US20190038897A1 - Systems and methods for intravascular catheter positioning and/or nerve stimulation - Google Patents
Systems and methods for intravascular catheter positioning and/or nerve stimulation Download PDFInfo
- Publication number
- US20190038897A1 US20190038897A1 US15/666,989 US201715666989A US2019038897A1 US 20190038897 A1 US20190038897 A1 US 20190038897A1 US 201715666989 A US201715666989 A US 201715666989A US 2019038897 A1 US2019038897 A1 US 2019038897A1
- Authority
- US
- United States
- Prior art keywords
- electrodes
- catheter
- ecg signal
- nerve
- distal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3601—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of respiratory organs
-
- A61B5/0422—
-
- A61B5/0452—
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
- A61B5/283—Invasive
- A61B5/287—Holders for multiple electrodes, e.g. electrode catheters for electrophysiological study [EPS]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/48—Other medical applications
- A61B5/4887—Locating particular structures in or on the body
- A61B5/4893—Nerves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/0551—Spinal or peripheral nerve electrodes
Definitions
- This disclosure relates to systems, devices, and methods for one or more of positioning an intravascular nerve stimulation catheter, selecting electrodes for nerve stimulation, or stimulating nerves.
- Nerves and muscles may be stimulated by placing electrodes in, around, or near the nerves and muscles and by activating the electrodes by means of an implanted or external source of energy (e.g., electricity).
- an implanted or external source of energy e.g., electricity
- the diaphragm muscle provides an important function for the respiration of human beings.
- the phrenic nerves normally transmit signals from the brain to cause the contractions of the diaphragm muscle necessary for breathing.
- various conditions can prevent appropriate signals from being delivered to the phrenic nerves. These include: permanent or temporary injury or disease affecting the spinal cord or brain stem; Amyotrophic Lateral Sclerosis (ALS); decreased day or night ventilatory drive (e.g., central sleep apnea, Ondine's curse); and decreased ventilatory drive while under the influence of anesthetic agents and/or mechanical ventilation. These conditions affect a significant number of people.
- ALS Amyotrophic Lateral Sclerosis
- day or night ventilatory drive e.g., central sleep apnea, Ondine's curse
- decreased ventilatory drive while under the influence of anesthetic agents and/or mechanical ventilation.
- Intubation and positive pressure mechanical ventilation may be used for periods of several hours or several days, sometimes weeks, to help critically ill patients breathe while in intensive care units (ICU). Some patients may be unable to regain voluntary breathing and thus require prolonged or permanent mechanical ventilation. Although mechanical ventilation can be initially lifesaving, it has a range of significant problems and/or side effects.
- Mechanical ventilation can be initially lifesaving, it has a range of significant problems and/or side effects.
- a patient who is sedated and connected to a mechanical ventilator cannot breathe normally because the central neural drive to the diaphragm and accessory respiratory muscles are suppressed. Inactivity leads to muscle disuse atrophy and an overall decline in well-being. Diaphragm muscle atrophy occurs rapidly and can be a serious problem to the patient. According to a published study of organ donor patients (Levine et al., New England Journal of Medicine, 358: 1327-1335, 2008), after only 18 to 69 hours of mechanical ventilation, all diaphragm muscle fibers had shrunk on average by 52-57%. Muscle fiber atrophy results in muscle weakness and increased fatigability. Therefore, ventilator-induced diaphragm atrophy could cause a patient to become ventilator-dependent.
- Embodiments of the present disclosure relate to, among other things, systems, devices, and methods for one or more of positioning an intravascular nerve stimulation catheter, selecting electrodes for nerve stimulation, or stimulating nerves.
- Each of the embodiments disclosed herein may include one or more of the features described in connection with any of the other disclosed embodiments.
