US20100185049A1 - Dome and screw valves for remotely adjustable gastric banding systems - Google Patents

Dome and screw valves for remotely adjustable gastric banding systems Download PDF

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Publication number
US20100185049A1
US20100185049A1 US12712952 US71295210A US2010185049A1 US 20100185049 A1 US20100185049 A1 US 20100185049A1 US 12712952 US12712952 US 12712952 US 71295210 A US71295210 A US 71295210A US 2010185049 A1 US2010185049 A1 US 2010185049A1
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Prior art keywords
valve
implantable device
fluid
actuator
screw
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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
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US12712952
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Janel Birk
Robert E. Hoyt, JR.
Sean Snow
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Allergan Inc
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Allergan Inc
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    • 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
    • A61F5/005Gastric bands
    • A61F5/0053Gastric bands remotely adjustable
    • A61F5/0059Gastric bands remotely adjustable with wireless means
    • 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
    • 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
    • A61F5/005Gastric bands
    • A61F5/0053Gastric bands remotely adjustable
    • A61F5/0056Gastric bands remotely adjustable using injection ports
    • 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
    • A61F5/005Gastric bands
    • A61F5/0066Closing devices for gastric bands
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00Fluid handling
    • Y10T137/7287Liquid level responsive or maintaining systems
    • Y10T137/7358By float controlled valve
    • Y10T137/7368Servo relay operation of control
    • Y10T137/7371Fluid pressure
    • Y10T137/7374Flexible diaphragm valve
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00Fluid handling
    • Y10T137/8593Systems
    • Y10T137/877With flow control means for branched passages
    • Y10T137/87708With common valve operator
    • Y10T137/87716For valve having a flexible diaphragm valving member

Abstract

An implantable device controls the movement of fluid to an inflatable portion of a gastric band. The implantable device includes a body. The body has an inlet, an outlet and a valve seat positioned between the inlet and the outlet. The body defines a fluid passage from the inlet to the outlet. The implantable device also includes a diaphragm. The diaphragm has one or more edges coupled to the body. The diaphragm is made of an elastomeric material and capable of being moved between a closed position that blocks the valve seat and does not allow the fluid to move from the inlet to the outlet and an open position that does not block the valve seat and allows the fluid to move from the inlet to the outlet.

