030139782A1 (en) FES stimulator
US6417777B2 (en) Pressure sensitive mat with breathing tube apparatus

Legal Events

Date Code Title Description
AS Assignment

Owner name: SENSURTEC, INC., CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:CHEN, RICHARD D.Y.;REEL/FRAME:030914/0109

Effective date: 20130719