- a method for positioning an intravascular catheter may include inserting the intravascular catheter into a venous system of a patient, wherein the catheter includes a plurality of electrodes, and multiple electrodes of the plurality of electrodes are configured to emit electrical signals; positioning a distal portion of the catheter in a first position; using one or more electrodes of the plurality of electrodes to acquire an ECG signal; based on the acquired ECG signal, adjusting the distal portion of the catheter to a second position different from the first position; identifying at least one first electrode of the plurality of electrodes to stimulate a first nerve; identifying at least one second electrode of the plurality of electrodes to stimulate a second nerve; and stimulating at least one of the first and second nerves to cause a contraction of a respiratory muscle.
- inserting the intravascular catheter into the venous system may include inserting the intravascular catheter into: 1) at least one of a left subclavian, axillary, cephalic, cardiophrenic, brachial, radial, or left jugular vein, and 2) a superior vena cava;
- the first position may be proximate an atrium of a heart of the patient, and the second position may be in a superior vena cava;
- the ECG signal may be a first ECG signal, and the method may further comprise using one or more electrodes of the plurality of electrodes to acquire a second ECG signal;
- the one or more electrodes used to acquire the first ECG signal may be positioned on a proximal portion of the catheter and may be configured to stimulate the first nerve, and the one or more electrodes used to acquire the second ECG signal may be positioned on a distal portion of the catheter and may be configured to stimulate the second nerve;
- the method may further comprise using one or more electrodes of the plurality of
- a method for positioning an intravascular catheter may include inserting the intravascular catheter into: 1) at least one of a left subclavian vein or a left jugular vein, and 2) a superior vena cava, wherein the catheter includes a plurality of electrodes, and the plurality of electrodes includes a proximal set of electrodes positioned proximate a left phrenic nerve and a distal set of electrodes positioned proximate a right phrenic nerve; using one or more electrodes of the plurality of electrodes to acquire an ECG signal; based on a change in the ECG signal, withdrawing the catheter away from a heart of a patient; stimulating the left phrenic nerve using one or more electrodes of the proximal set of electrodes; and stimulating the right phrenic nerve using one or more electrodes of the distal set of electrodes.
- a method for positioning an intravascular catheter may include inserting the intravascular catheter into a venous system of a patient, wherein the catheter includes a plurality of proximal electrodes and a plurality of distal electrodes; using one or more electrodes of the plurality of proximal electrodes to acquire a first ECG signal, and using one or more electrodes of the plurality of distal electrodes to acquire a second ECG signal; comparing the first ECG signal to the second ECG signal; based on the comparison between the first ECG signal and the second ECG signal, adjusting a position of the catheter; stimulating the first nerve using one or more of the plurality of proximal electrodes; and stimulating the second nerve using one or more of the plurality of distal electrodes.
- any method described herein may additionally or alternatively include one or more of the following features or steps: the first nerve may be a left phrenic nerve, and the second nerve may be a right phrenic nerve; comparing the first ECG signal to the second ECG signal may include comparing an amplitude of a portion of the first ECG signal to an amplitude of a portion of the second ECG signal; the step of comparing may occur a plurality of times during the inserting step; adjusting the position of the catheter may include moving the catheter away from a heart; at least one of stimulating the first nerve or stimulating the second nerve may cause a contraction of a diaphragm; or the method may further include sensing activity of the first nerve using one or more of the proximal electrodes and sensing activity of the second nerve using one or more of the distal electrodes
- a method for positioning an intravascular catheter may include inserting the intravascular catheter into: 1) at least one of a left subclavian vein or a left jugular vein, and 2) a superior vena cava, wherein the catheter includes a plurality of proximal electrodes configured to be positioned proximate a left phrenic nerve and a plurality of distal electrodes configured to be positioned proximate a right phrenic nerve; at multiple positions of the catheter during the inserting step, using one or more electrodes of the plurality of proximal electrodes to acquire a first ECG signal, and using one or more electrodes of the plurality of distal electrodes to acquire a second ECG signal; comparing the first ECG signal to the second ECG signal at several of the multiple positions; based on the comparisons of the first ECG signal to the second ECG signal, determining a desired position of the catheter for nerve stimulation; stimulating the left phrenic nerve using one or more of the plurality of proximal electrode
- any method described herein may additionally or alternatively include one or more of the following features or steps: the method may further include advancing a distal end of the catheter into a region proximate an atrium of a heart; one of the multiple positions may be a position in which the distal end of the catheter is proximate the atrium of the heart, and in the position, the comparison may indicate a difference between an amplitude of the first ECG signal and an amplitude of the second ECG signal that exceeds a predetermined value; the method may further include moving the catheter away from the heart; stimulating the left phrenic nerve may cause a diaphragm contraction, and stimulating the right phrenic nerve may cause a diaphragm contraction; the proximal electrodes used to acquire the first ECG signal may be configured to stimulate the left phrenic nerve, and the distal electrodes used to acquire the second ECG signal may be configured to stimulate the right phrenic nerve.