Description

    CROSS REFERENCE TO RELATED APPLICATIONS
  • This application is a continuation-in-part of U.S. patent application Ser. No. 12/603,058, filed Oct. 21, 2009, which claims the benefit of U.S. provisional patent application No. 61/107,576, filed Oct. 22, 2008, the entire disclosure of each of these applications are incorporated herein by reference.
  • FIELD
  • The present invention generally relates to medical systems and apparatus and uses thereof for treating obesity and/or obesity-related diseases, and more specifically, relates to dome and screw valves for remotely adjustable gastric banding systems.
  • BACKGROUND
  • Adjustable, gastric banding systems provide an effective and substantially less invasive alternative to gastric bypass surgery and other conventional surgical weight loss procedures. Despite the sustained weight loss of invasive weight loss procedures, such as gastric bypass surgery, it has been recognized that sustained weight loss can also be achieved through a laparoscopically-placed gastric band, for example, the LAP-BAND® (Allergan, Inc., Irvine, Calif.) gastric band or the LAP-BAND AP® (Allergan, Inc., Irvine, Calif.) gastric band. Generally, gastric bands are placed about the cardia, or upper portion, of a patient's stomach forming a stoma that restricts the food's passage into a lower portion of the stomach. When the stoma is of an appropriate size that is restricted by a gastric band, food held in the upper portion of the stomach provides a feeling of satiety or fullness that discourages overeating. Unlike gastric bypass surgery procedures, adjustable gastric banding systems are reversible and require no permanent modification to the gastrointestinal tract.
  • Over time, a stoma created by the gastric band may need an adjustment in order to maintain an appropriate size, which is neither too restrictive nor too passive. Prior art gastric banding systems provide a subcutaneous fluid access port connected to an expandable or inflatable portion of the gastric band. By adding fluid to or removing fluid from the inflatable portion by means of a hypodermic needle inserted into the fluid access port, the effective size of the gastric band can be adjusted to provide a tighter or looser constriction.
  • It would be desirable to allow for non-invasive adjustment of gastric band constriction, for example, without the use of the hypodermic needle. Thus, remotely adjustable gastric banding systems capable of non-invasive adjustment are desired and described herein.
  • SUMMARY
  • In one example embodiment of the present invention, there is an implantable device that controls the movement of fluid to an inflatable portion of a gastric band. The implantable device includes a body. The body has an inlet, an outlet and a valve seat positioned between the inlet and the outlet. The body defines a fluid passage from the inlet to the outlet.
  • The implantable device also includes a diaphragm. The diaphragm has one or more edges coupled to the body. The diaphragm is made of an elastomeric material and capable of being moved between a closed position that blocks the valve seat and does not allow the fluid to move from the inlet to the outlet and an open position that does not block the valve seat and allows the fluid to move from the inlet to the outlet.
  • The implantable device also includes an actuator. The actuator is configured to apply a force on the diaphragm causing the diaphragm to move from the closed position to the open position. The implantable device also includes a microcontroller coupled to the actuator, the microcontroller configured to receive a telemetric signal from a remote transmitter and control the actuator based on the telemetric signal.
  • In another example embodiment of the present invention, there is an implantable device that controls the movement of fluid to an inflatable portion of a gastric band. The implantable device includes a body. The body has an inlet, an outlet and a valve seat. The body defines a fluid passage from the inlet to the outlet.
  • The implantable device also includes a valve seal. The valve seal has one or more edges coupled to the body. The valve seal is made of an elastomeric material and is capable of being moved between an open position that does not block the valve seat and allows the fluid to move from the inlet to the outlet and a closed position that blocks the valve seat and does not allow the fluid to move from the inlet to the outlet.
  • The implantable device also includes an actuator. The actuator is positioned within the body. The actuator has an actuator body defining a threaded screw hole and a screw positioned within the threaded screw hole. The screw is configured to apply a force on the valve seal causing the valve seal to move from the open position to the closed position when the actuator receives a telemetric signal from an implantable microcontroller. A first telemetric signal may be used to move the valve seal from the open position to the closed position and a second telemetric signal may be used to move the valve seal from the closed position to the open position.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 illustrates a perspective view of a remotely adjustable gastric banding system according to an embodiment of the present invention.
  • FIG. 2 illustrates an example configuration of the internal components of the high precision pump unit illustrated in FIG. 1 according to an embodiment of the present invention.
  • FIGS. 3A and 3B illustrate the filling and draining, respectively, of a gastric band using the systems described herein according to an embodiment of the present invention.
  • FIGS. 4A and 4B illustrate cross-sectional views of an exemplary valve in a closed position and an open position according to an embodiment of the present invention.
  • FIGS. 5A and 5B illustrate cross-sectional views of an exemplary dome valve in a closed position and an open position according to an embodiment of the present invention.
  • FIGS. 6A and 6B illustrate cross-sectional views of an exemplary screw valve in a closed position and an open position according to an embodiment of the present invention.
  • FIGS. 7A, 7B and 7C illustrate side views of examples of the coupling mechanism illustrated in FIGS. 6A and 6B according to various embodiments of the present invention.
  • FIG. 8 is a flow chart of a method of controlling a dome valve according to an embodiment of the present invention.
  • FIG. 9 is a flow chart of a method of controlling a screw valve according to an embodiment of the present invention.
  • DETAILED DESCRIPTION
  • The present invention generally provides remotely adjustable gastric banding systems, for example, for treatment of obesity and obesity related conditions, as well as systems for controlling inflation of a gastric banding system.
  • Remotely adjustable gastric banding systems, otherwise referred to as a remotely adjustable band (RAB), include one or more medical devices, or a system, which allows a healthcare worker to adjust a gastric band without requiring a hypodermic needle to be inserted into an implanted access port. The RAB may use a remote transmitter to send radiofrequency signals or telemetric signals for powering and communicating with an implanted device of the RAB. The implanted device can fill or drain a gastric band of the RAB as requested by the healthcare worker via the remote transmitter. In between filling and draining adjustments to the gastric band, the volume of fluid contained in the gastric band ideally remains unchanged.
  • In one embodiment, a dome valve is used to pass and block fluid. The dome valve has an actuator that can adjust an elastomeric diaphragm (e.g., a valve seal) to an open or closed position. The dome valve can be used safely during magnetic resonance imaging (MRI) since the dome valve does not have a significant amount of ferromagnetic material. The elastomeric diaphragm is also inexpensive and robust.
  • In another embodiment, a screw valve is used to pass and block fluid. The screw valve has a screw that can adjust a valve seal to multiple precise positions, not just fully open or fully closed. The screw valve can be used in a high pressure environment since no force is required to maintain a position and because the screw can be driven to create a tight seal.
  • FIG. 1 illustrates a perspective view of a remotely adjustable gastric banding system 100 according to an embodiment of the present invention. The gastric banding system 100 includes a gastric band 102, a reservoir 104, a high precision pump unit 106, a remote transmitter 108 and tubing 110. The skin 122 of a human illustrates a separation between implantable components and non-implantable components. As illustrated, the remote transmitter 108 (e.g., a remote controller unit) is non-implantable, whereas the gastric band 102, the reservoir 104, the high precision pump unit 106, and the tubing 110 are implantable (e.g., an implantable device), and can be implanted in the human using conventional surgical techniques. The high precision pump unit 106 can be used to replace or complement a conventional access port for adjusting inflation or deflation of the gastric band 102. In some embodiments, the system includes an override port 212 which can be used, for example, with a hypodermic needle 112, to fill and drain the gastric band 102.
  • The high precision pump unit 106 is connected to the reservoir 104 and the gastric band 102 via the tubing 110, and can move precisely metered volumes of fluid (e.g., saline) in or out of the gastric band 102. Moving the fluid into the gastric band 102 causes inflation of at least one bladder, or an inflatable portion 114 (e.g., inflatable member) and constricts around the cardia, or upper portion of the stomach, forming a stoma that restricts the passage of food into a lower portion of the stomach. This stoma can provide a patient with a sensation of satiety or fullness that discourages overeating. In contrast, moving the fluid out of the inflatable portion 114 of the gastric band 102 reduces the pressure around the cardia and allows the stoma to be at least partially released and allows the human to regain a hunger sensation.
  • The high precision pump unit 106 is implanted within a patient, and therefore, is non-biodegradable. The encasement or housing of the high precision pump unit 106 may be non-hermetically sealed or hermetically sealed from the in situ environment (e.g., undisturbed environment) in the patient and formed at least partially of any rugged plastic material including, polypropylene, cyclicolephin co-polymer, nylon, and other compatible polymers and the like or at least partially formed of a non-radioopaque metal. The housing has a smooth exterior shape, with no jagged edges, to minimize foreign body response and tissue irritation. The high precision pump unit 106 is also sterilizable, in one embodiment, dry heat sterilizable before implantation.
  • The reservoir 104 may be a soft, collapsible balloon made of a biocompatible polymer material, for example, silicone, which holds a reserve of a biocompatible fluid, for example, saline, to allow for adjustments in the size of the gastric band 102. In one embodiment, the reservoir 104 is fully collapsible and can contain the extra fluid required to increase the volume of the gastric band 102 to therapeutic levels. Further, the reservoir 104 also may have excess capacity so the gastric band 102 may be fully drained into it without the reservoir 104 being filled beyond its maximum capacity.
  • The reservoir 104 may represent one or both of a source reservoir and a drain reservoir, where the source reservoir provides fluid to the gastric band 102, and the drain reservoir receives fluid from the gastric band 102.
  • The fluids used within the systems of the present invention may include any fluid that is biocompatible. The fluid has no adverse effect on the patient in the unlikely event that a leak emanates from the system. The fluid can simply be water or any biocompatible polymer oil such as caster oil. In an example embodiment, the fluid is, saline.
  • The tubing 110 is any biocompatible flexible tubing that does not degrade in vivo (e.g., within the human). The tubing 110 is configured to withstand hydraulic pressure up to about 30 psi (about 206 kPa) without leakage. This hydraulic pressure tolerance is true of the entire fluid path of the systems described herein. Although the systems described herein do not generally leak, if they do, fluid is not lost at a rate greater than about 0.2 cc/yr, or about 0.1 cc/yr.
  • Other biocompatible and biostable polymers which are useful for forming the reservoir 104 and the tubing 110 include: polyolefins, polyisobutylene and ethylene-alphaolefin copolymers; acrylic polymers and copolymers, ethylene-co-vinylacetate, polybutylmethacrylate, vinyl halide polymers and copolymers, such as polyvinyl chloride; polyvinyl ethers, such as polyvinyl methyl ether; polyvinylidene halides, such as polyvinylidene fluoride and polyvinylidene chloride; polyacrylonitrile, polyvinyl ketones; polyvinyl aromatics, such as polystyrene, polyvinyl esters, such as polyvinyl acetate; copolymers of vinyl monomers with each other and olefins, such as ethylene-methyl methacrylate copolymers, acrylonitrile-styrene copolymers, ABS resins, and ethylene-vinyl acetate copolymers; polyamides, such as Nylon 66 and polycaprolactam; alkyd resins; polycarbonates; polyoxymethylenes; polyimides; polyethers; epoxy resins, polyurethanes; rayon; rayon-triacetate; cellulose, cellulose acetate, cellulose butyrate; cellulose acetate butyrate; cellophane; cellulose nitrate; cellulose propionate; cellulose ethers; and carboxymethyl cellulose.
  • The systems and apparatus described herein further include the remote transmitter 108 (e.g., a remote controller unit), which provides access to system data and functions, and can be an external, handheld, reusable battery-powered device. The remote transmitter 108 can be made of any rugged plastic material including polypropylene, cyclicolephin co-polymer, nylon, and other compatible polymers and the like. The remote transmitter 108 is not implanted within the patient so hermetic sealing of the unit is not required. However, in one embodiment, the remote transmitter 108 is at least water resistant, if not waterproof, and can be cleaned using standard hospital disinfectants without damage to the unit.
  • Further, the remote transmitter 108 has a user interface including at least one display 116 and at least one user input 118. In some example embodiments, the display 116 and the user input 118 are combined in the form of a touch screen with a color display. In other embodiments, the display is grayscale. The remote transmitter 108 permits a clinician or a medical technician to navigate through menu driven screens used for data entry, data collection, and controlling the high precision pump unit 106.
  • The remote transmitter 108 is capable of communicating with the high precision pump unit 106. “Capable of communicating” as used herein refers to the remote controller's ability to establish communications with the high precision pump unit 106 yet still have the ability to break communication and the systems described herein still function. To establish communication, in one example embodiment, once the remote transmitter 108 is initialized, the display 116 shows a searching query for a nearby high precision pump unit 106. As the remote transmitter 108 is brought into range of the high precision pump unit 106, a symbol displays the strength of the communication link. Once stable communications have been acquired, the display 116 shows the serial number of the system so a clinician can verify they have the appropriate patient records in hand. If the patient requires a tightening of the gastric band 102, the clinician can enter the amount of the desired volume increase. The remote transmitter 108 can also display the current volume within the gastric band 102 and indicate the new volume as the gastric band 102 fills. The display 116 can also indicate desired and actual volumes during draining of the gastric band 102.
  • To verify the appropriate adjustment has been made to the system, the clinician can set the remote transmitter 108 into a pressure monitor mode and request that the patient drink water. The display 116 shows a real time graph of the pressure measured within the gastric band 102. This diagnostic tool may show higher pressures and warning messages if the gastric band 102 has been over-tightened.
  • The remote transmitter 108 can synchronize and charge when coupled with a charging cradle or docking station. This docking station provides the ability to recharge a rechargeable battery of the remote transmitter 108 and provides a link to download information to a personal computer such as the adjustment history of a patient. Other data that can be stored on the remote transmitter 108 and downloaded from the high precision pump unit 106 includes, but is not limited to serial number, gastric band size, patient information, firmware version and patient adjustment history. This data can be downloaded directly to a patient tracking database for easy tracking.
  • Any data stored on the remote transmitter 108 or within the high precision pump unit 106 can be electronically secured. In other words, security measures can be put in place to keep the data confidential, including communication between the high precision pump unit 106 and the remote transmitter 108. Security measures can include computer generated algorithms that prevent intrusion by outside parties.
  • The high precision pump unit 106 can contain a micro-fluidic pump with active valves. In such an embodiment, the high precision pump unit 106 is a passive device that can only be powered by the remote transmitter 108 when it is in close proximity. For example, in one example embodiment, the remote transmitter 108 may be configured to power and communicate with the high precision pump unit 106 at any distance less than about 8 inches, in one embodiment less than about 4 inches (about 10.2 cm) of tissue plus about 4 inches of air, and in another embodiment about 2 inches (about 5.1 cm) of air. Power and communications can be tailored to transmit over longer distances or can be tailored to have the remote transmitter 108 placed on the skin adjacent to the high precision pump unit 106.
  • Further, the remote transmitter 108 can provide an inductive power and telemetric control through a transmission 124 to the high precision pump unit 106. The remote transmitter 108 may be configured to provide continuous power to the high precision pump unit 106. A dedicated microcontroller within the remote transmitter 108 monitors the amount of power that is transmitted. Further still, a power management system may be implemented to optimize energy transmission between the remote transmitter 108 and the high precision pump unit 106 relative to their separation distance. For example, the power transmission may automatically decrease as the remote transmitter 108 is closer to the high precision pump unit 106, and may be increased as the distance is increased. This minimizes wasted energy, and energy exposure to the patient.
  • The systems and apparatus described herein use common surgical techniques to place the components in their respective positions within a patient. The surgical techniques may be identical or similar to those used in the placement of conventional gastric banding systems. For example, the gastric band 102 may be placed around the stomach using laparoscopic techniques, as known to those of skill in the art. Like a conventional access port, the high precision pump unit 106 may be sutured onto the rectus muscle sheath or any other conveniently accessible muscle. In order to achieve a secure attachment of the high precision pump unit 106, the unit shall be sutured to the rectus muscle and remain securely attached for forces below about 6 lbf, in one embodiment below about 3 lbf (13.3 N). The tubing 110 from the high precision pump unit 106 passes through the rectus muscle into the peritoneal cavity in the same manner as the tubing of a conventional access port.
  • The systems and apparatus of the present invention further allow for a remotely controlled adjustment without needles, non-invasively, by using the remote transmitter 108. Also, should the remote transmitter 108 be unavailable, damaged, out of power, or in the even of an emergency, an adjustment of the gastric band 102 can be performed invasively using a needle. By using the override port 212, a clinician can choose to use the hypodermic needle 112, a standard needle, or a syringe for adjustments. If any of the electronics associated with the systems and apparatus described herein become inoperable, the override port 212 can be used to add or remove fluid from the gastric band 102. The override port 212 and the hypodermic needle 112 can always be used to adjust the gastric band 102.
  • FIG. 2 illustrates an example configuration of the internal components of the high precision pump unit 106 illustrated in FIG. 1 according to an embodiment of the present invention. The housing of the high precision pump unit 106 has an internal volume of between about 0.75 in3 to about 1.6 in3. Exemplary internal features of the high precision pump unit 106 that fit within the housing include a first valve 202, a second valve 204, a pump 206, a pressure/flow sensor 208, an electronics board 210 including an antenna 211, and the override port 212. The internal components of the high precision pump unit 106 can be arranged in any fashion appropriate for delivering and removing precise amounts of fluid from the gastric band 102 and the reservoir 104.
  • The pump 206 can be actively or passively driven. If the pump 206 is actively driven, a local power source such as a battery (not illustrated) is provided to drive the pump 206. If the pump 206 is passively driven, it may be inductively powered by a device external to the high precision pump unit 106. In an exemplary configuration, the pump 206 is passively driven through inductive power from the remote transmitter 108.
  • In one example embodiment, the pump 206 is an inductively powered, electrically driven, positive displacement piezoelectric pump. The pump 206 provides a means to move fluid into the gastric band 102.
  • The pump 206 can move fluid from the reservoir 104 to the gastric band 102 at rates higher than about 0.5 cc/min, for example, higher than about 1 cc/min for band pressures less than about 20 psi (about 138 kPa) relative to the reservoir pressure. Alternatively, fluid can be drained from the gastric band 102 to the reservoir 104 at rates higher than about 0.5 cc/min, for example, higher than about 1 cc/min for band pressures above about 0.2 psi (about 1.38 kPa).
  • The first valve 202 and the second valve 204, illustrated in FIG. 2, can be any valve known in the art to allow precise delivery of fluid and precise flow rates therethrough. In one embodiment, the first valve 202 and the second valve 204 only allow fluid to move in one direction, therefore, the two valves are situated in parallel with the high precision pump unit 106 allowing fluid to drain back from the gastric band 102. Further, the first valve 202 and the second valve 204 should have a precision orifice that restricts the flow rate to a well-characterized, precise amount.
  • The gastric banding system 100 may further comprise at least one flow or pressure sensor 208 disposed, for example, within or adjacent to the high precision pump unit 106. In an exemplary embodiment, two pressure sensors are situated within the fluid pathway between the first valve 202 and the second valve 204 and the gastric band 102. During a no-flow condition, both of the pressure sensors may be used to measure pressure thereby providing the benefits of redundancy and averaging.
  • For example, sensing or measuring the pressure within the fluid pathway of the gastric banding system 100 provides diagnostic uses. A clinician can measure pressure while a patient drinks water, recording and analyzing resulting pressure fluctuations which can help determine if the gastric band 102 is too restrictive. Whether the gastric band 102 is too restrictive can also be confirmed by the patient's response (generally discomfort) upon drinking the water, and can then be appropriately adjusted. Further, sensing or measuring pressure in the gastric banding system 100 can be useful in diagnosing system leaks or obstructions. For example, if the pressure consistently drops over an extended period of time, the clinician can diagnose a leak within the system and plan for an appropriate treatment to fix the problem. In contrast, if there is an obstruction within the system with a sustained pressure rise over time, the clinician can diagnose an obstruction within the system and plan for an appropriate treatment to fix the problem.
  • The override port 212, as illustrated in FIGS. 1 and 2, is an optional feature of some of the embodiments of the present invention. The override port 212 can be manufactured from a metal or a non-radioopaque material and is accessible by insertion of the hypodermic needle 112 (in FIG. 1) through a self-sealing septum 214 (in FIG. 2). The override port 212 allows a clinician to use the hypodermic needle 112 or a standard syringe to fill or drain the gastric band 102. Further, the override port 212 may be located on the distal end 216 of the high precision pump unit 106, for example, at a position substantially opposite from the proximal end 218 where the tubing 220 extends from the high precision pump unit 106. This placement of the override port 212 thereby reduces possible occurrences of a needle damaging the tubing 220. An extension body 222 emanating from the high precision pump unit 106 further protects the tubing 220 from accidental needle sticks.
  • The high precision pump unit 106 can be a passive device which may be entirely controlled and powered by the remote transmitter 108. The antenna 211 on the electronics board 210 is housed within the high precision pump unit 106 and the remote transmitter 108 is coupled to allow the transmission 124 of signals and power through the skin 122 (as illustrated in FIG. 1). The power issued from the remote transmitter 108 is continually monitored by a dedicated microprocessor to ensure that power transmission is minimized to the lowest level required for operation. To minimize the transmission 124 of power and to optimize the transmission 124 of command communication, the high precision pump unit 106 and the remote transmitter 108 have a channel frequency dedicated to command communication and a separate channel frequency dedicated to power transmission. The command communication can be configured, for example, to take place at about 402-406 MHz while the power transmission, for example, takes place at about 400 kHz. This command communication adheres to the frequency and power standards set by the Medical Implant Communications Service. To ensure accuracy, communication and control commands are verified by error check algorithms prior to data reporting or command implementation.
  • A portion of the electronics board 210 within the high precision pump unit 106 is devoted to conditioning and managing the power received at the antenna 211 or from a local battery. Communication electronics manage the bidirectional transmissions with timing verification and error checking. Controller circuits of the electronics board 210 send commands to the first valve 202, the second valve 204, the pump 206, and the pressure/flow sensor 208 and receive data back from the pressure/flow sensor 208. The electronics board 210 can be encased in a biocompatible sealant if further protection, or redundant protection, is necessary.
  • In one example embodiment, the systems and apparatus described herein are configured and structured to be compatible with MRI, or MRI safe, at, for example 1.5 T. In the exemplary embodiment shown, the high precision pump unit 106 is entirely inductively powered. The systems utilize no permanent magnets, no long metallic wires or leads, and a minimal or negligible amount of ferrous or ferromagnetic material. The systems are substantially free or contain substantially no ferromagnetic materials. Substantially no ferromagnetic materials refers to materials containing less than about 5%, in one embodiment, less than about 1% or 0.1% (w/w) of ferromagnetic material. The resulting systems are thus MRI safe given standard specifications regulating translational and rotational attraction, MRI heating, and imaging artifacts. In one embodiment, all materials selected for the systems are selected to be compatible and safe in an MRI environment.
  • Further, the inductive powering of the high precision pump unit 106 requires that energy be passed through body tissue. Since the body tissue absorbs a small amount of the energy passing through it, the heating of the tissue can be proportional to the total energy transferred. To ensure that the systems meet standards to minimize tissue heating (below 2° C. above body temperature per ISO 45652), the systems described herein have been designed to use very little power to move the fluid within the system and do not cause excessive heating of the patient's tissue.
  • The pressure/flow sensor 208 can monitor pressure inside the gastric band 102 as needed. Using the remote transmitter 108 to communicate with the high precision pump unit 106, a clinician can monitor pressure inside the gastric band 102, for example, in “real time” during an adjustment of the constriction within the gastric band 102. This will allow the clinician to observe the response of the gastric band 102 to a patient's adjustment. This may permit a new modality for the gastric band 102 adjustment management to monitor pressure as well as volume during an adjustment. With these new pressure sensing capabilities, the clinician can make a determination of whether there is a leak within the system (e.g., zero pressure reading) or whether there is an obstruction in the system (e.g., prolonged pressure rise).
  • In an example embodiment, the high precision pump unit 106 includes a first fluid line including a first pump for passing fluid in a first direction and a second fluid line in parallel with the first fluid line including a first valve and a second pump for passing fluid in an opposing direction. In another example embodiment, the second pump is not needed because the gastric band 102 provides enough pressure the move the fluid to the reservoir 104. The parallel line configuration allows for filling and draining of the gastric band 102 with a minimal number of components and minimal complexity.
  • The systems and apparatus described herein can achieve at least one of the following features. The total time required to complete a fill or drain of the gastric band 102 does not exceed about 10 minutes, and in one embodiment, about 5 minutes. The systems are able to adjust the volume in the gastric band 102 accurately to within about 0.1 cc or about 10%, whichever is greater. The pressure/flow sensor 208 has a resolution between about 0.010 psi to about 0.025 psi, and in one embodiment, about 0.019 psi (about 130 Pa).
  • In one example embodiment of the present invention, components of the systems can be replaced without replacing the entire system and subjecting patients to overly invasive surgeries to replace entire systems when a single component is defective or damaged. For example, if the high precision pump unit 106 becomes damaged, it can be replaced independently of other components. Alternatively, if the gastric band 102 becomes damaged, it can be replaced independently of other components. The same is true of the tubing 110 and the reservoir 104. Although components can be disconnected for single part replacement, components shall not become dislodged from the tubing 110 for tubing pull-off forces less than about 10 lbf, and in one embodiment, less than about 5 lbf (22.2 N).
  • The systems described herein meet at least one safety specification. For example, in the event of any failure of the systems, either no change in the gastric band 102 tightness or a loosening of the gastric band 102 results. Further, the high precision pump unit 106 is biocompatible for long term implantation and the remote transmitter 108 is biocompatible for transient use both per ISO 10993. The systems are designed to have no significant interaction or interference with other electronics in any of the following modalities: implantable energy sources such as defibrillators and pacemakers; internal energy sources such as electrosurgical instruments; external energy sources such as ultrasound, x-rays and defibrillators; and radiofrequency signals such as pacemaker programmers and neurostimulators.
  • Example 1 Implantation of a Gastric Band System
  • A 40 year old female is diagnosed by her clinician as obese, weighing 510 lbs. The clinician suggests to the patient that she consider the gastric banding system 100 according to the present invention. She agrees and undergoes the implantation procedure. The gastric band 102 is implanted around her cardia thereby creating a stoma. The high precision pump unit 106 is sutured onto the rectus muscle sheath and the tubing 110 and the reservoir 104 passes through the rectus muscle into the peritoneal cavity and connects to the gastric band 102. The gastric banding system 100 comes pre-filled, so there is no need for the clinician to fill the gastric banding system 100 during the surgical procedure. The patient is sutured and sent to recovery.
  • Example 2 Adjustment of a Gastric Band System
  • The female patient of Example 1, after the completion of the surgical implantation, has her gastric band system 100 properly adjusted by her clinician. The clinician holds the remote transmitter 108 to the skin 122 adjacent to the rectus muscle where the high precision pump unit 106 is located and initiates communication between the devices. An initial pressure of zero is displayed for the gastric band 102 as no fluid has been added to the gastric band 102. The clinician begins to fill the gastric band 102 using saline housed within the reservoir 104 at a rate of about 1 cc/min and the entire filling takes less than about 5 minutes.
  • After filling, to about 10 psi, the patient is instructed to drink a glass of water in order to properly assess the proper inflation pressure of the gastric band 102 to ensure it has not been over inflated. Upon confirmation that the gastric band 102 is properly inflated, the procedure is completed and the patient returns to her normal life.
  • The patient instantly notices that she is much less hungry than she previously had been and is consistently consuming less food as her appetite has been decreased. She returns to her clinician's office for a follow-up visit three months after her implantation and initial gastric band filling and she has lost 20 pounds. A year later, she has lost nearly 60 lbs.
  • The gastric banding system 100 generally functions as follows. When a clinician uses the remote transmitter 108 to adjust the gastric band 102, the high precision pump unit 106 initiates a sequence of events to move a precise amount of fluid in the desired direction, where the filling is discussed in FIG. 3A and the draining is discussed in FIG. 3B.
  • FIG. 3A illustrates the filling of the gastric band 102 according to an embodiment of the present invention. Just before pumping is initiated, the second valve 204, in line with the pump 206, is opened. The pump 206 creates a differential pressure to draw fluid out of the reservoir 104 and into the gastric band 102. The first valve 202 and the pressure/flow sensor 208 are closed or not engaged. The reservoir 104 is collapsible and does not impede the outward flow of fluid. Further, the reservoir 104 is sized such that when filled to the maximum recommended fill volume, there is a slight vacuum therein. Once the proper amount of fluid has been transferred from the reservoir 104 to the gastric band 102, the electronics board 210 (or circuitry thereon) shuts off the pump 206 and closes the second valve 204. The gastric band 102 now assumes the new higher pressure and fluid.
  • Referring to FIG. 3B, if the clinician decides to there is a need to loosen the gastric band 102, fluid is released from the gastric band 102 and returned to the reservoir 104. Once the high precision pump unit 106 receives a drain command from the remote transmitter 108, the first valve 202 behind the pressure/flow sensor 208 opens. The fluid is transferred from the gastric band 102 through the pressure/flow sensor 208 and the first valve 202 and into the reservoir 104. The amount of fluid released from the gastric band 102 can be monitored and determined by the pressure/flow sensor 208. Once the correct volume of fluid has been transferred, the first valve 202 is closed. With both the first valve 202 and the second valve 204 closed, the volume in the gastric band 102 is maintained and the pressure in the gastric band 102 can be measured accurately using the pressure/flow sensor 208.
  • When compared to conventional gastric banding systems having standard access ports which exclusively require syringe access (as oppose to being optional), the presently described systems and apparatus offer several benefits. First, the conventional access ports are located under a thick layer of fatty tissue, which is generally the case as the devices are generally used to treat obesity, and the access port can be difficult to locate. The present systems reduce or eliminate the need for (or to locate) the access port, as the use of the remote transmitter 108 removes the need for adjustment using the hypodermic needle 112.
  • Secondly, when accessing the access port in conventional systems, the ambiguity on its location may lead to damage by accidentally puncturing the tubing 110 which connects the access port 212 to the gastric band 102. This can require a revision surgery in order to repair the punctured tubing 110. Further, when a conventional access port cannot be located by palpation, x-ray imaging may be required to guide a needle into the access port. Such imaging practices put a patient at risk for x-ray radiation exposure. The present systems and apparatus remove the need for these unnecessary procedures and save the patient from x-ray radiation exposure. The present systems and apparatus are compatible with magnetic resonance imaging (MRI), which is much safer for a patient.
  • In the unlikely event that the override port 212 of the present invention needs to be used, the override port 212 may be located away from the tubing connection to the gastric band 102 to reduce the potential for tubing needle sticks. The high precision pump unit 106 has geometry and a rigid case that can be structured to facilitate the user in locating the override port 212 when needed.
  • FIGS. 4A and 4B illustrate cross-sectional views of an exemplary valve 400 in a closed position (FIG. 4A) and an open position (FIG. 4B) according to an embodiment of the present invention. The valve 400 may be used in place of one or both of the first valve 202 and the second valve 204.
  • Referring to FIG. 4A, the valve 400 is biased in a closed position, for example, by a spring preload force 402 acting on a seal 404, for example, a flexible silicone seal 404. For example, the spring preload force 402 pushes the flexible silicone seal 404 into sealing engagement with a valve seat 406. When the valve 400 is sealed as shown in FIG. 4A, fluid cannot pass from a valve inlet 408 to a valve outlet 410.
  • Now referring to FIG. 4B, when fluid flow is desired, a signal is sent to a valve actuator (not shown), which removes the spring preload force 402 and permits the flexible silicone seal 404 to relax or move upward into an open position, out of sealing engagement with the valve seat 406. The fluid is then free to flow from the valve inlet 408 to the valve outlet 410 until the valve 400 is closed, for example, by reapplication of the spring preload force 402.
  • FIGS. 5A and 5B illustrate cross-sectional views of an exemplary dome valve 500 in a closed position (FIG. 5A) and an open position (FIG. 5B) according to an embodiment of the invention. In one embodiment, the dome valve 500 is an implantable device that controls the movement of fluid to the inflatable portion 114 of the gastric band 102. The dome valve 500 may be used in place of one or both of first valve 202 and the second valve 204.
  • The dome valve 500 is designed to be implanted into a patient, and thus may be referred to as a micro valve. In an embodiment, the dome valve 500 has a length of about 15 mm (e.g., 10-25 mm range) and an about 10 mm outer, diameter (e.g., 7-15 mm range). In one embodiment, the dome valve 500 is a radially symmetric shape (e.g., disk, tube, rod, etc.). However, the dome valve 500 can be any shape (e.g., circular, square, rectangular, etc). The dome valve 500 can include a body 560, an actuator 505, a cap 510, and a diaphragm 520.
  • The body 560 has an inlet component 530, an outlet component 535, and a bottom component 550. The inlet component 530, the outlet component 535, and the bottom component 550 have been identified for illustrative purposes and may not be separate components from the body 560. An inlet 540, which is a fluid entrance into the body 560, is defined between the inlet component 530 and the bottom component 550. An outlet 545, which is a fluid exit from the body 560, is defined between the outlet component 535 and the bottom component 550.
  • The inlet component 530 and the bottom component 550 form a valve seat 570. The valve seat 570 can be the surfaces (e.g., the tips) of the inlet component 530 and the bottom component 550 which provide sealing when the diaphragm 520 is placed against and in contact with the inlet component 530 and the bottom component 550. In one embodiment, the vertical column of the inlet component 530 and the bottom component 550 define the valve seat 570. The vertical columns may be short segments (e.g., 1.5 mm) of plastic or metal tubing (e.g., stainless steel).
  • The actuator 505 is configured to apply a force (e.g., stress) on the cap 510 causing the diagraph 520 to move from the closed position (FIG. 5A) to the open position (FIG. 5B) when the actuator 505 receives a telemetric signal 124 (e.g., electrical energy) from the remote transmitter 108. The force includes a smaller downward force 555 to keep the valve 500 in a closed position (FIG. 5A) and a larger downward force 565 to keep the valve 500 in an open position (FIG. 5B). In an embodiment, the smaller force 555 is less than 10 newtons. In an embodiment, the larger force 565 is between 10-100 newtons. In another embodiment, the larger force 565 is between 15-45 newtons.
  • FIG. 5A illustrates the actuator 505 applying the smaller force 555 (e.g., 0 newtons, little or no downward force, a reduced in force, a de-energized state), which is low enough to keep the valve 500 in the closed position. In particular, when the actuator 505 applies the smaller force 555, the cap 510 receives little or no downward force on cap edges 515. Since the cap edges 515 are adjacent to the diaphragm edges 525, the diaphragm edges 525 also receive little or no downward force. As such, the diaphragm center 527 of the diaphragm 520 remains sitting on (or relaxed onto) the valve seat 570, blocking fluid from flowing from the inlet 540 to the outlet 545.
  • FIG. 5B illustrates the actuator 505 applying a large force 565 (e.g., an energized state) that compresses (e.g., squeezes) the diaphragm edges 525 between the cap 510 and the body 560. The large force 565 is great enough that the material on the diaphragm edges 525 is compressed, with the cap 510 blocking diaphragm edges 525 from expanding outward, the diaphragm is expanded inward such that the diaphragm center 527 is moved up off the valve seat 570 due to a build up of material. This opens a passage from the inlet 540 to the outlet 545 and permitting fluid flow in the valve 500 as shown by fluid flow indicators 575. When a downward force is applied, the diaphragm center 527 moves in a substantially opposite direction to the downward force.
  • The actuator 505 can take many forms (e.g., solenoids, stepper motors, piezoelectric actuator, electroactive polymer, etc.) as dictated by the specific application. In one embodiment of the RAB, the actuator 505 is a piezoelectric actuator. In another embodiment, the actuator 505 is an electroactive polymer.
  • The cap 510 may be positioned between the diaphragm 520 and the actuator 505. The cap 510 has one or more cap edges 515 (e.g., cap ends). The cap edges 515 direct the small force 555 and the large force 565 from the actuator 505 to the diaphragm 520. In one embodiment, the cap 510 is part of the actuator 505.
  • The diaphragm 520, which may be referred to as a valve seal, is positioned between the cap 510 and the body 560. The diaphragm 520 has a diaphragm center 527 (e.g., a body) and one or more diaphragm edges 525 (e.g., ends of the diaphragm 520) coupled to the body 560.
  • The diaphragm 520 (e.g., valve seal) has an open position (FIG. 5B) and a closed position (FIG. 5A). When the diaphragm 520 is in the open position, the diaphragm 520 does not block the valve seat 570 and therefore allows the fluid to move from the inlet 540 to the outlet 545. Conversely, when the diaphragm 520 is in a closed position, the diaphragm 520 blocks the valve seat 570 and does not allow the fluid to move from the inlet 540 to the outlet 545.
  • In one embodiment, the diaphragm 520 is made of an elastomeric material. The elastomeric material includes silicon and any other material that is stretchy like a rubber band. For example, the elastomeric material includes flexible materials, naturally occurring elastic substances (e.g., natural rubber), and synthetically produced substances (e.g., silicon, butyl rubber, neoprene).
  • The elastomeric material can be stretched across the valve seat 570 to provide a seal and can buckle to create a gap 526 above the valve seat 570. In an embodiment, the gap 526 below the diaphragm 520 is substantially less than 1 mm off the valve seat 570. In one embodiment, the gap 526 is about 0.03 mm. In one embodiment, the range for the gap 526 is between about 0.01 mm to about 0.25 mm. In another embodiment, the range for the gap 526 is between about 0.01 mm to about 0.10 mm.
  • In one embodiment, the diaphragm 520 is circular, although any shape is possible (e.g., a thin strip, rectangular, etc).
  • The dome valve 500 has numerous advantages over conventional valves. The dome valve 500 contains no ferromagnetic material as is commonly used in conventional valves (e.g., solenoid valves). As a result, the dome valve 500 advantageously can be safely used in conjunction with magnetic resonance imaging (MRI) scanning.
  • Additionally, the dome valve 500 advantageously is not concentric with the diaphragm, unlike conventional valves which have a concentric shaped seal which results in high susceptibility to leakage and contamination to the moving parts of the valve.
  • Advantageously, both the diaphragm 520 and the cap 510 restrict fluid from contacting the moving valve components, such as the actuator 505. This allows the dome valve 500 to be used in a system where the fluid is highly corrosive to the moving parts and can be used where the moving parts rub and create contaminants that must be keep free from the fluid, because the dome valve 500 protects the moving valve components from contamination.
  • Dome valve 500 advantageously can be inexpensively manufactured, due partly to the mechanical linkage, while still being robust and efficient. Opening the valve 500 requires very little stroke or travel from the actuator 505 to produce a suitably large upward deflection in the diaphragm 520. In contrast, conventional valves use energy inefficient methods such as forming a seal for a valve by heating a membrane comprised of two materials with different coefficients of linear thermal expansion.
  • Also, the dome valve 500 achieves a low leak/leakage rate when in the closed position (e.g., closed/sealed tightly) compared to conventional valves and achieves a high flow rate when in the open position. Further, the dome valve 500 minimizes the space required for the implanted device because the dome valve 500 can be smaller than other implantable devices.
  • FIGS. 6A and 6B illustrate cross-sectional views of an exemplary screw valve 600 in a closed position (FIG. 6A) and an open position (FIG. 6B) according to an embodiment of the present invention. The screw valve 600 is part of the RAB and may be used in place of one or both of the first valve 202 and the second valve 204. The screw valve 600 is designed small enough to be implanted into a patient, and thus may be referred to as a micro valve. In an embodiment, the screw valve 600 has a length of approximately 30-50 mm and an about 10 mm outer diameter (e.g., 7-15 mm range). In comparison to the dome valve 500 embodiment discussed above (10-25 mm length, 10 mm outer diameter), the screw valve 600 is almost twice as long, but has the same outer diameter.
  • The screw valve 600 in accordance with one embodiment of the present invention generally includes a body 660, a screw 615, a screw actuator 605, a coupling mechanism 610, a valve seal 620, and a valve seat 670.
  • The body 660 houses the components of the screw valve 600. The body 660 also has an inlet 640 and an outlet 645. The inlet 640 may be in communication with the reservoir 104 and the outlet 645 may be in communication with the inflatable portion 114 of the gastric band 102, or vice-versa, using suitable fluid port connectors, not shown.
  • The screw 615 includes a lead screw (where lead means a type of screw, and does not mean the material lead as used in a graphite pencil), power screw, translation screw. The screw 615 can be designed to translate radial (e.g., circular) motion/movement into linear (e.g., translational) motion/movement. The screw 615 is configured to apply a force on the valve seal 620 to cause the valve seal 620 to move from an open position (FIG. 6B) to a closed position (FIG. 6A) when the screw actuator 605 receives a telemetric signal 124 from the remote transmitter 108.
  • The screw actuator 605, positioned within the body 660 of the screw valve 600, has an actuator body defining a threaded screw hole 606. The screw 615 is positioned within the threaded screw hole 606.
  • In one embodiment, the screw actuator 605 is a motor. In another embodiment, the motor may be positioned within the screw actuator 605. In another embodiment, the motor is external to the body 660 for moving the screw 615.
  • The motor (not shown) may also be included in the screw valve 600 and coupled to the screw 615 for moving the screw 615 within the threaded screw hole 606. The motor can be a DC motor, an AC motor, a solenoid, a stepper motor, a piezoelectric actuator, a piezoelectric driver, and an electroactive polymer. In one embodiment, the motor is selected to be the same type of motor used elsewhere in the implantable system. The motor can be configured to move the screw 615 to at least two positions so that the valve seal 620 can be moved to at least two positions depending on the telemetric signal 124 sent from the remote transmitter 108 to the actuator 605.
  • The coupling mechanism 610, positioned between the valve seal 620 and the screw 615, decouples a rotational motion of the screw 615. In one embodiment, the coupling mechanism 610 may be securely fastened or fixed to the valve seal 620 so that the coupling mechanism 610 does not rotate with the rotation of the screw 615. The screw 615 moves forward and backward (or upward and downward) through both rotational and translational motion. However, to prevent damage to the valve seal 620, the valve seal 620 should only receive translational motion (not rotational motion). The coupling mechanism 610 decouples the rotational motion of the screw 615 but transmits the translational motion. The coupling mechanism 610 is illustrated as being a tappet, but can also include a ball bearing, a bellows unit, etc., as illustrated in FIGS. 7A-7C.
  • The valve seal 620 has one or more edges 621 coupled to the body 660. The valve seal 620 is capable of being moved from an open position that is spaced apart from the valve seat 670 and does not block a fluid (e.g., saline) from flowing from the inlet 640 to the outlet 645 to a closed position that blocks or contacts the valve seat 670 and does not allow the fluid to move from the inlet 640 to the outlet 645. The valve seal 620 can be in the closed position, the open position, and a partially-open position, which is between the closed position and the open position.
  • The valve seal 620, like the diaphragm 520, is made of an elastomeric material. In one embodiment, the elastomeric material is silicon. However, any material that is stretchy like a rubber band can be used. For example, the elastomeric materials include flexible materials, naturally occurring elastic substances (e.g., natural rubber), and synthetically produced substances (e.g., silicon, butyl rubber, neoprene).
  • The valve seat 670 provides an opening for the valve seal 620 to close or open. To close the screw valve 600, a command signal (e.g., a telemetric signal) is sent to the screw actuator 605 which drives the screw 615 (and the coupling device or mechanism 610) into the valve seal 620 to press the valve seal 620 onto the valve seat 670. To open the screw valve 600, a command signal is sent to the screw actuator 605 which drives the screw 615 (and the coupling device or mechanism 610) away from the valve seal 620 to decompress or move the valve seal 620 away from the valve seat 670.
  • The pressure/flow sensor 208 may also be included in or coupled to the screw valve 600. For example, one or both of the flow sensor and/or the pressure sensor can be coupled to the valve seat 670 for determining and adjusting an amount of the fluid flowing between the inlet 640 and the outlet 645.
  • FIG. 6A illustrates the screw 615 displacing the valve seal 620 onto the valve seat 670 to block the fluid from flowing from the inlet 640 to the outlet 645.
  • FIG. 6B illustrates the screw 615 moved upward such that the valve seal 620 is not touching the valve seat 670 to allow the fluid to flow from the inlet 640 to the outlet 645 as shown by fluid flow indicators 675. The fluid can also flow in the opposite direction as shown by the fluid flow indicators 675.
  • The lead screw valve 600 provides many advantages when used for the gastric banding system 100. For example, the screw valve 600 achieves a low leak/leakage rate when closed (e.g., closed/sealed tightly) compared to conventional valves and a high flow rate during adjustment. The screw valve 600 is also easier to manufacture than other implantable devices (such as the dome valve 500).
  • An additional advantage, is that the screw valve 600 can remain in position (e.g., fully open, partially open, tightly closed) in the presence of very high constant and intermittent pressures present from the inlet 640 and the outlet 645. For example, the screw valve 600 can handle high pressures, such as 30 psi. The screw valve 600 can resist high pressures by being overdriven and by being a normally-still valve.
  • If the screw 615 is intentionally overdriven, the screw 615 presses tightly against the coupling mechanism 610, which presses tightly against the valve seal 620, which presses tightly against the valve seat 670. The term overdriven means that the screw 615 is driven just beyond the point where the valve seal 620 contacts the valve seat 670. The phrase “just beyond” means a point where force is generated. Even though it's not possible (without damage) to move the valve seal 620 beyond the point that it touches the valve seat 670, it is possible to generate force. For example, forces develop in the motor and forces develop loading up the motor. These forces creating a force balance between the valve seal 620 and the valve seat 670. In one embodiment, “just beyond” is a point where an additional force is required from the motor.
  • Even though the screw 615 drives the valve seal 620 hard into the valve seat 670, in one embodiment, the valve seal 620 is made of a soft material (e.g., silicon) and the valve seat 670 is made of a hard material (e.g., polished stainless steel) such that the two materials can be pressed together without resulting in substantial damage or marring. This tight seal blocks fluid, including fluid under high pressure. The screw 615 can optionally be reversed to relieve any unwanted excess pressure on the screw 615, the coupling mechanism 610, the valve seal 620, and the valve seat 670.
  • Another advantage of the screw valve 600 is that the screw 615 can resist the opening and closing in the presence of steady or high pressure, without requiring an additional energy, because the screw valve 600 is a normally still valve (as oppose to normally open or normally closed). Thus, in the absence of a drive command, the screw actuated valve will remain in whichever state it was left, whether that was fully open, partially open, or fully closed.
  • An additional advantage of the screw valve 600 is the amount of positions available to regulate fluid flow. The screw valve 600 can be fully open, fully closed, or anywhere in between, providing significant flexibility in designing actuation drive characteristics. The fluid flow rate can be adjusted by partially opening the screw valve 600. The screw seal 620 can occupy any position by making precise and incremental adjustments to the screw 615. In one embodiment, the screw valve 600 is used in a closed loop system, where a sensor (e.g., flow sensor, a pressure sensor, etc.) is used to adjust the position of the screw 615 to regulate the fluid flow from the inlet 640 to the outlet 645.
  • FIGS. 7A, 7B and 7C illustrate side views of examples of the coupling mechanism 610 illustrated in FIG. 6 according to various embodiments of the present invention. FIG. 7A illustrates a tappet 705 as the coupling mechanism 610. The tappet 705 can be a sliding rod for moving a valve. The tappet 705 touches the screw 615, and connects or rides on the screw 615. The tappet 705 allows an intentional rotational slippage between the tappet 705 and the screw 615 to decouple the rotational motion.
  • FIG. 7B illustrates a ball 710 along with the tappet 705 as the coupling mechanism 610. The ball 710 is located between the screw 615 and the tappet 705. The ball 710 provides two surfaces designed to allow an intentional rotational slippage between the screw 615 and the valve seal 620. Having two surfaces for slippage is advantageous because one surface may bind up due to particulate contamination (e.g., particles from the screw 615 or the tappet 705) or manufacturing imperfection (e.g., molding flash, burrs, etc.). The ball 710 can be a ball bearing.
  • FIG. 7C illustrates a bellows unit 715 as the coupling mechanism 610 used with the screw 615. The bellows unit 715 can isolate the screw 615 from the valve seal 620. Without the bellows unit 715, the screw 615 would rotate and rub against a surface of the valve seal 620 generating particulates which are further rubbed against the valve seal 620. Since the valve seal 620 can be sensitive and not designed to be rubbed with particulates, the bellows unit 715 advantageously keeps all the possible generated particulates enclosed and sealed away from the valve seal 620.
  • FIG. 8 is a flow chart of a method of using the dome valve 500 to control the movement of fluid between the reservoir 104 and the inflatable portion 114 of the gastric band 102.
  • The process starts at step 800. At step 805, the dome valve 500 receives a telemetric signal from the remote transmitter 108. Alternatively, the dome valve 500 can receive a signal from an implanted microcontroller. The implanted microcontroller may be part of, coupled to or located within the actuator 505. The implanted microcontroller can receive a telemetric signal from the remote transmitter 108. Next, the actuator 505 applies a downward force on the diaphragm 520 to open the dome valve 500 at step 810. The downward force is applied onto the diaphragm edges 525 of the diaphragm 520 in the dome valve 500, lifting up the diaphragm center 527, and allowing fluid to flow through the dome valve 500.
  • At step 815, the actuator 505 reduces the downward force on the diaphragm 520 to close the dome valve 500. The downward force is reduced on the diaphragm edges 525 of the diaphragm 520 in the dome valve 500, lowering the diaphragm center 527, and blocking fluid from flowing through the dome valve 500. The process ends at step 820.
  • FIG. 9 is a flow chart of a method of using the screw valve 600 to control the movement of fluid between the reservoir 104 and the inflatable portion 114 of the gastric band 102.
  • The process starts at step 900. At step 905, the screw valve 600 receives a telemetric signal from the remote transmitter 108. Alternatively, the dome valve 600 can receive a signal from an implanted microcontroller. The implanted microcontroller may be part of, coupled to or located within the screw actuator 605. The implanted microcontroller can receive a telemetric signal from the remote transmitter 108. At step 910, the screw actuator 605 turns the screw 615 in one direction to increase a force on the valve seal 620 to close the screw valve 600.
  • Then, the screw actuator 605 turns the screw 615 in the opposite direction to decrease the force on the valve seal 620 to open the screw valve 600. The process ends at step 920.
  • Unless otherwise indicated, all numbers expressing quantities of ingredients, properties such as molecular weight, reaction conditions, and so forth used in the specification and claims are to be understood as being modified in all instances by the term “about.” Accordingly, unless indicated to the contrary, the numerical parameters set forth in the specification and attached claims are approximations that may vary depending upon the desired properties sought to be obtained by the present invention. At the very least, and not as an attempt to limit the application of the doctrine of equivalents to the scope of the claims, each numerical parameter should at least be construed in light of the number of reported significant digits and by applying ordinary rounding techniques.
  • Notwithstanding that the numerical ranges and parameters setting forth the broad scope of the invention are approximations, the numerical values set forth in the specific examples are reported as precisely as possible. Any numerical value, however, inherently contains certain errors necessarily resulting from the standard deviation found in their respective testing measurements.
  • The terms “a,” “an,” “the” and similar referents used in the context of describing the invention (especially in the context of the following claims) are to be construed to cover both the singular and the plural, unless otherwise indicated herein or clearly contradicted by context. Recitation of ranges of values herein is merely intended to serve as a shorthand method of referring individually to each separate value falling within the range. Unless otherwise indicated herein, each individual value is incorporated into the specification as if it were individually recited herein. All methods described herein can be performed in any suitable order unless otherwise indicated herein or otherwise clearly contradicted by context. The use of any and all examples, or exemplary language (e.g., “such as”) provided herein is intended merely to better illuminate the invention and does not pose a limitation on the scope of the invention otherwise claimed. No language in the specification should be construed as indicating any non-claimed element essential to the practice of the present invention.
  • Groupings of alternative elements or embodiments of the invention disclosed herein are not to be construed as limitations. Each group member may be referred to and claimed individually or in any combination with other members of the group or other elements found herein. It is anticipated that one or more members of a group may be included in, or deleted from, a group for reasons of convenience and/or patentability. When any such inclusion or deletion occurs, the specification is deemed to contain the group as modified thus fulfilling the written description of all Markush groups used in the appended claims.
  • Certain embodiments of the present invention are described herein, including the best mode known to the inventors for carrying out the present invention. Of course, variations on these described embodiments will become apparent to those of ordinary skill in the art upon reading the foregoing description. The inventor expects skilled artisans to employ such variations as appropriate, and the inventors intend for the present invention to be practiced otherwise than specifically described herein. Accordingly, the present invention includes all modifications and equivalents of the subject matter recited in the claims appended hereto as permitted by applicable law. Moreover, any combination of the above-described elements in all possible variations thereof is encompassed by the present invention unless otherwise indicated herein or otherwise clearly contradicted by context.
  • Furthermore, references may have been made to patents and printed publications in this specification. Each of the above-cited references and printed publications are individually incorporated herein by reference in their entirety.
  • Specific embodiments disclosed herein may be further limited in the claims using consisting of or and consisting essentially of language. When used in the claims, whether as filed or added per amendment, the transition term “consisting of” excludes any element, step, or ingredient not specified in the claims. The transition term “consisting essentially of” limits the scope of a claim to the specified materials or steps and those that do not materially affect the basic and novel characteristic(s). Embodiments of the present invention so claimed are inherently or expressly described and enabled herein.
  • In closing, it is to be understood that the embodiments of the present invention disclosed herein are illustrative of the principles of the present invention. Other modifications that may be employed are within the scope of the present invention. Thus, by way of example, but not of limitation, alternative configurations of the present invention may be utilized in accordance with the teachings herein. Accordingly, the present invention is not limited to that precisely as shown and described.

Claims (20)

  1. 1. An implantable device for controlling movement of a fluid to an inflatable portion of a gastric band, the implantable device comprising:
    a body having an inlet, an outlet and a valve seat positioned between the inlet and the outlet, the body defining a fluid passage from the inlet to the outlet;
    a diaphragm having one or more edges coupled to the body, the diaphragm being made of an elastomeric material and capable of being moved from a closed position that blocks the valve seat and does not allow the fluid to move from the inlet to the outlet to an open position that does not block the valve seat and allows the fluid to move from the inlet to the outlet;
    an actuator configured to apply a force on the diaphragm causing the diaphragm to move from the closed position to the open position; and
    a microcontroller coupled to the actuator, the microcontroller configured to receive a telemetric signal from a remote transmitter and control the actuator based on the telemetric signal.
  2. 2. The implantable device of claim 1 further comprising a cap, coupled between the diaphragm and the actuator, for directing the force from the actuator to the diaphragm.
  3. 3. The implantable device of claim 1 wherein the force is applied on the one or more edges of the diaphragm.
  4. 4. The implantable device of claim 1 wherein the diaphragm moves in a direction substantially opposite to a direction of the force.
  5. 5. The implantable device of claim 1 wherein the diaphragm prevents the fluid from coming into direct contact with the actuator.
  6. 6. The implantable device of claim 1 wherein the diaphragm is made of a flexible material.
  7. 7. The implantable device of claim 1 wherein the diaphragm is in the open position when the actuator is in an energized state.
  8. 8. The implantable device of claim 1 wherein the diaphragm is in the closed position when the actuator is in an unenergized state.
  9. 9. The implantable device of claim 1 wherein the actuator is selected from a group consisting of a solenoid, a stepper motor, a piezoelectric actuator, an electroactive polymer, and combinations thereof.
  10. 10. The implantable device of claim 1 wherein the remote transmitter transmits the telemetric signal to the microcontroller.
  11. 11. An implantable device that controls the movement of fluid to an inflatable portion of a gastric band, the implantable device comprising:
    a body having an inlet, an outlet and a valve seat, the body defining a fluid passage from the inlet to the outlet;
    a valve seal having one or more edges coupled to the body, the valve seal being made of an elastomeric material and capable of being moved from an open position that does not block the valve seat and allows the fluid to move from the inlet to the outlet to a closed position that blocks the valve seat and does not allow the fluid to move from the inlet to the outlet; and
    an actuator having an actuator body defining a threaded screw hole and positioned within the body and a screw positioned within the threaded screw hole, the screw configured to apply a force on the valve seal causing the valve seal to move from the open position to the closed position when the actuator receives a telemetric signal from a remote transmitter.
  12. 12. The implantable device of claim 11 further comprising a motor, positioned within the actuator body, for moving the screw within the threaded screw hole.
  13. 13. The implantable device of claim 12 wherein the motor is selected from a group consisting of a DC motor, an AC motor, a solenoid, a stepper motor, a piezoelectric actuator, a piezoelectric driver, an electroactive polymer, and combinations thereof.
  14. 14. The implantable device of claim 13 wherein the motor is configured to move the screw to a first screw position so that the valve seal can be moved to a first valve seal position depending on the telemetric signal received from the remote transmitter.
  15. 15. The implantable device of claim 14 wherein the first valve seal position is selected from a group consisting of the closed position, the open position, and a partially-open position which is between the closed position and the open position.
  16. 16. The implantable device of claim 11 further comprising a coupling mechanism, positioned between the valve seal and the screw, for decoupling a rotational motion of the screw but allowing for a translational motion of the screw.
  17. 17. The implantable device of claim 16 wherein the coupling mechanism is selected from a group consisting of a tappet, a ball bearing, a bellows unit, and combinations thereof.
  18. 18. The implantable device of claim 11 further comprising a flow sensor, coupled to the valve seat, for determining and adjusting an amount of the fluid flowing between the inlet and the outlet.
  19. 19. The implantable device of claim 11 further comprising a pressure sensor, coupled to the valve seat, for determining and adjusting a pressure of the fluid flowing between the inlet and the outlet.
  20. 20. The implantable device of claim 11 wherein the remote transmitter transmits the telemetric signal to the actuator.
US12712952 2008-10-22 2010-02-25 Dome and screw valves for remotely adjustable gastric banding systems Abandoned US20100185049A1 (en)

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US10757608 true 2008-10-22 2008-10-22
US12603058 US8366602B2 (en) 2008-10-22 2009-10-21 Electrically activated valve for implantable fluid handling system
US12712952 US20100185049A1 (en) 2008-10-22 2010-02-25 Dome and screw valves for remotely adjustable gastric banding systems