- FIG. 1 illustrates a nerve stimulation system with an intravascular catheter positioned within a patient, according to an exemplary embodiment.
- FIG. 2 illustrates a nerve stimulation system having a portable control unit, according to an exemplary embodiment.
- FIG. 3 illustrates a wireless configuration of a nerve stimulation system, according to an exemplary embodiment.
- FIG. 4 illustrates an intravascular catheter having a helical portion, according to an exemplary embodiment.
- FIG. 6 illustrates an intravascular catheter having an ultrasound transducer, according to an exemplary embodiment.
- FIG. 7 illustrates a block diagram of a nerve stimulation system having an intravascular catheter and a control unit, according to an exemplary embodiment.
- Electrodes When electrically stimulating nerves or muscles, a variety of goals may be considered. First, it may be desirable to place the electrodes in proximity to the phrenic nerves. Second, it may be desirable to avoid placing electrodes in close proximity to the sinoatrial (SA) node, atrioventricular (AV) node, or the His-Purkinje system located in heart tissue, as electrical stimulation of these anatomical features may cause arrhythmia. Third, when using a device that includes multiple electrodes, it may be desirable to identify particular electrodes that are in close proximity to the nerve. Identifying the proper electrodes may minimize the electrical charge required to effectively stimulate the nerves. Finally, as with any medical procedure, the risk of injury to the patient increases with the length and complexity of the medical procedure. Accordingly, it may be desirable to minimize the length of any procedure to electrically stimulate nerves or muscles.
- the present disclosure is drawn to systems, devices, and methods for one or more of positioning an intravascular catheter for nerve stimulation, selecting electrodes for nerve stimulation, and stimulating nerves.
- embodiments of the present disclosure may use various positioning features to obtain information useful for positioning a transvascular nerve stimulation catheter, or may use information gathered by sensors to select electrodes and parameters for nerve stimulation.
- FIG. 1 illustrates a system 10 that includes a transvascular nerve stimulation catheter 12 and a control unit 14 .
- Catheter 12 may include a plurality of electrodes 34 .
- Catheter 12 may be operably connected (e.g., hardwired, wireless, etc.) to a control unit 14 .
- the control unit 14 may be programmed to perform any of the functions described herein in connection with system 10 .
- the control unit 14 may include a remote controller 16 to allow a patient or health professional to control operation of the control unit 14 at a distance from the control unit 14 .
- the controller 16 may include a handheld device, as illustrated in FIG. 1 .
- controller 16 may include a footswitch/pedal, a voice-activated, touch-activated, or pressure-activated switch, or any other form of a remote actuator.
- the control unit 14 may include a touch screen 18 and may be supported by a cart 20 .
- catheter 12 may be positioned to electrically stimulate one or both of the left and right phrenic nerves 26 , 28 to cause contraction of the diaphragm muscle 30 to initiate or support a patient breath.
- the proximal portion of catheter 12 may be positioned in a left jugular vein 32
- the distal portion of catheter 12 may be positioned in superior vena cava 24 .
- catheter 12 can be placed into and advanced through other vessels providing access to the locations adjacent the target nerve(s) (e.g., phrenic nerves), such as: the jugular, axillary, cephalic, cardiophrenic, brachial, or radial veins.
- catheter 12 may use other forms of stimulation energy, such as ultrasound, to activate the target nerves.
- the system 10 can target other respiratory muscles (e.g., intercostal) either in addition to, or alternatively to, the diaphragm 30 .