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US12712952 US20100185049A1 (en) 2008-10-22 2010-02-25 Dome and screw valves for remotely adjustable gastric banding systems
EP20110706980 EP2538897B1 (en) 2010-02-25 2011-02-16 Dome and screw valves for remotely adjustable gastric banding systems
PCT/US2011/024954 WO2011106208A1 (en) 2010-02-25 2011-02-16 Dome and screw valves for remotely adjustable gastric banding systems
US13894955 US8900118B2 (en) 2008-10-22 2013-05-15 Dome and screw valves for remotely adjustable gastric banding systems
US14556754 US20150126807A1 (en) 2008-10-22 2014-12-01 Dome and Screw Valves for Remotely Adjustable Gastric Banding Systems

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US13894955 Active US8900118B2 (en) 2008-10-22 2013-05-15 Dome and screw valves for remotely adjustable gastric banding systems
US14556754 Abandoned US20150126807A1 (en) 2008-10-22 2014-12-01 Dome and Screw Valves for Remotely Adjustable Gastric Banding Systems

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Cited By (37)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20110306827A1 (en) * 2010-02-05 2011-12-15 Allergan, Inc. Needle guard to protect access port tubing
US8187164B2 (en) * 2002-04-26 2012-05-29 Torax Medical, Inc. Methods and apparatus for treating body tissue sphincters and the like
WO2012071395A1 (en) * 2010-11-22 2012-05-31 Aria Cv, Inc. System and method for reducing pulsatile pressure
US20120157759A1 (en) * 2010-12-16 2012-06-21 Ams Research Corporation Artificial Sphincter System and Method
US8236023B2 (en) 2004-03-18 2012-08-07 Allergan, Inc. Apparatus and method for volume adjustment of intragastric balloons
WO2012110623A1 (en) * 2011-02-17 2012-08-23 Allergan Medical Sàrl Hydraulic gastric band with reversible self-opening mechanism
US8251888B2 (en) 2005-04-13 2012-08-28 Mitchell Steven Roslin Artificial gastric valve
US8292800B2 (en) 2008-06-11 2012-10-23 Allergan, Inc. Implantable pump system
US8308630B2 (en) 2006-01-04 2012-11-13 Allergan, Inc. Hydraulic gastric band with collapsible reservoir
US8317677B2 (en) 2008-10-06 2012-11-27 Allergan, Inc. Mechanical gastric band with cushions
US8377081B2 (en) 2004-03-08 2013-02-19 Allergan, Inc. Closure system for tubular organs
US8382780B2 (en) 2002-08-28 2013-02-26 Allergan, Inc. Fatigue-resistant gastric banding device
US8517915B2 (en) 2010-06-10 2013-08-27 Allergan, Inc. Remotely adjustable gastric banding system
US8678993B2 (en) 2010-02-12 2014-03-25 Apollo Endosurgery, Inc. Remotely adjustable gastric banding system
US8698373B2 (en) 2010-08-18 2014-04-15 Apollo Endosurgery, Inc. Pare piezo power with energy recovery
US8725435B2 (en) 2011-04-13 2014-05-13 Apollo Endosurgery, Inc. Syringe-based leak detection system
US8758221B2 (en) 2010-02-24 2014-06-24 Apollo Endosurgery, Inc. Source reservoir with potential energy for remotely adjustable gastric banding system
US8764624B2 (en) 2010-02-25 2014-07-01 Apollo Endosurgery, Inc. Inductively powered remotely adjustable gastric banding system
US8840541B2 (en) 2010-02-25 2014-09-23 Apollo Endosurgery, Inc. Pressure sensing gastric banding system
US8845513B2 (en) 2002-08-13 2014-09-30 Apollo Endosurgery, Inc. Remotely adjustable gastric banding device
US8876694B2 (en) 2011-12-07 2014-11-04 Apollo Endosurgery, Inc. Tube connector with a guiding tip
US8876850B1 (en) 2014-06-19 2014-11-04 Aria Cv, Inc. Systems and methods for treating pulmonary hypertension
US8900117B2 (en) 2004-01-23 2014-12-02 Apollo Endosurgery, Inc. Releasably-securable one-piece adjustable gastric band
US8905915B2 (en) 2006-01-04 2014-12-09 Apollo Endosurgery, Inc. Self-regulating gastric band with pressure data processing
US8939888B2 (en) 2010-04-28 2015-01-27 Apollo Endosurgery, Inc. Method and system for determining the pressure of a fluid in a syringe, an access port, a catheter, and a gastric band
US8961393B2 (en) 2010-11-15 2015-02-24 Apollo Endosurgery, Inc. Gastric band devices and drive systems
US8961394B2 (en) 2011-12-20 2015-02-24 Apollo Endosurgery, Inc. Self-sealing fluid joint for use with a gastric band
US9028394B2 (en) 2010-04-29 2015-05-12 Apollo Endosurgery, Inc. Self-adjusting mechanical gastric band
US9044298B2 (en) 2010-04-29 2015-06-02 Apollo Endosurgery, Inc. Self-adjusting gastric band
US9050165B2 (en) 2010-09-07 2015-06-09 Apollo Endosurgery, Inc. Remotely adjustable gastric banding system
US20150240958A1 (en) * 2012-10-22 2015-08-27 President And Fellows Of Harvard College Apparatus, systems, and methods for actuating pressurizable chambers
US9192501B2 (en) 2010-04-30 2015-11-24 Apollo Endosurgery, Inc. Remotely powered remotely adjustable gastric band system
US9211207B2 (en) 2010-08-18 2015-12-15 Apollo Endosurgery, Inc. Power regulated implant
US9226840B2 (en) 2010-06-03 2016-01-05 Apollo Endosurgery, Inc. Magnetically coupled implantable pump system and method
US9295573B2 (en) 2010-04-29 2016-03-29 Apollo Endosurgery, Inc. Self-adjusting gastric band having various compliant components and/or a satiety booster
WO2016200612A1 (en) * 2015-06-11 2016-12-15 Obalon Therapeutics, Inc. Intragastric device system
US9987153B2 (en) 2010-06-08 2018-06-05 The Regents Of The University Of Minnesota Vascular elastance

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2929842B1 (en) * 2008-04-14 2011-09-30 Cie Euro Etude Rech Paroscopie Gastric band with overhead pockets
US20100185049A1 (en) 2008-10-22 2010-07-22 Allergan, Inc. Dome and screw valves for remotely adjustable gastric banding systems
US9526648B2 (en) 2010-06-13 2016-12-27 Synerz Medical, Inc. Intragastric device for treating obesity

Citations (98)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1174814A (en) * 1915-09-17 1916-03-07 Manville E J Machine Co Automatic threader.
US2339138A (en) * 1942-09-18 1944-01-11 Central Equipment Co Clamp
US2438231A (en) * 1946-01-18 1948-03-23 Schultz Closure for fountain pens and the like
US4133315A (en) * 1976-12-27 1979-01-09 Berman Edward J Method and apparatus for reducing obesity
US4370982A (en) * 1980-09-10 1983-02-01 Medrad, Inc. Method and apparatus for injecting and for controlling the pressure of fluid being injected into a catheter
US4424208A (en) * 1982-01-11 1984-01-03 Collagen Corporation Collagen implant material and method for augmenting soft tissue
US4492004A (en) * 1982-12-03 1985-01-08 Hans Oetiker Earless clamp structure
US4803075A (en) * 1986-06-25 1989-02-07 Collagen Corporation Injectable implant composition having improved intrudability
US4896787A (en) * 1987-08-14 1990-01-30 Genus International Article with resilient hinges becoming rigid under tension
US4989756A (en) * 1986-10-14 1991-02-05 Kabushiki Kaisha Shinkawa Dispensing apparatus
US5084061A (en) * 1987-09-25 1992-01-28 Gau Fred C Intragastric balloon with improved valve locating means
US5089019A (en) * 1989-12-06 1992-02-18 Medtronic, Inc. Muscle work output monitor by intramuscular temperature variation measurement
US5091171A (en) * 1986-12-23 1992-02-25 Yu Ruey J Amphoteric compositions and polymeric forms of alpha hydroxyacids, and their therapeutic use
US5188609A (en) * 1991-07-08 1993-02-23 Bryman Medical Inc. Swivel clip medical tube holder
US5277333A (en) * 1990-07-10 1994-01-11 Musashi Engineering, Inc. Apparatus for metering and discharging a liquid
US5383858A (en) * 1992-08-17 1995-01-24 Medrad, Inc. Front-loading medical injector and syringe for use therewith
US5391156A (en) * 1992-06-30 1995-02-21 Ethicon, Inc. Flexible encoscopic surgical port
US5399351A (en) * 1990-07-09 1995-03-21 Biomatrix, Inc. Biocompatible viscoelastic gel slurries, their preparation and use
US5496313A (en) * 1994-09-20 1996-03-05 Conmed Corporation System for detecting penetration of medical instruments
US5496312A (en) * 1993-10-07 1996-03-05 Valleylab Inc. Impedance and temperature generator control
US5601604A (en) * 1993-05-27 1997-02-11 Inamed Development Co. Universal gastric band
US5607418A (en) * 1995-08-22 1997-03-04 Illinois Institute Of Technology Implantable drug delivery apparatus
US5704893A (en) * 1994-07-11 1998-01-06 Dacomed Corportion Vessel occlusive apparatus and method
US5713911A (en) * 1996-10-03 1998-02-03 United States Surgical Corporation Surgical clip
US5733257A (en) * 1993-10-11 1998-03-31 Gambro Ab Method for calibrating a pump segment used in a peristaltic pump and a medical machine adapted for carrying out the method
US5861014A (en) * 1997-04-30 1999-01-19 Medtronic, Inc. Method and apparatus for sensing a stimulating gastrointestinal tract on-demand
USRE36176E (en) * 1993-02-18 1999-03-30 Kuzmak; Lubomyr I. Laparoscopic adjustable gastric banding device and method for implantation and removal thereof
US6010511A (en) * 1995-05-04 2000-01-04 Murphy; Richard Lesion diameter measurement catheter and method
US6013679A (en) * 1989-08-01 2000-01-11 Anika Research, Inc. Water-insoluble derivatives of hyaluronic acid and their methods of preparation and use
US6024704A (en) * 1998-04-30 2000-02-15 Medtronic, Inc Implantable medical device for sensing absolute blood pressure and barometric pressure
US6024340A (en) * 1996-12-04 2000-02-15 Active Control Experts, Inc. Valve assembly
US6042345A (en) * 1997-04-15 2000-03-28 Face International Corporation Piezoelectrically actuated fluid pumps
US6171321B1 (en) * 1995-02-24 2001-01-09 Heartport, Inc. Devices and methods for performing a vascular anastomosis
US6179569B1 (en) * 1997-01-10 2001-01-30 Japan Servo Co., Ltd. Liquid transportation apparatus
US6193734B1 (en) * 1998-01-23 2001-02-27 Heartport, Inc. System for performing vascular anastomoses
US6203523B1 (en) * 1998-02-02 2001-03-20 Medtronic Inc Implantable drug infusion device having a flow regulator
US20020038105A1 (en) * 1998-09-23 2002-03-28 Mayo Foundation For Medical Education And Research Automatic manifold for vascular catheter
US20030009123A1 (en) * 2001-07-07 2003-01-09 Nxstage Medical, Inc. Method and aparatus for leak detection in a fluid line
US20030014003A1 (en) * 2001-06-20 2003-01-16 The Regents Of The University Of California Hemodialysis system and method
US6511490B2 (en) * 2001-06-22 2003-01-28 Antoine Jean Henri Robert Gastric banding device and method
US20030019498A1 (en) * 1998-08-13 2003-01-30 Obtech Medical Ag. Non-injection port food intake restriction device
US6517556B1 (en) * 1999-10-28 2003-02-11 Niti Alloys Technologies Ltd. Shape memory alloy clip and method of use thereof
US6527701B1 (en) * 2000-09-29 2003-03-04 Precision Medical Devices, Inc. Body fluid flow control device
US20030045775A1 (en) * 1999-08-12 2003-03-06 Obtech Medical Ag. Hydraulic anal incontinence treatment
US20030045902A1 (en) * 2001-08-28 2003-03-06 Weadock Kevin S Composite staple for completing an anastomosis
US20030055311A1 (en) * 1996-02-15 2003-03-20 Neukermans Armand P. Biocompatible transducers
US20030060873A1 (en) * 2001-09-19 2003-03-27 Nanomedical Technologies, Inc. Metallic structures incorporating bioactive materials and methods for creating the same
US6676674B1 (en) * 1999-03-17 2004-01-13 Moshe Dudai Gastric band
US6681135B1 (en) * 2000-10-30 2004-01-20 Medtronic, Inc. System and method for employing temperature measurements to control the operation of an implantable medical device
US6685668B1 (en) * 2000-07-31 2004-02-03 Abbott Laboratories Closed-loop IV fluid flow control
US6691047B1 (en) * 2000-03-16 2004-02-10 Aksys, Ltd. Calibration of pumps, such as blood pumps of dialysis machine
US20040034479A1 (en) * 2002-08-07 2004-02-19 Akihiro Shimase Sample dispensing apparatus and automatic analyzer using the same
US20040044332A1 (en) * 2000-11-03 2004-03-04 Nikolaus Stergiopulos Implantable medical device for delivering a liquid
US20040049209A1 (en) * 2000-05-12 2004-03-11 Salomon Benchetrit Adjustable gastroplastry ring comprising a grip tab
US20040059393A1 (en) * 2001-01-05 2004-03-25 Shai Policker Regulation of eating habits
US20050002984A1 (en) * 2003-06-27 2005-01-06 Byrum Randal T. Implantable band with attachment mechanism having dissimilar material properties
US20050038484A1 (en) * 2003-02-03 2005-02-17 Enteromedics, Inc. Controlled vagal blockage therapy
US20050038498A1 (en) * 2003-04-17 2005-02-17 Nanosys, Inc. Medical device applications of nanostructured surfaces
US20050055039A1 (en) * 2003-07-28 2005-03-10 Polymorfix, Inc. Devices and methods for pyloric anchoring
US6871090B1 (en) * 2000-10-13 2005-03-22 Advanced Bionics Corporation Switching regulator for implantable spinal cord stimulation
US20050070934A1 (en) * 2003-09-30 2005-03-31 Tanaka Don A. Anastomosis wire ring device
US20050070937A1 (en) * 2003-09-30 2005-03-31 Jambor Kristin L. Segmented gastric band
US20050109973A1 (en) * 2003-11-21 2005-05-26 Glime William H. Valve diaphragm
US20060009697A1 (en) * 2004-04-07 2006-01-12 Triage Wireless, Inc. Wireless, internet-based system for measuring vital signs from a plurality of patients in a hospital or medical clinic
US20060015138A1 (en) * 2004-07-19 2006-01-19 Michael Gertner Emboli diverting devices created by microfabricated means
US20060020298A1 (en) * 2004-07-20 2006-01-26 Camilleri Michael L Systems and methods for curbing appetite
US20060041183A1 (en) * 2004-08-20 2006-02-23 Massen Richard J Electromechanical machine-based artificial muscles, bio-valves and related devices
US7017582B2 (en) * 2002-02-04 2006-03-28 Restore Medical Inc. Stiffening pharyngeal wall treatment
US7017883B2 (en) * 2001-08-14 2006-03-28 Continential Teves Ag & Co. Ohg Piezoelectrically actuated fluid valve
US20070000843A1 (en) * 2005-06-29 2007-01-04 Christopher Kimball Apparatus for measuring a set of electrical characteristics in a plasma
US20070001447A1 (en) * 2005-05-20 2007-01-04 Fennington George J Jr Gauge tee device
US20070016231A1 (en) * 2005-07-15 2007-01-18 Jambor Kristin L Precurved gastric band
US20070015955A1 (en) * 2005-07-15 2007-01-18 Mark Tsonton Accordion-like gastric band
US20070016262A1 (en) * 2005-07-13 2007-01-18 Betastim, Ltd. Gi and pancreatic device for treating obesity and diabetes
US20070015954A1 (en) * 2005-07-15 2007-01-18 Dlugos Daniel F Gastric band with mating end profiles
US20070015956A1 (en) * 2005-07-15 2007-01-18 Crawford Norman D Latching device for gastric band
US20070027358A1 (en) * 2004-03-23 2007-02-01 Michael Gertner Devices and methods to treat a patient
US20070027356A1 (en) * 2005-07-28 2007-02-01 Ethicon Endo-Surgery, Inc. Electroactive polymer actuated gastric band
US7172607B2 (en) * 2002-08-16 2007-02-06 Ami Agency For Medical Innovations Gmbh Device for generating an artificial constriction in the gastrointestinal tract
US7177693B2 (en) * 2004-01-07 2007-02-13 Medtronic, Inc. Gastric stimulation for altered perception to treat obesity
US20070044655A1 (en) * 2005-08-23 2007-03-01 Fish Elson B Removable end plug
US7191007B2 (en) * 2004-06-24 2007-03-13 Ethicon Endo-Surgery, Inc Spatially decoupled twin secondary coils for optimizing transcutaneous energy transfer (TET) power transfer characteristics
US7195610B1 (en) * 2001-09-17 2007-03-27 Cardinal Health 303, Inc. Pneumatic syringe driver
US20070219597A1 (en) * 2006-02-09 2007-09-20 Dean Kamen Adhesive and peripheral systems and methods for medical devices
US7314443B2 (en) * 2002-03-08 2008-01-01 Allergan Medical S.A. Implantable device
US7314636B2 (en) * 2001-06-29 2008-01-01 Medgraft Microtech, Inc. Biodegradable injectable implants containing glycolic acid
US7314598B2 (en) * 2003-02-14 2008-01-01 Stack System Co., Ltd. Dispenser and dispensing device
US20080009680A1 (en) * 2005-06-24 2008-01-10 Hassler William L Jr Remote monitoring and adjustment of a food intake restriction device
US20080015406A1 (en) * 2005-02-24 2008-01-17 Dlugos Daniel F External Mechanical Pressure Sensor for Gastric Band Pressure Measurements
US20080027269A1 (en) * 2006-04-04 2008-01-31 Michael Gertner Methods of using pericardial inserts
US20080027469A1 (en) * 2002-09-04 2008-01-31 Endoart Sa Surgical ring featuring a reversible diameter remote control system
US20080071306A1 (en) * 2004-03-23 2008-03-20 Michael Gertner Extragastric Balloon With Attachment Tabs
US7481763B2 (en) * 2004-05-28 2009-01-27 Ethicon Endo-Surgery, Inc. Metal bellows position feedback for hydraulic control of an adjustable gastric band
US20090054914A1 (en) * 2005-04-11 2009-02-26 Wolfgang Lechner Controllable Gastric Band
US20100010291A1 (en) * 2008-07-14 2010-01-14 Allergan, Inc. Implantable pump system with calibration
US7658196B2 (en) * 2005-02-24 2010-02-09 Ethicon Endo-Surgery, Inc. System and method for determining implanted device orientation
US7862502B2 (en) * 2006-10-20 2011-01-04 Ellipse Technologies, Inc. Method and apparatus for adjusting a gastrointestinal restriction device
US7879068B2 (en) * 2005-01-14 2011-02-01 Ethicon Endo-Surgery, Inc. Feedback sensing for a mechanical restrictive device

Family Cites Families (465)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1830947A (en) 1927-04-18 1931-11-10 Edward L Klingel Ground clamp
US1999683A (en) 1933-12-01 1935-04-30 Helge A Borresen Hose clamp
US2013025A (en) 1934-04-26 1935-09-03 Girdler Corp Process of solidifying material
US2163048A (en) 1937-02-13 1939-06-20 Mckee Brothers Corp Band clamp
US2405667A (en) 1944-01-20 1946-08-13 Ottesen Andrew Receptacle cover
US2635907A (en) 1950-11-13 1953-04-21 Brummer Mfg Corp Seal for shafts
US2936980A (en) 1954-10-01 1960-05-17 Illinois Tool Works Cable strap
US2714469A (en) 1954-11-24 1955-08-02 Emery Carpenter Container Comp Locking ring construction
US3059645A (en) 1960-11-28 1962-10-23 Paul A Hasbrouck Adjustable clamp
US3189961A (en) 1963-09-17 1965-06-22 Rotron Mfg Co Hose clamp
NL6701946A (en) 1966-02-10 1967-08-11
FR1566202A (en) 1967-12-27 1969-05-09
BE758322A (en) 1969-11-03 1971-04-01 Bosch Gmbh Robert Device for wiping windows such as headlights ice and defeux rear of motor vehicles
CA949965A (en) 1971-12-03 1974-06-25 Robert H. Marchessault Method of preparing cross-linked starch and starch derivatives
US3955834A (en) 1972-02-11 1976-05-11 Aktiebolaget Svenska Flaktfabriken Apparatus for connecting ducts with a self-sealing joint
US3840018A (en) 1973-01-31 1974-10-08 M Heifetz Clamp for occluding tubular conduits in the human body
US4053176A (en) 1975-10-15 1977-10-11 West Chester Chemical Co., Inc. Collar for sealing pipe joints
US4118805A (en) 1977-02-28 1978-10-10 Codman & Shurtleff, Inc. Artificial sphincter
US4157713A (en) 1977-05-11 1979-06-12 Clarey Michael T Air-pressure splint
DE2721548C2 (en) 1977-05-13 1982-11-04 Friedrich Gerd 5000 Koeln De Lauterjung
US4117727A (en) 1977-12-12 1978-10-03 Friswell David R Bubble sensor and method
US4286584A (en) 1978-06-16 1981-09-01 Infusaid Corporation Septum locating apparatus
US4176412A (en) 1978-09-15 1979-12-04 The Kendall Company Urine collection device
US4340083A (en) 1978-11-30 1982-07-20 Carleton Controls Corporation Deflectable beam valve
US4299012A (en) 1979-05-08 1981-11-10 Hans Oetiker Hose clamp
US4271827A (en) 1979-09-13 1981-06-09 Angelchik Jean P Method for prevention of gastro esophageal reflux
CA1156003A (en) 1979-10-30 1983-11-01 Juan Voltas Baro Apparatus for the continence of digestive stomas and anal incontinence
US4375882A (en) * 1980-10-27 1983-03-08 Schreiber Jr Lloyd J In-line flow control apparatus
DE3048051C2 (en) 1980-12-19 1985-08-29 Siemens Ag, 1000 Berlin Und 8000 Muenchen, De
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
JPH036454Y2 (en) 1981-04-22 1991-02-19
US4406656A (en) 1981-06-01 1983-09-27 Brack Gillium Hattler Venous catheter having collapsible multi-lumens
US4417567A (en) 1981-08-12 1983-11-29 Medical Engineering Corporation Artificial sphincter
US4582640A (en) 1982-03-08 1986-04-15 Collagen Corporation Injectable cross-linked collagen implant material
US4408597A (en) 1982-04-23 1983-10-11 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Prosthetic occlusive device for an internal passageway
US4485805A (en) 1982-08-24 1984-12-04 Gunther Pacific Limited Of Hong Kong Weight loss device and method
US4450375A (en) 1982-11-12 1984-05-22 Kiwi Coders Corporation Piezoelectric fluid control device
US4551862A (en) 1982-12-15 1985-11-12 Haber Terry M Prosthetic sphincter
US4558699A (en) 1983-01-03 1985-12-17 Bashour Samuel B Method of and apparatus for restricting the passage of food through the stomach
US4592355A (en) 1983-01-28 1986-06-03 Eliahu Antebi Process for tying live tissue and an instrument for performing the tying operation
DE3309788C2 (en) 1983-03-18 1985-12-05 Karl Dr. 6301 Pohlheim De Aigner
EP0189417B1 (en) 1983-10-25 1989-03-08 Microdialogsystem Cuff equipment for, inter alia, achieving and maintaining fluid- and gas-depleted regions in parts of the body
US4716154A (en) 1984-06-08 1987-12-29 Pharmacia Ab Gel of crosslinked hyaluronic acid for use as a vitreous humor substitute
US4559699A (en) 1984-06-08 1985-12-24 Westinghouse Electric Corp. Method of constructing a padmounted distribution transformer
CA1263647A (en) 1984-07-23 1989-12-05 Belder Anthony Norman De Method of preventing adhesion between body tissues, means for preventing such adhesion, and process for producing said means
US4603699A (en) 1984-11-20 1986-08-05 Himpens Jacques M Apparatus and method for measuring osmotic pressure in situ
US4582865A (en) 1984-12-06 1986-04-15 Biomatrix, Inc. Cross-linked gels of hyaluronic acid and products containing such gels
US4881939A (en) 1985-02-19 1989-11-21 The Johns Hopkins University Implantable helical cuff
US4601713A (en) 1985-06-11 1986-07-22 Genus Catheter Technologies, Inc. Variable diameter catheter
US4592339A (en) 1985-06-12 1986-06-03 Mentor Corporation Gastric banding device
US4671351A (en) 1985-07-17 1987-06-09 Vertech Treatment Systems, Inc. Fluid treatment apparatus and heat exchanger
US4696288A (en) 1985-08-14 1987-09-29 Kuzmak Lubomyr I Calibrating apparatus and method of using same for gastric banding surgery
US4710174A (en) 1985-12-16 1987-12-01 Surgical Engineering Associates, Inc. Implantable infusion port
US4753086A (en) 1986-01-13 1988-06-28 Schmidt Kenneth J Costume jewelry circlet
US4694827A (en) 1986-01-14 1987-09-22 Weiner Brian C Inflatable gastric device for treating obesity and method of using the same
US5120313A (en) 1986-03-28 1992-06-09 Nancy W. Elftman Method for measuring blood pressure in an animal or human using a percutaneous access port
US4693695A (en) 1986-03-31 1987-09-15 Cheng Peter S C Ascending and descending balloon action toy
US4708140A (en) 1986-05-08 1987-11-24 Baron Howard C Atraumatic vascular balloon clamp
JPH0126944B2 (en) 1986-09-17 1989-05-25 Shinagawa Shoko Kk
US5385938B1 (en) 1986-12-23 1997-07-15 Tristrata Inc Method of using glycolic acid for treating wrinkles
GB8701731D0 (en) 1987-01-27 1987-03-04 Patcentre Benelux Nv Sa Pumps
US4760837A (en) 1987-02-19 1988-08-02 Inamed Development Company Apparatus for verifying the position of needle tip within the injection reservoir of an implantable medical device
US4919650A (en) 1987-03-30 1990-04-24 Bionica Pty. Limited Infusion pump
EP0287920B1 (en) 1987-04-22 1991-05-15 Siemens Aktiengesellschaft Piston pump for a device for dosing medicaments
US4858619A (en) 1987-06-29 1989-08-22 Toth Marie A Intracranial pressure monitoring system
US6174999B1 (en) 1987-09-18 2001-01-16 Genzyme Corporation Water insoluble derivatives of polyanionic polysaccharides
US4872483B1 (en) 1987-12-31 1993-01-26 Int Medical Products Inc
US4915690A (en) 1988-02-02 1990-04-10 C. R. Bard, Inc. Micro-injection port
DE58908695D1 (en) 1988-05-28 1995-01-12 Hasler Werke Stiftung Query and telecontrol device.
US4925446A (en) 1988-07-06 1990-05-15 Transpharm Group Inc. Removable inflatable intragastrointestinal device for delivering beneficial agents
US4969899A (en) 1989-03-08 1990-11-13 Cox-Uphoff International Inflatable implant
US5045060A (en) 1989-04-26 1991-09-03 Therex Corp. Implantable infusion device
US4944487A (en) 1989-05-08 1990-07-31 Lee Company Diaphragm valve
US4994019A (en) 1989-07-28 1991-02-19 Micro-Magnetics, Inc. Magnetic occluding device
EP0416250A3 (en) 1989-08-01 1991-08-28 The Research Foundation Of State University Of New York N-acylurea and o-acylisourea derivatives of hyaluronic acid
US5116652A (en) 1989-10-13 1992-05-26 Abbott Laboratories Kink-resistant medical tubing and catheters
DE9014048U1 (en) 1990-03-22 1990-12-13 Ab Hepar
US5458568A (en) 1991-05-24 1995-10-17 Cortrak Medical, Inc. Porous balloon for selective dilatation and drug delivery
US5143724A (en) 1990-07-09 1992-09-01 Biomatrix, Inc. Biocompatible viscoelastic gel slurries, their preparation and use
US5074868A (en) 1990-08-03 1991-12-24 Inamed Development Company Reversible stoma-adjustable gastric band
JP3115625B2 (en) 1991-03-30 2000-12-11 帝國製薬株式会社 Lidocaine-containing patch for external use
US5226429A (en) 1991-06-20 1993-07-13 Inamed Development Co. Laparoscopic gastric band and method
DE9107798U1 (en) 1991-06-25 1991-10-10 Steinbeck, Ulrich, Dr.Med., 2000 Hamburg, De
US5425716A (en) 1991-08-09 1995-06-20 Atom Kabushiki Kaisha Infusion apparatus
US5343894A (en) 1991-09-30 1994-09-06 Hoerbiger Ventilwerke Aktiengesellschaft Piezo valve
US5360445A (en) 1991-11-06 1994-11-01 International Business Machines Corporation Blood pump actuator
US5160338A (en) 1991-11-13 1992-11-03 Inamed Development Co. Device for removing implantable articles
US5318533A (en) 1992-02-21 1994-06-07 Scimed Life Systems, Inc. Balloon catheter inflation device including apparatus for monitoring and wireless transmission of inflation data, and system
US5259399A (en) 1992-03-02 1993-11-09 Alan Brown Device and method of causing weight loss using removable variable volume intragastric bladder
US5224494A (en) 1992-03-19 1993-07-06 Enhorning Goran E Vaginal pessary
FR2688693A1 (en) 1992-03-19 1993-09-24 Ferriere Xavier Artificial sphincter, especially urethral (urinary) sphincter
US5246456A (en) 1992-06-08 1993-09-21 Wilkinson Lawrence H Fenestrated gastric pouch
DE4219888C2 (en) 1992-06-17 2003-01-02 Storz Endoskop Gmbh Schaffhaus Medical pressure transducer
US5326349A (en) 1992-07-09 1994-07-05 Baraff David R Artificial larynx
DE4225524C2 (en) 1992-08-01 1994-08-04 Fresenius Ag The implantable infusion device
US5676651A (en) 1992-08-06 1997-10-14 Electric Boat Corporation Surgically implantable pump arrangement and method for pumping body fluids
US6402718B1 (en) 1992-08-17 2002-06-11 Medrad, Inc. Front-loading medical injector and syringe for use therewith
US5972000A (en) 1992-11-13 1999-10-26 Influence Medical Technologies, Ltd. Non-linear anchor inserter device and bone anchors
ES2125310T3 (en) 1993-02-18 1999-03-01 Lubomyr Ihor Kuzmak Laparoscopic Adjustable Gastric Banding.
EP0784487A1 (en) 1993-03-19 1997-07-23 Medinvent A composition and a method for tissue augmentation
JP3105702B2 (en) 1993-06-11 2000-11-06 レーザーテック株式会社 Optical defect inspection apparatus
DE4320909C1 (en) 1993-06-18 1994-06-01 Siemens Ag Servo valve operating between inlet and outlet air nozzles - uses flexible beam held at one end in adjustable braked liner
US5944751A (en) 1993-09-17 1999-08-31 Zertl Medical, Inc. Vibratory heart valve
US5531716A (en) 1993-09-29 1996-07-02 Hercules Incorporated Medical devices subject to triggered disintegration
US5658298A (en) 1993-11-09 1997-08-19 Inamed Development Company Laparoscopic tool
FR2712696B1 (en) 1993-11-17 1996-02-02 Inst Francais Du Petrole Method and device for measuring the pore volume of a solid sample.
DE69410487D1 (en) 1993-12-28 1998-06-25 Westonbridge Int Ltd micropump
US5762599A (en) 1994-05-02 1998-06-09 Influence Medical Technologies, Ltd. Magnetically-coupled implantable medical devices
US5449363A (en) 1994-05-06 1995-09-12 Browne Medical Systems, Inc. Endoscopic lithotripsy system
US5653718A (en) 1994-05-16 1997-08-05 Yoon; Inbae Cannula anchoring system
DE69534453D1 (en) 1994-05-17 2005-10-20 Hadasit Med Res Service System for coronary angioplasty
DE4417927B4 (en) 1994-05-19 2005-02-03 Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin Telemetry device, particularly for a tissue stimulator system
US5509888A (en) 1994-07-26 1996-04-23 Conceptek Corporation Controller valve device and method
US5681284A (en) 1994-10-31 1997-10-28 Glenn Herskowitz Infusion pump with tube spike holder
US5591217A (en) 1995-01-04 1997-01-07 Plexus, Inc. Implantable stimulator with replenishable, high value capacitive power source and method therefor
EP0723783A1 (en) 1995-01-26 1996-07-31 Siemens Elema AB Device for locating a port on a medical implant
US5562714A (en) 1995-02-03 1996-10-08 Medtronic, Inc. Magnetic field strength regulator for implant
US5695504A (en) 1995-02-24 1997-12-09 Heartport, Inc. Devices and methods for performing a vascular anastomosis
US5535752A (en) 1995-02-27 1996-07-16 Medtronic, Inc. Implantable capacitive absolute pressure and temperature monitor system
JP3707822B2 (en) 1995-03-23 2005-10-19 富士写真フイルム株式会社 Image display device
FR2733426B1 (en) 1995-04-25 1997-07-18 Debacker Yves Medical device for filling deformations of skin volume such as wrinkles and scars by injection of two different physico-chemical forms of a biological polymer
US6102922A (en) 1995-09-22 2000-08-15 Kirk Promotions Limited Surgical method and device for reducing the food intake of patient
WO1997027829A1 (en) 1996-01-31 1997-08-07 The Trustees Of The University Of Pennsylvania Remote control drug delivery device
US6048309A (en) 1996-03-04 2000-04-11 Heartport, Inc. Soft tissue retractor and delivery device therefor
US6117086A (en) 1996-04-18 2000-09-12 Sunscope International, Inc. Pressure transducer apparatus with disposable dome
US5766232A (en) 1996-05-10 1998-06-16 Medtronic, Inc. Method and apparatus for altering the Q of an implantable medical device telemetry antenna
US5944696A (en) 1996-06-03 1999-08-31 Bayless; William Brian Swivel clip medical tube holder
US5833698A (en) 1996-07-23 1998-11-10 United States Surgical Corporation Anastomosis instrument and method
US5785295A (en) 1996-08-27 1998-07-28 Industrial Technology Research Institute Thermally buckling control microvalve
WO1998017285A1 (en) 1996-10-17 1998-04-30 Fidia S.P.A. Pharmaceutical preparations comprised of salts of hyaluronic acid with local anaesthetics
US5807311A (en) 1996-11-29 1998-09-15 Palestrant; Aubrey M. Dialysis catheter having rigid and collapsible lumens and related method
US5997517A (en) 1997-01-27 1999-12-07 Sts Biopolymers, Inc. Bonding layers for medical device surface coatings
FR2759576B1 (en) 1997-02-17 1999-08-06 Corneal Ind Implant sclero-keratectomy pre-descemetic
FR2759577B1 (en) 1997-02-17 1999-08-06 Corneal Ind implant for deep sclerectomy
JP3274384B2 (en) 1997-03-31 2002-04-15 株式会社パイオラックス Indwelling catheter and insertion device
DE69723955D1 (en) 1997-04-04 2003-09-11 Christian Peclat peristaltic pump
US5938669A (en) 1997-05-07 1999-08-17 Klasamed S.A. Adjustable gastric banding device for contracting a patient's stomach
US6129668A (en) 1997-05-08 2000-10-10 Lucent Medical Systems, Inc. System and method to determine the location and orientation of an indwelling medical device
US5808203A (en) 1997-05-12 1998-09-15 Medrad, Inc. Fluid pressure measurement devices
US6391336B1 (en) 1997-09-22 2002-05-21 Royer Biomedical, Inc. Inorganic-polymer complexes for the controlled release of compounds including medicinals
US6090131A (en) 1997-09-25 2000-07-18 Daley; Robert J. Bioabsorbable staples
FR2769491B1 (en) 1997-10-15 2000-01-07 Patrick Sangouard adjustable artificial sphincter with magnetic control
NL1007349C2 (en) 1997-10-24 1999-04-27 Suyker Wilhelmus Joseph Leonardus System for mechanical production of anastomoses between hollow structures; as well as device and applicator for use therewith.
US5993473A (en) 1997-11-19 1999-11-30 Chan; Yung C. Expandable body device for the gastric cavity and method
DE19802615A1 (en) 1998-01-24 1999-08-12 Manfred Adolfs Connecting element for connecting a transducer having a sealed fluid system
JPH11244395A (en) 1998-02-19 1999-09-14 Due Eng & Dev Ltd Device for transferring energy through skins and method for controlling and adjusting its conbination of electric power
US6164933A (en) 1998-04-27 2000-12-26 Matsushita Electric Works, Ltd. Method of measuring a pressure of a pressurized fluid fed through a diaphragm pump and accumulated in a vessel, and miniature pump system effecting the measurement
US5910149A (en) 1998-04-29 1999-06-08 Kuzmak; Lubomyr I. Non-slipping gastric band
US7647237B2 (en) 1998-04-29 2010-01-12 Minimed, Inc. Communication station and software for interfacing with an infusion pump, analyte monitor, analyte meter, or the like
US6601604B1 (en) 1998-05-08 2003-08-05 Michael S. Cooper Fire-control sprinkler system
US6113609A (en) 1998-05-26 2000-09-05 Scimed Life Systems, Inc. Implantable tissue fastener and system for treating gastroesophageal reflux disease
GB9811398D0 (en) 1998-05-27 1998-07-22 Pbt Limited Spool valve
US6074341A (en) 1998-06-09 2000-06-13 Timm Medical Technologies, Inc. Vessel occlusive apparatus and method
FR2780730B1 (en) 1998-07-01 2000-10-13 Corneal Ind Injectable compositions biphasic, particularly useful Reconstructive and Aesthetic Surgery
US6221024B1 (en) 1998-07-20 2001-04-24 Medtronic, Inc. Implantable pressure sensor and method of fabrication
US6210347B1 (en) 1998-08-13 2001-04-03 Peter Forsell Remote control food intake restriction device
US6067991A (en) 1998-08-13 2000-05-30 Forsell; Peter Mechanical food intake restriction device
FR2783153B1 (en) 1998-09-14 2000-12-01 Jerome Dargent gastric constriction device
US6306088B1 (en) 1998-10-03 2001-10-23 Individual Monitoring Systems, Inc. Ambulatory distributed recorders system for diagnosing medical disorders
US6024755A (en) 1998-12-11 2000-02-15 Embol-X, Inc. Suture-free clamp and sealing port and methods of use
US6635049B1 (en) 1999-04-30 2003-10-21 Medtronic, Inc. Drug bolus delivery system
CA2368765C (en) 1999-05-04 2005-01-11 Simon Marcus Horner Augmenting cardiac function
US6372494B1 (en) 1999-05-14 2002-04-16 Advanced Tissue Sciences, Inc. Methods of making conditioned cell culture medium compositions
US20050192629A1 (en) 1999-06-25 2005-09-01 Usgi Medical Inc. Methods and apparatus for creating and regulating a gastric stoma
DE19931990C1 (en) 1999-07-09 2001-01-11 Festo Ag & Co solenoid valve
EP1072282A1 (en) 1999-07-19 2001-01-31 EndoArt S.A. Flow control device
FR2797181B1 (en) 1999-08-05 2002-05-03 Richard Cancel Gastric band device remote to form a restricted stoma opening in the stomach
US6454701B1 (en) 1999-08-12 2002-09-24 Obtech Medical Ag Heartburn and reflux disease treatment apparatus with energy transfer device
US6453907B1 (en) 1999-08-12 2002-09-24 Obtech Medical Ag Food intake restriction with energy transfer device
US6503189B1 (en) 1999-08-12 2003-01-07 Obtech Medical Ag Controlled anal incontinence disease treatment
US6464628B1 (en) 1999-08-12 2002-10-15 Obtech Medical Ag Mechanical anal incontinence
ES2338208T3 (en) 1999-08-12 2010-05-05 Potencia Medical Ag Apparatus for forming a stoma opening.
EP1259201A2 (en) 2000-02-11 2002-11-27 Obtech Medical AG Food intake restriction apparatus with controlled wireless energy supply
US6306116B1 (en) 1999-09-30 2001-10-23 Origin Medsystems, Inc. Method and apparatus for pressurizing the right atrium or right ventricle to assist cardiac function during beating heart surgery
FR2799118B1 (en) 1999-10-01 2002-07-12 Medical Innovation Dev adjustable gastric implant
US6910479B1 (en) 1999-10-04 2005-06-28 Advanced Respiratory, Inc. Airway treatment apparatus with bias line cancellation
US20030208212A1 (en) 1999-12-07 2003-11-06 Valerio Cigaina Removable gastric band
JP2003526410A (en) 1999-12-07 2003-09-09 トランスニューロニックス インコーポレイテッド Band of removable stomach
FR2802407B1 (en) 1999-12-21 2002-12-13 Rc Medical gastroplasty ring releasable
FR2804011B1 (en) 2000-01-20 2002-07-19 Rc Medical gastroplasty ring single command
US7204821B1 (en) 2000-01-31 2007-04-17 Ethicon, Inc. Surgical fluid management system with suction control
US6454700B1 (en) 2000-02-09 2002-09-24 Obtech Medical Ag Heartburn and reflux disease treatment apparatus with wireless energy supply
US6463935B1 (en) 2000-02-10 2002-10-15 Obtech Medical Ag Controlled heartburn and reflux disease treatment
US6470892B1 (en) 2000-02-10 2002-10-29 Obtech Medical Ag Mechanical heartburn and reflux treatment
US6450946B1 (en) 2000-02-11 2002-09-17 Obtech Medical Ag Food intake restriction with wireless energy transfer
US6454699B1 (en) 2000-02-11 2002-09-24 Obtech Medical Ag Food intake restriction with controlled wireless energy supply
US6475136B1 (en) 2000-02-14 2002-11-05 Obtech Medical Ag Hydraulic heartburn and reflux treatment
US6454785B2 (en) 2000-02-24 2002-09-24 DE HOYOS GARZA ANDRéS Percutaneous intragastric balloon catheter for the treatment of obesity
FR2805986B1 (en) 2000-03-13 2002-10-11 Districlass Madical intragastric device has variable volume
DE10013519A1 (en) 2000-03-20 2001-10-04 Adeva Medical Ges Fuer Entwick An implantable sphincter
KR20010096388A (en) 2000-04-19 2001-11-07 진세훈 Human glans enhancing materials and glans enhancing method
DE60114411T2 (en) 2000-05-25 2006-07-20 Debiotech S.A. Micro Machined fluidic device and manufacturing method
US20030191433A1 (en) 2000-05-31 2003-10-09 Prentiss John Gilbert Breast pump
US6419696B1 (en) 2000-07-06 2002-07-16 Paul A. Spence Annuloplasty devices and related heart valve repair methods
FR2811671B1 (en) 2000-07-17 2003-02-28 Corneal Ind Hydrogel polymer (s), resistant to biodegradation, preparation and use as tissue regeneration medium
FR2811996B1 (en) 2000-07-19 2003-08-08 Corneal Ind crosslinking polysaccharide (s), hydrogel preparation (s); polysaccharide (s) and hydrogel (s) obtained, their uses
US20030167022A1 (en) 2000-07-26 2003-09-04 Gerrat Dijkman Catheter for measuring pressure
WO2002009792A1 (en) 2000-07-28 2002-02-07 Anika Therapeutics, Inc. Bioabsorbable composites of derivatized hyaluronic acid
JP4240779B2 (en) 2000-07-31 2009-03-18 ソニー株式会社 A liquid crystal projector and the adjustment method
FR2813786B1 (en) 2000-09-11 2003-03-14 Medical Innovation Dev Method and swelling control device of an inflatable prosthetic envelope and prosthesis by applying
US6432040B1 (en) 2000-09-14 2002-08-13 Nizam N. Meah Implantable esophageal sphincter apparatus for gastroesophageal reflux disease and method
US7198250B2 (en) 2000-09-18 2007-04-03 Par Technologies, Llc Piezoelectric actuator and pump using same
US20020072780A1 (en) 2000-09-26 2002-06-13 Transneuronix, Inc. Method and apparatus for intentional impairment of gastric motility and /or efficiency by triggered electrical stimulation of the gastrointestinal tract with respect to the intrinsic gastric electrical activity
US6924273B2 (en) 2000-10-03 2005-08-02 Scott W. Pierce Chondroprotective/restorative compositions and methods of use thereof
US6615084B1 (en) 2000-11-15 2003-09-02 Transneuronix, Inc. Process for electrostimulation treatment of morbid obesity
US6579301B1 (en) 2000-11-17 2003-06-17 Syntheon, Llc Intragastric balloon device adapted to be repeatedly varied in volume without external assistance
FR2816828B1 (en) 2000-11-23 2004-10-22 Richard Cancel Device implementing remote and unconnected material of an implant and implant implemented by this device
US6609025B2 (en) 2001-01-02 2003-08-19 Cyberonics, Inc. Treatment of obesity by bilateral sub-diaphragmatic nerve stimulation
US6572627B2 (en) 2001-01-08 2003-06-03 Shlomo Gabbay System to inhibit and/or control expansion of anatomical features
US20020098097A1 (en) 2001-01-22 2002-07-25 Angad Singh Magnetically-actuated micropump
US20020103430A1 (en) 2001-01-29 2002-08-01 Hastings Roger N. Catheter navigation within an MR imaging device
US7040349B2 (en) 2002-03-27 2006-05-09 Viking Technologies, L.C. Piezo-electric actuated multi-valve manifold
US6450987B1 (en) 2001-02-01 2002-09-17 Innercool Therapies, Inc. Collapsible guidewire lumen
US6474584B2 (en) 2001-02-20 2002-11-05 Faruk Ekich Fly tying method and apparatus
EP1234554A1 (en) 2001-02-21 2002-08-28 EndoArt SA Vascular graft with internal deflector
US7119062B1 (en) 2001-02-23 2006-10-10 Neucoll, Inc. Methods and compositions for improved articular surgery using collagen
US7044933B2 (en) 2001-03-01 2006-05-16 Scimed Life Systems, Inc. Fluid injection system for coronary intervention
US6723053B2 (en) 2001-03-14 2004-04-20 Coopersurgical, Inc. Esophageal balloon catheter device
US6513403B2 (en) 2001-04-03 2003-02-04 Cray Inc. Flexible drive rod for access to enclosed locations
US6889086B2 (en) 2001-04-06 2005-05-03 Cardiac Pacemakers, Inc. Passive telemetry system for implantable medical device
JP4246998B2 (en) 2001-04-18 2009-04-02 インパルス ダイナミックス エヌヴィ Analysis of eating habits
FR2823663B1 (en) 2001-04-18 2004-01-02 Cousin Biotech Device for treatment of morbid obesity
KR100429773B1 (en) 2001-04-20 2004-05-03 김철원 Device for injecting liquid transmitting pressure of pressure gage and sensor protector, injecting method using this and diapram housing equipped with nipple
FR2825264B1 (en) 2001-06-01 2004-04-02 Surgical Diffusion Ring gastroplasty
US6635020B2 (en) 2001-06-26 2003-10-21 Thermometrics Reusable fluid pressure transducer monitoring apparatus
US6457801B1 (en) 2001-06-27 2002-10-01 Lexmark International, Inc. Method and apparatus for measuring ink dry time
DE10139857B4 (en) 2001-08-14 2009-09-10 Robert Bosch Gmbh Valve for controlling fluids
US6754527B2 (en) 2001-09-06 2004-06-22 Medtronic, Inc. System and method for reducing noise in an implantable medical device
US6770067B2 (en) 2001-09-07 2004-08-03 Medtronic Minimed, Inc. Infusion device and driving mechanism for same
US6796004B2 (en) 2001-09-14 2004-09-28 Donaldson Company, Inc. Exhaust system clamp
US6632239B2 (en) 2001-10-02 2003-10-14 Spiration, Inc. Constriction device including reinforced suture holes
US6659937B2 (en) 2001-10-11 2003-12-09 M. Sheldon Polsky Continent bladder access device
US7686781B2 (en) 2001-10-25 2010-03-30 Emory University Catheter for modified perfusion
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
US6892095B2 (en) 2001-12-31 2005-05-10 Cardiac Pacemakers, Inc. Method and apparatus for monitoring left ventricular work or power
KR100463897B1 (en) 2002-01-09 2004-12-30 충북대학교 산학협력단 Method and system for obtaining characteristic measuring factors of pneumotachometer
FR2834443B1 (en) 2002-01-09 2004-04-02 Sofradim Production Ring gastric treatment of obesity
FR2834444B1 (en) 2002-01-09 2004-10-29 Sofradim Production Ring gastric treatment of obesity
WO2003058067A1 (en) 2002-01-10 2003-07-17 Interacoustics A/S Piezo electric pump and device with such pump
US20080234354A1 (en) 2006-11-21 2008-09-25 Lippa Arnold S Methods And Compositions For Controlling Body Weight And Appetite
FR2834631B1 (en) 2002-01-15 2004-10-22 Cie Euro Etude Rech Paroscopie gastroplasty ring in elastomer material hardness is variable
US7544177B2 (en) 2002-01-24 2009-06-09 The Regents Of The University Of California Aerosol device to deliver bioactive agent
US20030181890A1 (en) 2002-03-22 2003-09-25 Schulze Dale R. Medical device that removably attaches to a bodily organ