- the energy can be delivered via one or more methods including transvascular, subcutaneous, nerve cuffs, transdermal stimulation, or other techniques known in the field.
- FIG. 2 illustrates an alternative example of system 10 , in which control unit 14 ′ is portable.
- Portable control unit 14 ′ may include all of the functionality of control unit 14 of FIG. 1 , but it may be carried by a patient or other user to provide the patient with more mobility.
- the patient can wear control unit 14 ′ on a belt, on other articles of clothing, or around his/her neck, for example.
- control unit 14 ′ may be mounted to a patient's bed to minimize the footprint of system 10 in the area around the patient, or to provide portable muscle stimulation in the event a bed-ridden patient needs to be transported or moved to another location.
- the system of FIG. 2 may include a controller 16 , shown as a handheld controller 16 .
- Handheld controller 16 may include buttons 17 , 19 that can be pressed by a patient or other user to control breathing patterns. In one example, pressing one of buttons 17 , 19 can initiate a “sigh” breath, which may cause a greater volume of air to enter the patient's lungs than in a previous breath.
- a sigh breath may result when electrodes 34 of catheter 12 are directed to stimulate one or more of the phrenic nerves 26 , 28 at a higher level than a normal breath (i.e., a stimulation train having a longer duration of stimulation or having pulses with a higher amplitude, pulse width, or frequency).
- Higher amplitude stimulation pulses can recruit additional nerve fibers, which in turn can engage additional muscle fibers to cause stronger and/or deeper muscle contractions.
- Extended pulse widths or extended durations of the stimulation train can deliver stimulation over longer periods of time to extend the duration of the muscle contractions.
- longer pulse widths have the potential to help expand the lower lung lobes by providing greater or extended negative pressure around the outside of the lungs. Such negative pressure has the potential to help prevent or mitigate a form of low pressure lung injury known as atelectasis.
- the increased stimulation of the one or more phrenic nerves 26 , 28 may result in a more forceful contraction of the diaphragm 30 , causing the patient to inhale a greater volume of air, thereby providing a greater amount of oxygen to the patient. Sigh breaths may increase patient comfort.
- buttons 17 , 19 may allow the patient or other user to start and stop stimulation therapy, or to increase or decrease stimulation parameters, including stimulation charge (amplitude ⁇ pulse width), frequency of pulses in a stimulation train, or breath rate.
- LED indicators or a small LCD screen (not shown) on the controller may provide other information to guide or inform the operator regarding the stimulation parameters, the feedback from the system sensors, or the condition of the patient.
- Remote controller 16 may be used as described in connection with FIGS. 1 and 2 . In other examples, remote controller 16 may be in the form of a smartphone, tablet, watch or other wearable device.
- catheter 12 may include a stimulation array comprising a plurality of electrodes 34 or other energy delivery elements.
- electrodes 34 may be surface electrodes located on an outer wall of catheter 12 .
- electrodes 34 may be positioned radially inward relative to the outer wall of catheter 12 (e.g., exposed through openings in the outer wall).
- the electrodes 34 may include printed electrodes as described in U.S. Pat. No. 9,242,088, which is incorporated by reference herein (see below).
- Electrodes 34 may extend partially around the circumference of catheter 12 . This “partial” electrode configuration may allow electrodes 34 to target a desired nerve for stimulation, while minimizing application of electrical charge to undesired areas of the patient's anatomy (e.g., other nerves or the heart).
- catheter 12 may include a proximal set 35 of electrodes 34 configured to be positioned proximate to and stimulate left phrenic nerve 26 and a distal set 37 of electrodes 34 configured to be positioned proximate to and stimulate right phrenic nerve 28 .
- electrodes 34 may be arranged in rows extending along the length of catheter 12 .
- proximal set 35 may include two rows
- distal set 37 may include two rows.
- control units described herein can have any of the functionality of the control units described in the above-referenced patent documents (e.g., the control units described herein can implement the methods of nerve stimulation described in the incorporated documents).