DE60213555T2 (en) 2002-03-28 2007-08-09 Fluid Automation Systems S.A. A solenoid valve
US6691556B2 (en) 2002-05-20 2004-02-17 General Electric Company Automatic data logging kit and method
EP1367307B1 (en) 2002-05-31 2004-07-21 FESTO AG & Co Piezo-electric valve
FR2840193B1 (en) 2002-05-31 2005-02-11 Textile Hi Tec Gastric Band
FR2840804B1 (en) 2002-06-13 2004-09-17 Richard Cancel System for the treatment of obesity and to implant such a system
US20040133219A1 (en) 2002-07-29 2004-07-08 Peter Forsell Multi-material constriction device for forming stoma opening
EP1534162B1 (en) 2002-08-13 2012-04-04 Allergan, Inc. Remotely adjustable gastric banding device
US7338433B2 (en) 2002-08-13 2008-03-04 Allergan, Inc. Remotely adjustable gastric banding method
DE60331457D1 (en) 2002-08-28 2010-04-08 Allergan Inc Fatigue-resistant gastric belt device
DE60223535T2 (en) 2002-09-04 2008-09-18 Endoart S.A. Device for closing surgical rings
US7901419B2 (en) 2002-09-04 2011-03-08 Allergan, Inc. Telemetrically controlled band for regulating functioning of a body organ or duct, and methods of making, implantation and use
US7972346B2 (en) 2002-09-04 2011-07-05 Allergan Medical S.A. Telemetrically controlled band for regulating functioning of a body organ or duct, and methods of making, implantation and use
US7216648B2 (en) 2002-09-06 2007-05-15 Apneon, Inc. Systems and methods for moving and/or restraining tissue in the upper respiratory system
EP1403519A1 (en) 2002-09-27 2004-03-31 Novo Nordisk A/S Membrane pump with stretchable pump membrane
DE10246340A1 (en) 2002-10-04 2004-04-29 Wohlrab, David, Dr. Combination preparation of hyaluronic acid and at least one local anesthetic and its use
US6905594B2 (en) 2002-10-11 2005-06-14 G6 Science Corp. Filter apparatus and methods to capture a desired amount of material from a sample suspension for monolayer deposition, analysis or other uses
US7037344B2 (en) 2002-11-01 2006-05-02 Valentx, Inc. Apparatus and methods for treatment of morbid obesity
US20040106899A1 (en) 2002-11-30 2004-06-03 Mcmichael Donald J. Gastric balloon catheter with improved balloon orientation
GB0229616D0 (en) 2002-12-19 2003-01-22 Nokia Corp Mobile communication
US7563249B2 (en) 2002-12-20 2009-07-21 Medrad, Inc. Syringe having an alignment flange, an extending lip and a radial expansion section of reduced wall thickness
US6940467B2 (en) 2003-01-10 2005-09-06 Atmel Germany Gmbh Circuit arrangement and method for deriving electrical power from an electromagnetic field
US7613515B2 (en) 2003-02-03 2009-11-03 Enteromedics Inc. High frequency vagal blockage therapy
JP4392474B2 (en) 2003-02-21 2010-01-06 兵神装備株式会社 Material supply system
US7682818B2 (en) 2003-03-28 2010-03-23 Fujifilm Corporation Apparatus for separating and purifying nucleic acid and method for separating and purifying nucleic acid
FR2861734B1 (en) 2003-04-10 2006-04-14 Corneal Ind Crosslinking polysaccharides low and high molecular weight; preparation of hydrogels injectable monophase; polysaccharides and hydrogels obtained
US7048519B2 (en) 2003-04-14 2006-05-23 Agilent Technologies, Inc. Closed-loop piezoelectric pump
DE502004004488D1 (en) 2003-06-04 2007-09-13 Ami Gmbh Means for generating an artificial constriction in the gastrointestinal tract
DE502004004119D1 (en) 2003-06-04 2007-08-02 Ami Gmbh Means for generating an artificial constriction in the gastrointestinal tract
FR2855744B1 (en) 2003-06-04 2006-04-14 Cie Euro Etude Rech Paroscopie Surgical ring closure system improves
DE502004009297D1 (en) 2003-06-04 2009-05-20 Ami Gmbh Means for generating an artificial constriction in the gastrointestinal tract
US8007474B2 (en) 2003-06-16 2011-08-30 Ethicon Endo-Surgery, Inc. Implantable medical device with reversible attachment mechanism and method
US7374557B2 (en) 2003-06-16 2008-05-20 Ethicon Endo-Surgery, Inc. Subcutaneous self attaching injection port with integral fasteners
US7862546B2 (en) 2003-06-16 2011-01-04 Ethicon Endo-Surgery, Inc. Subcutaneous self attaching injection port with integral moveable retention members
WO2004112563A3 (en) 2003-06-20 2005-10-06 Metacure N V Gastrointestinal methods and apparatus for use in treating disorders
ES2328567T3 (en) 2003-06-20 2009-11-16 Allergan, Inc. Two-way valve.
DE602004023898D1 (en) 2003-06-27 2009-12-17 Ethicon Endo Surgery Inc An implantable band with a connection device consisting of materials with different material properties
US7951067B2 (en) 2003-06-27 2011-05-31 Ethicon Endo-Surgery, Inc. Implantable band having improved attachment mechanism
US20040267292A1 (en) 2003-06-27 2004-12-30 Byrum Randal T. Implantable band with transverse attachment mechanism
US20040267291A1 (en) 2003-06-27 2004-12-30 Byrum Randal T. Implantable band with non-mechanical attachment mechanism
US7500944B2 (en) 2003-06-27 2009-03-10 Ethicon Endo-Surgery, Inc. Implantable band with attachment mechanism
WO2005007232A3 (en) 2003-07-21 2005-08-04 Impulse Dynamics Nv Gastrointestinal methods and apparatus for use in treating disorders and controlling blood sugar
EP1648355B1 (en) 2003-07-25 2008-07-23 Wolfgang Lechner Adjustable stomach band
CA2534033A1 (en) 2003-07-30 2005-02-10 Anteis S.A. Complex matrix for biomedical use
US7263405B2 (en) 2003-08-27 2007-08-28 Neuro And Cardiac Technologies Llc System and method for providing electrical pulses to the vagus nerve(s) to provide therapy for obesity, eating disorders, neurological and neuropsychiatric disorders with a stimulator, comprising bi-directional communication and network capabilities
US7144400B2 (en) 2003-10-01 2006-12-05 Ethicon Endo-Surgery, Inc. Gastric band introduction device
US7284966B2 (en) 2003-10-01 2007-10-23 Agency For Science, Technology & Research Micro-pump
KR100529496B1 (en) 2003-10-17 2005-11-21 현대모비스 주식회사 Passenger air bag system of vehicle
US7054690B2 (en) 2003-10-22 2006-05-30 Intrapace, Inc. Gastrointestinal stimulation device
US7758493B2 (en) 2003-10-23 2010-07-20 Proxy Biomedical Limited Gastric constriction device
US7299082B2 (en) 2003-10-31 2007-11-20 Abbott Diabetes Care, Inc. Method of calibrating an analyte-measurement device, and associated methods, devices and systems
US20050100779A1 (en) 2003-11-07 2005-05-12 Gertner Michael E. Three dimensional polymeric fuel cell components
US20050131383A1 (en) 2003-12-16 2005-06-16 How-Lun Chen Method for implanting flexible injection port
CA2490164C (en) 2003-12-17 2012-08-14 Ethicon Endo-Surgery, Inc. Mechanically adjustable gastric band
US8124120B2 (en) 2003-12-22 2012-02-28 Anika Therapeutics, Inc. Crosslinked hyaluronic acid compositions for tissue augmentation
WO2005066215A1 (en) 2003-12-30 2005-07-21 Genzyme Corporation Cohesive gels form cross-linked hyaluronan and/or hylan, their preparation and use
EP2399528B1 (en) 2004-01-23 2013-01-09 Allergan, Inc. Releasably-securable one-piece adjustable gastric band
US20050171568A1 (en) 2004-01-30 2005-08-04 Niall Duffy Catheter and guidewire exchange system with improved catheter design
US20050177111A1 (en) 2004-02-06 2005-08-11 Shaul Ozeri Miniature infusion pump
US7311716B2 (en) 2004-02-20 2007-12-25 Ethicon Endo-Surgery, Inc. Surgically implantable adjustable band having a flat profile when implanted
US7594885B2 (en) 2004-02-20 2009-09-29 Ethicon Endo-Surgery, Inc. Method for implanting an adjustable band
US7931693B2 (en) 2004-02-26 2011-04-26 Endosphere, Inc. Method and apparatus for reducing obesity
WO2005084592A2 (en) 2004-02-27 2005-09-15 Satiety, Inc. Methods and devices for reducing hollow organ volume
WO2005087147A1 (en) 2004-03-08 2005-09-22 Endoart S.A. Closure system for tubular organs
US8343031B2 (en) 2004-03-23 2013-01-01 Michael Gertner Obesity treatment systems
US7946976B2 (en) 2004-03-23 2011-05-24 Michael Gertner Methods and devices for the surgical creation of satiety and biofeedback pathways
US7712470B2 (en) 2005-03-19 2010-05-11 Michael Gertner Devices with integral magnets and uses thereof
US20060195139A1 (en) 2004-03-23 2006-08-31 Michael Gertner Extragastric devices and methods for gastroplasty
US20060264699A1 (en) 2004-10-27 2006-11-23 Michael Gertner Extragastric minimally invasive methods and devices to treat obesity
US7841978B2 (en) 2004-03-23 2010-11-30 Michael Gertner Methods and devices for to treatment of obesity
US8001976B2 (en) 2004-03-23 2011-08-23 Michael Gertner Management systems for the surgically treated obese patient
US20060142790A1 (en) 2004-03-23 2006-06-29 Michael Gertner Methods and devices to facilitate connections between body lumens
EP1901664A2 (en) 2005-05-10 2008-03-26 GERTNER, Michael Obesity treatment systems
US20080147002A1 (en) 2004-03-23 2008-06-19 Michael Eric Gertner Obesity treatment systems
US20070233170A1 (en) 2004-03-23 2007-10-04 Michael Gertner Extragastric Balloon
US20050228415A1 (en) 2004-03-23 2005-10-13 Michael Gertner Methods and devices for percutaneous, non-laparoscopic treatment of obesity
US20080300618A1 (en) 2004-03-23 2008-12-04 Michael Eric Gertner Obesity treatment systems
WO2006049725A3 (en) 2004-03-23 2007-06-14 Minimus Surgical Systems Surgical systems and devices to enhance gastric restriction therapies
EP1750627A2 (en) 2004-03-26 2007-02-14 Satiety, Inc. Systems and methods for treating obesity
US20050226936A1 (en) 2004-04-08 2005-10-13 Q-Med Ab Method of soft tissue augmentation
US20050240155A1 (en) 2004-04-27 2005-10-27 Conlon Sean P Surgically implantable injection port having a centered catheter connection tube
US20050240156A1 (en) 2004-04-27 2005-10-27 Conlon Sean P Method of implanting a fluid injection port
US7484940B2 (en) 2004-04-28 2009-02-03 Kinetic Ceramics, Inc. Piezoelectric fluid pump
ES2609105T3 (en) 2004-05-20 2017-04-18 Mentor Worldwide Llc Method BROOCHES covalent hyaluronic acid and chitosan
EP1750769B1 (en) 2004-05-20 2013-01-23 Mentor Worldwide LLC Methods for making injectable polymer hydrogels
US7390294B2 (en) 2004-05-28 2008-06-24 Ethicon Endo-Surgery, Inc. Piezo electrically driven bellows infuser for hydraulically controlling an adjustable gastric band
US7351240B2 (en) 2004-05-28 2008-04-01 Ethicon Endo—Srugery, Inc. Thermodynamically driven reversible infuser pump for use as a remotely controlled gastric band
US7374565B2 (en) 2004-05-28 2008-05-20 Ethicon Endo-Surgery, Inc. Bi-directional infuser pump with volume braking for hydraulically controlling an adjustable gastric band
US20050277899A1 (en) 2004-06-01 2005-12-15 Conlon Sean P Method of implanting a fluid injection port
US7351198B2 (en) 2004-06-02 2008-04-01 Ethicon Endo-Surgery, Inc. Implantable adjustable sphincter system
US7147205B1 (en) * 2004-06-16 2006-12-12 Sandia Corporation Low energy high pressure miniature screw valve
US7599744B2 (en) 2004-06-24 2009-10-06 Ethicon Endo-Surgery, Inc. Transcutaneous energy transfer primary coil with a high aspect ferrite core
US20050288739A1 (en) 2004-06-24 2005-12-29 Ethicon, Inc. Medical implant having closed loop transcutaneous energy transfer (TET) power transfer regulation circuitry
US20050288740A1 (en) 2004-06-24 2005-12-29 Ethicon Endo-Surgery, Inc. Low frequency transcutaneous telemetry to implanted medical device
US7599743B2 (en) 2004-06-24 2009-10-06 Ethicon Endo-Surgery, Inc. Low frequency transcutaneous energy transfer to implanted medical device
KR100592468B1 (en) 2004-09-03 2006-06-28 김종욱 Portable infusion pump
US7776061B2 (en) 2004-09-28 2010-08-17 Garner Dean L Fluid adjustable band
EP1799119A4 (en) 2004-09-30 2010-11-17 Duocure Inc Device and method for treating weight disorders
US20070078476A1 (en) 2004-10-12 2007-04-05 Hull Wendell C Sr Overweight control apparatuses for insertion into the stomach
US7507221B2 (en) 2004-10-13 2009-03-24 Mallinckrodt Inc. Powerhead of a power injection system
ES2582334T3 (en) 2004-10-15 2016-09-12 Bfkw, Llc bariatric device
US7366571B2 (en) 2004-12-10 2008-04-29 Cyberonics, Inc. Neurostimulator with activation based on changes in body temperature
US7585280B2 (en) 2004-12-29 2009-09-08 Codman & Shurtleff, Inc. System and method for measuring the pressure of a fluid system within a patient
US7601162B2 (en) 2005-01-14 2009-10-13 Ethicon Endo-Surgery, Inc. Actuator for an implantable band
US7771382B2 (en) 2005-01-19 2010-08-10 Gi Dynamics, Inc. Resistive anti-obesity devices
US8109981B2 (en) 2005-01-25 2012-02-07 Valam Corporation Optical therapies and devices
US20060173238A1 (en) 2005-01-31 2006-08-03 Starkebaum Warren L Dynamically controlled gastric occlusion device
US20060173424A1 (en) 2005-02-01 2006-08-03 Conlon Sean P Surgically implantable injection port having an absorbable fastener
US7771439B2 (en) 2005-02-04 2010-08-10 Symmetry Medical New Bedford Inc Gastric band insertion instrument
US20060178555A1 (en) 2005-02-10 2006-08-10 Mauro Bortolotti Medical antireflux device based on magnets action
JP2008537898A (en) 2005-02-11 2008-10-02 ミカーディア コーポレーション The method of treating obesity using dynamically adjustable gastric implants and this
US8016744B2 (en) 2005-02-24 2011-09-13 Ethicon Endo-Surgery, Inc. External pressure-based gastric band adjustment system and method
US7775966B2 (en) 2005-02-24 2010-08-17 Ethicon Endo-Surgery, Inc. Non-invasive pressure measurement in a fluid adjustable restrictive device
US7699770B2 (en) 2005-02-24 2010-04-20 Ethicon Endo-Surgery, Inc. Device for non-invasive measurement of fluid pressure in an adjustable restriction device
US8152710B2 (en) 2006-04-06 2012-04-10 Ethicon Endo-Surgery, Inc. Physiological parameter analysis for an implantable restriction device and a data logger
US7909754B2 (en) 2005-02-24 2011-03-22 Ethicon Endo-Surgery, Inc. Non-invasive measurement of fluid pressure in an adjustable gastric band
US20080249806A1 (en) 2006-04-06 2008-10-09 Ethicon Endo-Surgery, Inc Data Analysis for an Implantable Restriction Device and a Data Logger
US8870742B2 (en) 2006-04-06 2014-10-28 Ethicon Endo-Surgery, Inc. GUI for an implantable restriction device and a data logger
US8066629B2 (en) 2005-02-24 2011-11-29 Ethicon Endo-Surgery, Inc. Apparatus for adjustment and sensing of gastric band pressure
US20080250341A1 (en) 2006-04-06 2008-10-09 Ethicon Endo-Surgery, Inc. Gui With Trend Analysis for an Implantable Restriction Device and a Data Logger
US7775215B2 (en) 2005-02-24 2010-08-17 Ethicon Endo-Surgery, Inc. System and method for determining implanted device positioning and obtaining pressure data
WO2007145638A1 (en) 2006-06-14 2007-12-21 Michael Gertner Medical devices with integral magnets and uses thereof
US20060264762A1 (en) 2005-03-28 2006-11-23 Ric Investments, Llc. PC-based physiologic monitor and system for resolving apnea episodes during sedation
WO2006107901A1 (en) 2005-04-04 2006-10-12 Micardia Corporation Dynamic reinforcement of the lower esophageal sphincter
US8251888B2 (en) 2005-04-13 2012-08-28 Mitchell Steven Roslin Artificial gastric valve
US7610093B2 (en) 2005-04-28 2009-10-27 Medtronic, Inc. Implantable optical pressure sensor for sensing urinary sphincter pressure
US7899540B2 (en) 2005-04-29 2011-03-01 Cyberonics, Inc. Noninvasively adjustable gastric band
US7310557B2 (en) 2005-04-29 2007-12-18 Maschino Steven E Identification of electrodes for nerve stimulation in the treatment of eating disorders
US7727141B2 (en) 2005-05-04 2010-06-01 Ethicon Endo-Surgery, Inc. Magnetic resonance imaging (MRI) safe remotely adjustable artifical sphincter
US20060257488A1 (en) 2005-05-10 2006-11-16 Cytophil, Inc. Injectable hydrogels and methods of making and using same
US7918844B2 (en) 2005-06-24 2011-04-05 Ethicon Endo-Surgery, Inc. Applier for implantable medical device
US7021147B1 (en) 2005-07-11 2006-04-04 General Electric Company Sensor package and method
US7364542B2 (en) 2005-07-15 2008-04-29 Ethicon Endo-Surgery, Inc. Gastric band suture tab extender
US7618365B2 (en) 2005-07-15 2009-11-17 Ethicon Endo-Surgery, Inc. Method of implating a medical device using a suture tab extender
US8298133B2 (en) 2005-07-15 2012-10-30 Ethicon Endo-Surgery, Inc. Gastric band composed of different hardness materials
US7367937B2 (en) 2005-07-15 2008-05-06 Ethicon Endo-Surgey, Inc. Gastric band
US7353747B2 (en) 2005-07-28 2008-04-08 Ethicon Endo-Surgery, Inc. Electroactive polymer-based pump
US20080208240A1 (en) 2005-08-11 2008-08-28 Stimplant Ltd. Implantable Device For Obesity Prevention
JP5054904B2 (en) * 2005-08-30 2012-10-24 株式会社フジキン Direct touch type metal diaphragm valve
DE602006012694D1 (en) 2005-09-06 2010-04-15 Glaxosmithkline Llc Benzimidazolthiophenverbindungen as plk-modulators
JP2009510168A (en) 2005-10-03 2009-03-12 マーク エー. ピンスカイ Compositions and methods for improved skincare
EP1779821A1 (en) 2005-10-26 2007-05-02 Etervind AB Adjustable gastric band
US7246734B2 (en) 2005-12-05 2007-07-24 Ethicon Endo-Surgery, Inc. Rotary hydraulic pump actuated multi-stroke surgical instrument
US8622888B2 (en) 2005-12-22 2014-01-07 Wolfgang Lechner System for controlling a controllable stomach band
US8043206B2 (en) 2006-01-04 2011-10-25 Allergan, Inc. Self-regulating gastric band with pressure data processing
US7798954B2 (en) 2006-01-04 2010-09-21 Allergan, Inc. Hydraulic gastric band with collapsible reservoir
CN101495061A (en) 2006-01-04 2009-07-29 阿勒根公司 Self-interacting stomach belt
US20070265646A1 (en) 2006-01-17 2007-11-15 Ellipse Technologies, Inc. Dynamically adjustable gastric implants
US7762999B2 (en) 2006-02-01 2010-07-27 Ethicon Endo-Surgery, Inc. Injection port
US20070185373A1 (en) 2006-02-03 2007-08-09 Ethicon Endo-Surgery, Inc. Gastric band introduction device
US20070191717A1 (en) 2006-02-13 2007-08-16 Drexel University Catheter based implanted wireless pressure sensor
WO2007104356A1 (en) 2006-03-13 2007-09-20 Rudolf Steffen Adaptive device and adaptive method for adapting the stomach opening of a patient
US7794386B2 (en) 2006-03-15 2010-09-14 Allergan, Inc. Methods for facilitating weight loss
US20070243227A1 (en) 2006-04-14 2007-10-18 Michael Gertner Coatings for surgical staplers
US20070255335A1 (en) 2006-04-28 2007-11-01 Medtronic, Inc. Controller for gastric constriction device with selectable electrode configurations
US20070255336A1 (en) 2006-04-28 2007-11-01 Medtronic, Inc. Gastric constriction device with selectable electrode combinations
US7763039B2 (en) 2006-06-09 2010-07-27 Ethicon Endo-Surgery, Inc. Articulating blunt dissector/gastric band application device
US20070298005A1 (en) 2006-06-22 2007-12-27 Marie-Josee Thibault Injectable composition for treatment of skin defects or deformations
EP2053996B1 (en) 2006-08-21 2013-10-02 A.M.I. Agency for Medical Innovations GmbH Device for treating obesity
US20080319435A1 (en) 2006-10-12 2008-12-25 Boston Scientific Scimed, Inc. Shape-changing tissue constrictor and methods of use
US8246533B2 (en) 2006-10-20 2012-08-21 Ellipse Technologies, Inc. Implant system with resonant-driven actuator
EP2081638A4 (en) 2006-11-03 2013-06-12 Gep Technology Inc Apparatus and methods for minimally invasive obesity treatment
US20080161875A1 (en) 2006-11-21 2008-07-03 Stone Robert T Gastric restriction method and system for treatment of eating disorders
US20080166028A1 (en) 2007-01-10 2008-07-10 Turek Joseph J Pressure actuated biometric sensor
US20080172072A1 (en) 2007-01-11 2008-07-17 Ellipse Technologies, Inc. Internal sensors for use with gastric restriction devices
DE102007008901B4 (en) * 2007-02-23 2008-10-16 Compact Dynamics Gmbh Fluid injection valve
US8083665B2 (en) 2007-03-06 2011-12-27 Ethicon Endo-Surgery, Inc. Pressure sensors for gastric band and adjacent tissue
US8920307B2 (en) 2007-03-06 2014-12-30 Ethicon Endo-Surgery, Inc. Gastric band system with esophageal sensor
WO2008121409A1 (en) 2007-03-29 2008-10-09 Jaime Vargas Intragastric implant devices
US8226602B2 (en) 2007-03-30 2012-07-24 Reshape Medical, Inc. Intragastric balloon system and therapeutic processes and products
EP2135630B1 (en) 2007-04-09 2014-05-07 Obshchestvo S Ogranichennoy Otvetstvennostiu "Nauchno Proizvodstvennaya Firma 'Pozitom-Pro'" Automated strontium-rubidium infusion system
US20080255425A1 (en) 2007-04-13 2008-10-16 Ethicon Endo-Surgery, Inc. Nanoparticle treated medical devices
US20080275295A1 (en) 2007-05-01 2008-11-06 Michael Gertner Methods of using pericardial inserts
US20080287976A1 (en) 2007-05-14 2008-11-20 Weaner Lauren S Gastric band with engagement member
US8317676B2 (en) 2007-05-14 2012-11-27 Ethicon Endo-Surgery, Inc. Gastric band with contrasting supply tube
US8485964B2 (en) 2007-05-15 2013-07-16 Ethicon Endo-Surgery, Inc. Gastric band with supply tube check valve
US20080287776A1 (en) 2007-05-16 2008-11-20 Yaron Ephrath Gastric band with position sensing
US20080306443A1 (en) 2007-06-06 2008-12-11 Mallinckrodt Inc. Medical Fluid Injector Having Wireless Pressure Monitoring Feature
WO2009023247A1 (en) 2007-08-16 2009-02-19 East Carolina University Smart injection syringe systems providing real-time user feedback of correct needle position
US20090250021A1 (en) * 2007-10-02 2009-10-08 Artificial Muscle, Inc. Fluid control systems employing compliant electroactive materials
FR2921822A1 (en) 2007-10-05 2009-04-10 Dominique Branche Gastric band for treating obesity, has inflatable element defining passage for esophagus at interior of loop, and flexible tab integrated with support, and radially withdrawn towards interior of passage, where color of band is light blue
US9293062B2 (en) 2007-10-15 2016-03-22 Isaac Tavori Apparatus and methods for corrective guidance of eating behavior after weight loss surgery
FR2922097B1 (en) 2007-10-16 2010-09-24 Cie Euro Etude Rech Paroscopie Gastric band dual balloon
US8187163B2 (en) 2007-12-10 2012-05-29 Ethicon Endo-Surgery, Inc. Methods for implanting a gastric restriction device
US8100870B2 (en) 2007-12-14 2012-01-24 Ethicon Endo-Surgery, Inc. Adjustable height gastric restriction devices and methods
US20090157113A1 (en) 2007-12-18 2009-06-18 Ethicon Endo-Surgery, Inc. Wearable elements for implantable restriction systems
US8377079B2 (en) 2007-12-27 2013-02-19 Ethicon Endo-Surgery, Inc. Constant force mechanisms for regulating restriction devices
US8142452B2 (en) 2007-12-27 2012-03-27 Ethicon Endo-Surgery, Inc. Controlling pressure in adjustable restriction devices
US20090171379A1 (en) 2007-12-27 2009-07-02 Ethicon Endo-Surgery, Inc. Fluid logic for regulating restriction devices
US20090187202A1 (en) 2008-01-17 2009-07-23 Ortiz Mark S Optimizing the operation of a restriction system
JP5602360B2 (en) 2008-01-25 2014-10-08 キヤノン株式会社 How understand the ejection performance of the medicine ejection device, and the device
US8192350B2 (en) 2008-01-28 2012-06-05 Ethicon Endo-Surgery, Inc. Methods and devices for measuring impedance in a gastric restriction system
US8337389B2 (en) 2008-01-28 2012-12-25 Ethicon Endo-Surgery, Inc. Methods and devices for diagnosing performance of a gastric restriction system
US8591395B2 (en) 2008-01-28 2013-11-26 Ethicon Endo-Surgery, Inc. Gastric restriction device data handling devices and methods
US20090192541A1 (en) 2008-01-28 2009-07-30 Ethicon Endo-Surgery, Inc. Methods and devices for predicting performance of a gastric restriction system
US20090192534A1 (en) 2008-01-29 2009-07-30 Ethicon Endo-Surgery, Inc. Sensor trigger
WO2009097482A1 (en) 2008-01-30 2009-08-06 Medical Components, Inc. Gastric inflation band with integrated infusion catheter
US7844342B2 (en) 2008-02-07 2010-11-30 Ethicon Endo-Surgery, Inc. Powering implantable restriction systems using light
US8221439B2 (en) 2008-02-07 2012-07-17 Ethicon Endo-Surgery, Inc. Powering implantable restriction systems using kinetic motion
US20090204179A1 (en) 2008-02-07 2009-08-13 Ethicon Endo-Surgery, Inc. Powering implantable restriction systems using temperature
US8114345B2 (en) 2008-02-08 2012-02-14 Ethicon Endo-Surgery, Inc. System and method of sterilizing an implantable medical device
US8057492B2 (en) 2008-02-12 2011-11-15 Ethicon Endo-Surgery, Inc. Automatically adjusting band system with MEMS pump
US8591532B2 (en) 2008-02-12 2013-11-26 Ethicon Endo-Sugery, Inc. Automatically adjusting band system
US20090209995A1 (en) 2008-02-14 2009-08-20 Byrum Randal T Implantable adjustable sphincter system
US20090220176A1 (en) 2008-02-15 2009-09-03 Fusco Michael T Self-sealing container
US8034065B2 (en) 2008-02-26 2011-10-11 Ethicon Endo-Surgery, Inc. Controlling pressure in adjustable restriction devices
US20090222028A1 (en) 2008-02-29 2009-09-03 Ethicon Endo-Surgery, Inc. Methods and devices for fixing antenna orientation in a restriction system
US8233995B2 (en) 2008-03-06 2012-07-31 Ethicon Endo-Surgery, Inc. System and method of aligning an implantable antenna
US20090228063A1 (en) 2008-03-06 2009-09-10 Ethicon Endo-Surgery, Inc. System and method of communicating with an implantable antenna
US7856887B2 (en) 2008-03-27 2010-12-28 Endress + Hauser Gmbh + Co. Kg Pressure management arrangement
FR2929842B1 (en) 2008-04-14 2011-09-30 Cie Euro Etude Rech Paroscopie Gastric band with overhead pockets
US20090270904A1 (en) * 2008-04-23 2009-10-29 Birk Janel A Remotely Adjustable Gastric Banding System
EP2320836B1 (en) 2008-06-11 2015-08-12 Apollo Endosurgery, Inc. Implantable pump system
US20100305397A1 (en) 2008-10-06 2010-12-02 Allergan Medical Sarl Hydraulic-mechanical gastric band
EP2362762A1 (en) 2008-10-06 2011-09-07 Allergan Medical Sàrl Mechanical gastric band with cushions
US9364362B2 (en) 2008-10-21 2016-06-14 General Electric Company Implantable device system
US20100185049A1 (en) 2008-10-22 2010-07-22 Allergan, Inc. Dome and screw valves for remotely adjustable gastric banding systems
WO2010048280A1 (en) 2008-10-22 2010-04-29 Allergan, Inc. Electrically activated valve for implantable fluid handling system
EP2191796A1 (en) 2008-11-28 2010-06-02 Debiotech S.A. Artificial sphincter assembly
US20100191265A1 (en) 2009-01-29 2010-07-29 Cavu Medical, Inc. Assembly and method for automatically controlling pressure for a gastric band
US20100191271A1 (en) 2009-01-29 2010-07-29 Lilip Lau Assembly and method for automatically controlling pressure for a gastric band
US20100280310A1 (en) 2009-05-01 2010-11-04 Allergan, Inc. Laparoscopic Gastric Band With Active Agents
US20110201874A1 (en) 2010-02-12 2011-08-18 Allergan, Inc. Remotely adjustable gastric banding system