- one or more electrodes 34 may be selected from the proximal set 35 for stimulation of left phrenic nerve 26 , and one or more electrodes 34 may be selected from the distal set 37 for stimulation of right phrenic nerve 28 .
- Catheter 12 may stimulate nerves using monopolar, bipolar, or tripolar electrode combinations, or using any other suitable combination of electrodes 34 .
- a second or third stimulation array can be used to stimulate other respiratory muscles.
- the controller and sensors described herein may be used to coordinate stimulation to achieve the desired muscle activation, breath, or level of respiratory support.
- Catheter 12 may further include one or more lumens. Each lumen may extend from a proximal end of catheter 12 to a distal end of catheter 12 , or to a location proximate the distal end of catheter 12 .
- the lumens may contain medical devices, such as a guidewire or an optical fiber camera.
- the one or more lumens may be used for any suitable purpose, such as drawing blood samples or providing a pathway for delivering medications into the patient.
- lumens may contain or be fluidly connected to sensors, such as blood gas sensors or pressure sensors.
- catheter 12 may each illustrate different features and different combinations of features.
- catheter 12 may include any combination of the features that are described herein. Accordingly, the features of catheter 12 are not limited to the specific combinations shown in the various figures.
- a hub 36 may be connected to the proximal end of catheter 12 .
- Hub 36 may include a conductive surface and can act as a reference electrode during monopolar stimulation or sensing.
- hub 36 may be sutured on a patient's skin.
- hub 36 may be used as an ECG electrode.
- FIG. 4 illustrates catheter 12 inserted into left jugular vein 32 and superior vena cava 24 .
- catheter 12 includes a plurality of electrodes 34 , with proximal electrodes 34 positioned near left phrenic nerve 26 and distal electrodes 34 positioned near right phrenic nerve 28 .
- Catheter 12 may further include three lumens (not shown) that connect with extension lumens 38 , 40 , 42 that extend proximally from hub 36 .
- the distal portion of catheter 12 may be configured to assume a helical shape 44 when positioned within the patient. Helical shape 44 may help anchor catheter 12 to the vessel wall to stabilize catheter 12 during nerve stimulation.
- helical shape 44 may be obtained by using a stiffening wire inserted into a lumen of catheter 12 via an extension lumen 38 , 40 , or 42 .
- the stiffening wire may include a shape-memory material (e.g., Nitinol) biased to a helical shape, stainless steel, or any other suitable material.
- the portion of catheter 12 configured to assume the helical shape 44 may include materials having a lower stiffness than other portions of catheter 12 .
- the materials along helical shape 44 may be thinner or more flexible than the materials along the remaining length of catheter 12 .
- catheter 12 may include a temperature-activated shape memory material (e.g., Nitinol) along a portion of its length, such that the shape-memory material of catheter 12 may have a substantially straight shape at room temperature and may assume a helical shape when heated within the patient's body.
- a temperature-activated shape memory material e.g., Nitinol
- each of the extension lumens 38 , 40 , and 42 may end in a proximal-most port 38 a , 40 a , and 42 a , respectively.
- the lumens internal to catheter 12 may terminate in one or more distal ports.
- internal lumens that communicate with lumens 38 , 40 , and 42 terminate at a distal port 48 , medial port 50 , and proximal port 52 , respectively.
- Lumens 38 , 40 , 42 and their corresponding internal lumens may be used to transport fluid to and from the patient, such as to deliver medications or withdraw blood or other bodily fluids.
- FIG. 5 illustrates an optical fiber camera 46 inserted into lumen 38 , extending through a corresponding internal lumen, and exiting from distal port 48 .
- FIG. 6 illustrates another example of catheter 12 .
- Catheter 12 is similar to the catheter of FIG. 5 , except electrodes 34 may be formed by conductive inks (such as silver, gold, graphine, or carbon flakes suspended in polymer or other media) printed on the surface of catheter 12 , as described in U.S. Pat. No. 9,242,088, incorporated by reference herein (see above). These conductive inks may be deposited and adhered directly onto catheter 12 and sealed, except for the exposed electrodes 34 , with an outer polyurethane or other flexible insulative film.