Patent Citations (105)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1174814A (en) * 1915-09-17 1916-03-07 Manville E J Machine Co Automatic threader.
US2339138A (en) * 1942-09-18 1944-01-11 Central Equipment Co Clamp
US2438231A (en) * 1946-01-18 1948-03-23 Schultz Closure for fountain pens and the like
US4133315A (en) * 1976-12-27 1979-01-09 Berman Edward J Method and apparatus for reducing obesity
US4370982A (en) * 1980-09-10 1983-02-01 Medrad, Inc. Method and apparatus for injecting and for controlling the pressure of fluid being injected into a catheter
US4424208A (en) * 1982-01-11 1984-01-03 Collagen Corporation Collagen implant material and method for augmenting soft tissue
US4492004A (en) * 1982-12-03 1985-01-08 Hans Oetiker Earless clamp structure
US4803075A (en) * 1986-06-25 1989-02-07 Collagen Corporation Injectable implant composition having improved intrudability
US4989756A (en) * 1986-10-14 1991-02-05 Kabushiki Kaisha Shinkawa Dispensing apparatus
US5091171B2 (en) * 1986-12-23 1997-07-15 Tristrata Inc Amphoteric compositions and polymeric forms of alpha hydroxyacids and their therapeutic use
US5091171B1 (en) * 1986-12-23 1995-09-26 Ruey J Yu Amphoteric compositions and polymeric forms of alpha hydroxyacids, and their therapeutic use
US5091171A (en) * 1986-12-23 1992-02-25 Yu Ruey J Amphoteric compositions and polymeric forms of alpha hydroxyacids, and their therapeutic use
US4896787A (en) * 1987-08-14 1990-01-30 Genus International Article with resilient hinges becoming rigid under tension
US5084061A (en) * 1987-09-25 1992-01-28 Gau Fred C Intragastric balloon with improved valve locating means
US6013679C1 (en) * 1989-08-01 2001-06-19 Anika Res Inc Water-insoluble derivatives of hyaluronic acid and their methods of preparation and use
US6013679A (en) * 1989-08-01 2000-01-11 Anika Research, Inc. Water-insoluble derivatives of hyaluronic acid and their methods of preparation and use
US5886042A (en) * 1989-08-15 1999-03-23 Tristrata Technology, Inc. Amphoteric compostion and polymeric forms of alpha hydroxyacids, and their therapeutic use
US5089019A (en) * 1989-12-06 1992-02-18 Medtronic, Inc. Muscle work output monitor by intramuscular temperature variation measurement
US5399351A (en) * 1990-07-09 1995-03-21 Biomatrix, Inc. Biocompatible viscoelastic gel slurries, their preparation and use
US5277333A (en) * 1990-07-10 1994-01-11 Musashi Engineering, Inc. Apparatus for metering and discharging a liquid
US5188609A (en) * 1991-07-08 1993-02-23 Bryman Medical Inc. Swivel clip medical tube holder
US5391156A (en) * 1992-06-30 1995-02-21 Ethicon, Inc. Flexible encoscopic surgical port
US5383858B1 (en) * 1992-08-17 1996-10-29 Medrad Inc Front-loading medical injector and syringe for use therewith
US5383858A (en) * 1992-08-17 1995-01-24 Medrad, Inc. Front-loading medical injector and syringe for use therewith
US20030060754A1 (en) * 1992-08-17 2003-03-27 Reilly David M. System and method for providing information from a syringe to an injector
USRE36176E (en) * 1993-02-18 1999-03-30 Kuzmak; Lubomyr I. Laparoscopic adjustable gastric banding device and method for implantation and removal thereof
US5601604A (en) * 1993-05-27 1997-02-11 Inamed Development Co. Universal gastric band
US5496312A (en) * 1993-10-07 1996-03-05 Valleylab Inc. Impedance and temperature generator control
US5733257A (en) * 1993-10-11 1998-03-31 Gambro Ab Method for calibrating a pump segment used in a peristaltic pump and a medical machine adapted for carrying out the method
US5704893A (en) * 1994-07-11 1998-01-06 Dacomed Corportion Vessel occlusive apparatus and method
US5496313A (en) * 1994-09-20 1996-03-05 Conmed Corporation System for detecting penetration of medical instruments
US6171321B1 (en) * 1995-02-24 2001-01-09 Heartport, Inc. Devices and methods for performing a vascular anastomosis
US6010511A (en) * 1995-05-04 2000-01-04 Murphy; Richard Lesion diameter measurement catheter and method
US5607418A (en) * 1995-08-22 1997-03-04 Illinois Institute Of Technology Implantable drug delivery apparatus
US20030055311A1 (en) * 1996-02-15 2003-03-20 Neukermans Armand P. Biocompatible transducers
US5713911A (en) * 1996-10-03 1998-02-03 United States Surgical Corporation Surgical clip
US6024340A (en) * 1996-12-04 2000-02-15 Active Control Experts, Inc. Valve assembly
US6179569B1 (en) * 1997-01-10 2001-01-30 Japan Servo Co., Ltd. Liquid transportation apparatus
US6042345A (en) * 1997-04-15 2000-03-28 Face International Corporation Piezoelectrically actuated fluid pumps
US5861014A (en) * 1997-04-30 1999-01-19 Medtronic, Inc. Method and apparatus for sensing a stimulating gastrointestinal tract on-demand
US6193734B1 (en) * 1998-01-23 2001-02-27 Heartport, Inc. System for performing vascular anastomoses
US6203523B1 (en) * 1998-02-02 2001-03-20 Medtronic Inc Implantable drug infusion device having a flow regulator
US6024704A (en) * 1998-04-30 2000-02-15 Medtronic, Inc Implantable medical device for sensing absolute blood pressure and barometric pressure
US20030019498A1 (en) * 1998-08-13 2003-01-30 Obtech Medical Ag. Non-injection port food intake restriction device
US20020038105A1 (en) * 1998-09-23 2002-03-28 Mayo Foundation For Medical Education And Research Automatic manifold for vascular catheter
US6676674B1 (en) * 1999-03-17 2004-01-13 Moshe Dudai Gastric band
US20030045775A1 (en) * 1999-08-12 2003-03-06 Obtech Medical Ag. Hydraulic anal incontinence treatment
US6517556B1 (en) * 1999-10-28 2003-02-11 Niti Alloys Technologies Ltd. Shape memory alloy clip and method of use thereof
US6691047B1 (en) * 2000-03-16 2004-02-10 Aksys, Ltd. Calibration of pumps, such as blood pumps of dialysis machine
US20040049209A1 (en) * 2000-05-12 2004-03-11 Salomon Benchetrit Adjustable gastroplastry ring comprising a grip tab
US6685668B1 (en) * 2000-07-31 2004-02-03 Abbott Laboratories Closed-loop IV fluid flow control
US6527701B1 (en) * 2000-09-29 2003-03-04 Precision Medical Devices, Inc. Body fluid flow control device
US6871090B1 (en) * 2000-10-13 2005-03-22 Advanced Bionics Corporation Switching regulator for implantable spinal cord stimulation
US6681135B1 (en) * 2000-10-30 2004-01-20 Medtronic, Inc. System and method for employing temperature measurements to control the operation of an implantable medical device
US20040044332A1 (en) * 2000-11-03 2004-03-04 Nikolaus Stergiopulos Implantable medical device for delivering a liquid
US20040059393A1 (en) * 2001-01-05 2004-03-25 Shai Policker Regulation of eating habits
US20030014003A1 (en) * 2001-06-20 2003-01-16 The Regents Of The University Of California Hemodialysis system and method
US6511490B2 (en) * 2001-06-22 2003-01-28 Antoine Jean Henri Robert Gastric banding device and method
US7314636B2 (en) * 2001-06-29 2008-01-01 Medgraft Microtech, Inc. Biodegradable injectable implants containing glycolic acid
US20030009123A1 (en) * 2001-07-07 2003-01-09 Nxstage Medical, Inc. Method and aparatus for leak detection in a fluid line
US7017883B2 (en) * 2001-08-14 2006-03-28 Continential Teves Ag & Co. Ohg Piezoelectrically actuated fluid valve
US20030045902A1 (en) * 2001-08-28 2003-03-06 Weadock Kevin S Composite staple for completing an anastomosis
US7195610B1 (en) * 2001-09-17 2007-03-27 Cardinal Health 303, Inc. Pneumatic syringe driver
US20030060873A1 (en) * 2001-09-19 2003-03-27 Nanomedical Technologies, Inc. Metallic structures incorporating bioactive materials and methods for creating the same
US7017582B2 (en) * 2002-02-04 2006-03-28 Restore Medical Inc. Stiffening pharyngeal wall treatment
US7314443B2 (en) * 2002-03-08 2008-01-01 Allergan Medical S.A. Implantable device
US20040034479A1 (en) * 2002-08-07 2004-02-19 Akihiro Shimase Sample dispensing apparatus and automatic analyzer using the same
US7172607B2 (en) * 2002-08-16 2007-02-06 Ami Agency For Medical Innovations Gmbh Device for generating an artificial constriction in the gastrointestinal tract
US20080027469A1 (en) * 2002-09-04 2008-01-31 Endoart Sa Surgical ring featuring a reversible diameter remote control system
US20050038484A1 (en) * 2003-02-03 2005-02-17 Enteromedics, Inc. Controlled vagal blockage therapy
US7314598B2 (en) * 2003-02-14 2008-01-01 Stack System Co., Ltd. Dispenser and dispensing device
US20050038498A1 (en) * 2003-04-17 2005-02-17 Nanosys, Inc. Medical device applications of nanostructured surfaces
US20050002984A1 (en) * 2003-06-27 2005-01-06 Byrum Randal T. Implantable band with attachment mechanism having dissimilar material properties
US20050055039A1 (en) * 2003-07-28 2005-03-10 Polymorfix, Inc. Devices and methods for pyloric anchoring
US20050070937A1 (en) * 2003-09-30 2005-03-31 Jambor Kristin L. Segmented gastric band
US20050070934A1 (en) * 2003-09-30 2005-03-31 Tanaka Don A. Anastomosis wire ring device
US20050109973A1 (en) * 2003-11-21 2005-05-26 Glime William H. Valve diaphragm
US7177693B2 (en) * 2004-01-07 2007-02-13 Medtronic, Inc. Gastric stimulation for altered perception to treat obesity
US20080071306A1 (en) * 2004-03-23 2008-03-20 Michael Gertner Extragastric Balloon With Attachment Tabs
US20070027358A1 (en) * 2004-03-23 2007-02-01 Michael Gertner Devices and methods to treat a patient
US20080015501A1 (en) * 2004-03-23 2008-01-17 Michael Gertner Abdominal Wall Balloon To Treat Obesity
US20060009697A1 (en) * 2004-04-07 2006-01-12 Triage Wireless, Inc. Wireless, internet-based system for measuring vital signs from a plurality of patients in a hospital or medical clinic
US7481763B2 (en) * 2004-05-28 2009-01-27 Ethicon Endo-Surgery, Inc. Metal bellows position feedback for hydraulic control of an adjustable gastric band
US7191007B2 (en) * 2004-06-24 2007-03-13 Ethicon Endo-Surgery, Inc Spatially decoupled twin secondary coils for optimizing transcutaneous energy transfer (TET) power transfer characteristics
US20060015138A1 (en) * 2004-07-19 2006-01-19 Michael Gertner Emboli diverting devices created by microfabricated means
US20060020298A1 (en) * 2004-07-20 2006-01-26 Camilleri Michael L Systems and methods for curbing appetite
US20060041183A1 (en) * 2004-08-20 2006-02-23 Massen Richard J Electromechanical machine-based artificial muscles, bio-valves and related devices
US7879068B2 (en) * 2005-01-14 2011-02-01 Ethicon Endo-Surgery, Inc. Feedback sensing for a mechanical restrictive device
US7658196B2 (en) * 2005-02-24 2010-02-09 Ethicon Endo-Surgery, Inc. System and method for determining implanted device orientation
US20080015406A1 (en) * 2005-02-24 2008-01-17 Dlugos Daniel F External Mechanical Pressure Sensor for Gastric Band Pressure Measurements
US20090054914A1 (en) * 2005-04-11 2009-02-26 Wolfgang Lechner Controllable Gastric Band
US20070001447A1 (en) * 2005-05-20 2007-01-04 Fennington George J Jr Gauge tee device
US20080009680A1 (en) * 2005-06-24 2008-01-10 Hassler William L Jr Remote monitoring and adjustment of a food intake restriction device
US20070000843A1 (en) * 2005-06-29 2007-01-04 Christopher Kimball Apparatus for measuring a set of electrical characteristics in a plasma
US20070016262A1 (en) * 2005-07-13 2007-01-18 Betastim, Ltd. Gi and pancreatic device for treating obesity and diabetes
US20070015954A1 (en) * 2005-07-15 2007-01-18 Dlugos Daniel F Gastric band with mating end profiles
US20070016231A1 (en) * 2005-07-15 2007-01-18 Jambor Kristin L Precurved gastric band
US20070015956A1 (en) * 2005-07-15 2007-01-18 Crawford Norman D Latching device for gastric band
US20070015955A1 (en) * 2005-07-15 2007-01-18 Mark Tsonton Accordion-like gastric band
US20070027356A1 (en) * 2005-07-28 2007-02-01 Ethicon Endo-Surgery, Inc. Electroactive polymer actuated gastric band
US20070044655A1 (en) * 2005-08-23 2007-03-01 Fish Elson B Removable end plug
US20070219597A1 (en) * 2006-02-09 2007-09-20 Dean Kamen Adhesive and peripheral systems and methods for medical devices
US20080027269A1 (en) * 2006-04-04 2008-01-31 Michael Gertner Methods of using pericardial inserts
US7862502B2 (en) * 2006-10-20 2011-01-04 Ellipse Technologies, Inc. Method and apparatus for adjusting a gastrointestinal restriction device
US20100010291A1 (en) * 2008-07-14 2010-01-14 Allergan, Inc. Implantable pump system with calibration