- conductive inks such as silver, gold, graphine, or carbon flakes suspended in polymer or other media
- the exposed electrodes 34 may be coated (e.g., with titanium nitride) for purposes such as one or more of: enhancing electrical properties, such as conductivity and surface area; providing corrosion resistance; and reducing the potential for formation of silver oxide, which could be toxic.
- the conductive ink trace of distal electrodes may travel proximally along catheter 12 past the more proximal electrodes 34 .
- FIG. 6 further illustrates catheter 12 having an ultrasound transducer 54 at a distal end of catheter 12 , which will be described further below.
- FIG. 7 illustrates a block diagram of the various components of system 10 .
- the electrodes 34 a - 34 j , hub 36 , and lumens 38 , 40 , 42 , 58 , and 60 may be part of catheter 12 described herein.
- Catheter 12 may have any number of electrodes and any number of lumens. Five lumens are illustrated in FIG. 7 , but in different examples, the catheter may include one, two, three, four, or more than five lumens.
- catheter 12 may have three lumens (e.g., extension lumens 38 , 40 , 42 and corresponding internal lumens), which each may hold one or more of a guidewire or optical fiber camera, or may be used for fluid delivery or blood sample extraction (box 43 ).
- catheter 12 may include four lumens, with one lumen 58 holding or fluidly connected to a pressure sensor 90 , one lumen 60 holding or fluidly connected to a blood gas sensor 62 , and the other two lumens holding a guidewire or optical fiber camera and/or being used for fluid delivery or blood sample extraction.
- any lumen of system 10 may contain or be fluidly connected to any of the devices (e.g., sensors, guidewire, optical fiber camera) described herein and/or may be used for any of the functions described herein (e.g., fluid delivery, blood sample extraction).
- System 10 may include a controller 64 , which may be part of any of the control units described herein. Each of the components of system 10 may be operably coupled to the controller 64 , and controller 64 may manage operation of electrodes 34 during nerve stimulation, control the gathering of information by various sensors and electrodes 34 , and control fluid delivery or extraction. It should be understood that the various modules described herein may be part of a computing system and are separated in FIG. 7 for explanatory purposes only; it is not necessary for the modules to be physically separate.
- Electrodes 34 a - 34 j may be electronically coupled to switching electronics 56 , which may be communicably coupled to controller 64 . As shown in FIG. 7 , a portion of electrodes 34 may be distal electrodes 34 a - 34 d , and a portion of electrodes 34 may be proximal electrodes 34 g - 34 j . Other electrodes 34 , such as electrodes 34 e and 34 f , may be positioned between the proximal and distal electrodes and, depending on the placement of catheter 12 , may be used for stimulating either left or right phrenic nerves 26 , 28 . Hub 36 also may be connected to switching electronics 56 and may be used as an electrode.
- Electrodes 34 a - 34 j may be used for both electrically stimulating nerves and for gathering physiological information.
- a first combination of electrodes e.g., one, two, three, or more electrodes
- a second combination of electrodes e.g., one, two, three, or more electrodes
- a second stimulation module channel 72 for stimulation of a second nerve (e.g., the left phrenic nerve).
- Electrical signals may be sent from the first and second stimulation module channels 70 , 72 to the electrode combinations to cause the electrodes to stimulate the nerves.
- more than two electrode combinations e.g., 3, 4, or more
- system 10 may include more than two stimulation module channels.
- Electrodes 34 a - 34 f may be further configured to sense physiological information from a patient, such as nerve activity, ECG, or electrical impedance, as will be described further below.
- one or more of electrodes 34 a - 34 f may be electronically coupled to a signal acquisition module 68 .
- Signal acquisition module 68 may receive signals from electrodes 34 .
- Switching electronics 56 may selectively couple electrodes 34 to first stimulation module channel 70 , second stimulation module channel 72 , or signal acquisition module 68 .
- an electrode 34 e.g., electrode 34 a
- switching electronics 56 may be coupled via switching electronics 56 to signal acquisition module 68 .