Cited By (49)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8187164B2 (en) * 2002-04-26 2012-05-29 Torax Medical, Inc. Methods and apparatus for treating body tissue sphincters and the like
US8845513B2 (en) 2002-08-13 2014-09-30 Apollo Endosurgery, Inc. Remotely adjustable gastric banding device
US8382780B2 (en) 2002-08-28 2013-02-26 Allergan, Inc. Fatigue-resistant gastric banding device
US8900117B2 (en) 2004-01-23 2014-12-02 Apollo Endosurgery, Inc. Releasably-securable one-piece adjustable gastric band
US8377081B2 (en) 2004-03-08 2013-02-19 Allergan, Inc. Closure system for tubular organs
US8236023B2 (en) 2004-03-18 2012-08-07 Allergan, Inc. Apparatus and method for volume adjustment of intragastric balloons
US8251888B2 (en) 2005-04-13 2012-08-28 Mitchell Steven Roslin Artificial gastric valve
US8623042B2 (en) 2005-04-13 2014-01-07 Mitchell Roslin Artificial gastric valve
US8308630B2 (en) 2006-01-04 2012-11-13 Allergan, Inc. Hydraulic gastric band with collapsible reservoir
US8323180B2 (en) 2006-01-04 2012-12-04 Allergan, Inc. Hydraulic gastric band with collapsible reservoir
US8905915B2 (en) 2006-01-04 2014-12-09 Apollo Endosurgery, Inc. Self-regulating gastric band with pressure data processing
US8292800B2 (en) 2008-06-11 2012-10-23 Allergan, Inc. Implantable pump system
US8317677B2 (en) 2008-10-06 2012-11-27 Allergan, Inc. Mechanical gastric band with cushions
US20110306827A1 (en) * 2010-02-05 2011-12-15 Allergan, Inc. Needle guard to protect access port tubing
US8678993B2 (en) 2010-02-12 2014-03-25 Apollo Endosurgery, Inc. Remotely adjustable gastric banding system
US8758221B2 (en) 2010-02-24 2014-06-24 Apollo Endosurgery, Inc. Source reservoir with potential energy for remotely adjustable gastric banding system
US8764624B2 (en) 2010-02-25 2014-07-01 Apollo Endosurgery, Inc. Inductively powered remotely adjustable gastric banding system
US8840541B2 (en) 2010-02-25 2014-09-23 Apollo Endosurgery, Inc. Pressure sensing gastric banding system
US8939888B2 (en) 2010-04-28 2015-01-27 Apollo Endosurgery, Inc. Method and system for determining the pressure of a fluid in a syringe, an access port, a catheter, and a gastric band
US9044298B2 (en) 2010-04-29 2015-06-02 Apollo Endosurgery, Inc. Self-adjusting gastric band
US9028394B2 (en) 2010-04-29 2015-05-12 Apollo Endosurgery, Inc. Self-adjusting mechanical gastric band
US9295573B2 (en) 2010-04-29 2016-03-29 Apollo Endosurgery, Inc. Self-adjusting gastric band having various compliant components and/or a satiety booster
US9192501B2 (en) 2010-04-30 2015-11-24 Apollo Endosurgery, Inc. Remotely powered remotely adjustable gastric band system
US9226840B2 (en) 2010-06-03 2016-01-05 Apollo Endosurgery, Inc. Magnetically coupled implantable pump system and method
US9987153B2 (en) 2010-06-08 2018-06-05 The Regents Of The University Of Minnesota Vascular elastance
US8517915B2 (en) 2010-06-10 2013-08-27 Allergan, Inc. Remotely adjustable gastric banding system
US8698373B2 (en) 2010-08-18 2014-04-15 Apollo Endosurgery, Inc. Pare piezo power with energy recovery
US9211207B2 (en) 2010-08-18 2015-12-15 Apollo Endosurgery, Inc. Power regulated implant
US9050165B2 (en) 2010-09-07 2015-06-09 Apollo Endosurgery, Inc. Remotely adjustable gastric banding system
US8961393B2 (en) 2010-11-15 2015-02-24 Apollo Endosurgery, Inc. Gastric band devices and drive systems
WO2012071395A1 (en) * 2010-11-22 2012-05-31 Aria Cv, Inc. System and method for reducing pulsatile pressure
CN103260547A (en) * 2010-11-22 2013-08-21 阿里阿Cv公司 System and method for reducing pulsatile pressure
US9017359B2 (en) 2010-11-22 2015-04-28 Aria Cv, Inc. System and method for reducing pulsatile pressure
US9333328B2 (en) 2010-11-22 2016-05-10 Aria Cv, Inc. System and method for reducing pulsatile pressure
US20120157759A1 (en) * 2010-12-16 2012-06-21 Ams Research Corporation Artificial Sphincter System and Method
US9801702B2 (en) * 2010-12-16 2017-10-31 Boston Scientific Scimed, Inc. Artificial sphincter system and method
WO2012110623A1 (en) * 2011-02-17 2012-08-23 Allergan Medical Sàrl Hydraulic gastric band with reversible self-opening mechanism
US20120215061A1 (en) * 2011-02-17 2012-08-23 Allergan, Inc. Hydraulic gastric band with reversible self-opening mechanism
US20130281771A1 (en) * 2011-02-17 2013-10-24 Allergan, Inc. Hydraulic gastric band with reversible self-opening mechanism
US8725435B2 (en) 2011-04-13 2014-05-13 Apollo Endosurgery, Inc. Syringe-based leak detection system
US8876694B2 (en) 2011-12-07 2014-11-04 Apollo Endosurgery, Inc. Tube connector with a guiding tip
US8961394B2 (en) 2011-12-20 2015-02-24 Apollo Endosurgery, Inc. Self-sealing fluid joint for use with a gastric band
US20150240958A1 (en) * 2012-10-22 2015-08-27 President And Fellows Of Harvard College Apparatus, systems, and methods for actuating pressurizable chambers
US9242082B2 (en) 2014-06-19 2016-01-26 Aria Cv, Inc. Systems and methods for treating pulmonary hypertension
US9610391B2 (en) 2014-06-19 2017-04-04 Aria Cv, Inc. Systems comprising an implantable component for treating pulmonary hypertension
US9801989B2 (en) 2014-06-19 2017-10-31 Aria Cv, Inc. Systems and methods for treating pulmonary hypertension
US9039725B1 (en) 2014-06-19 2015-05-26 Aria Cv, Inc. Systems and methods for treating pulmonary hypertension
US8876850B1 (en) 2014-06-19 2014-11-04 Aria Cv, Inc. Systems and methods for treating pulmonary hypertension
WO2016200612A1 (en) * 2015-06-11 2016-12-15 Obalon Therapeutics, Inc. Intragastric device system

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US20130253262A1 (en) 2013-09-26 application
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