- a pair of electrodes e.g., electrodes 34 b and 34 d
- those electrodes may be coupled via switching electronics 56 to first stimulation module channel 70 .
- Electrodes 34 g and 34 h may be coupled via switching electronics 56 to second stimulation module channel 72 .
- Switching electronics 56 may change which electrodes 34 are used for stimulation and which are used for sensing at any given time.
- any electrode 34 can be used for nerve stimulation and any electrode 34 can be used for sensing functions described herein.
- each electrode 34 may be configured to stimulate nerves, and each electrode 34 may be configured to sense physiological information.
- Signal acquisition module 68 may further be coupled to one or more sensors configured to gather physiological information from a patient.
- system 10 may include one or more of blood gas sensor 62 or pressure sensor 90 . These sensors may be located in lumens of catheter 12 , outside of the patient in fluid communication with a lumen, on an outer surface of catheter 12 , or in any other suitable location.
- blood gas sensor 62 may be housed in or fluidly connected to lumen 60
- pressure sensor 90 may be housed in or fluidly connected to lumen 58 .
- Blood gas sensor 62 may measure the amount of O 2 or CO 2 in the patient's blood.
- Pressure sensor 90 may measure the central venous pressure (CVP) of the patient.
- CVP central venous pressure
- Signal acquisition module 68 may transmit the signals received from one or more of electrodes 34 , blood gas sensor 62 , and/or pressure sensor 90 to the appropriate processing/filtering module of system 10 .
- signals from pressure sensor 90 may be transmitted to a central venous pressure signal processing/filtering module 84 , where the signals are processed and filtered to aid in interpretation of CVP information.
- signals from blood gas sensor 62 may be transmitted to a blood gas signal processing/filtering module 86 for processing and filtering to determine blood gas levels.
- Signals from electrodes 34 when they are used for sensing, may be sent to nerve signal processing/filtering module 80 , ECG signal processing/filtering module 82 , or impedance signal processing/filtering module 88 , as appropriate.
- Signals from electrodes 34 or other sensors may be sent to amplification module 78 , if necessary, to amplify the signals prior to being sent to the appropriate processing/filtering module.
- Controller 64 may further communicate with display 74 , which may serve as a user interface and may have a touch screen 18 (see FIG. 1 ).
- System 10 may further include software/firmware 76 , which may contain the instructions necessary for carrying out the various functions described herein.
- system 10 may include data storage 79 , for storing information gathered during sensing operations of catheter 12 , and/or for storing instructions related to the operation of any of the modules or instructions for carrying out any of the functions described herein.
- Catheter 12 may include a variety of positioning features that may help a user to position catheter 12 within a patient. Some positioning features may be visualization aids, such as optical fiber camera 46 shown in FIG. 5 or ultrasound transducer 54 shown in FIG. 6 . Other positioning features may be sensors to sense physiological parameters, such as pressure sensor 90 . Electrodes 34 , which can be used to stimulate a nerve, also may be used as sensors to gather information that can then be used to position catheter 12 . For example, electrodes 34 may gather information related to nerve activity (e.g., the left or right phrenic nerve), ECG signals, and/or impedance. Accordingly, a sensing electrode 34 may be considered a positioning feature. Each of the positioning features and how they are used to help position catheter 12 will be described in further detail below.
- Catheter 12 may include any combination of positioning features, including one or more visualization aids, sensors (e.g., pressure), or electrodes capable of sensing various types of information.
- the control units described herein whether on a cart, wearable on a patient, or wireless, may be configured to process information gathered by the various positioning features described herein (e.g., visualization aids, sensors, and electrodes), as well as perform the various computerized functions described herein.
- ultrasound transducer 54 may be used in addition to or instead of optical fiber camera 46 to obtain information useful for positioning catheter 12 within the patient.
- Ultrasound transducer 54 may be secured temporarily or permanently to the exterior of catheter 12 , as shown in FIG. 6 , or may be positioned temporarily or permanently within a lumen of catheter 12 (e.g., positioned to extend from the distal end of a lumen of catheter 12 ).
- Positioning ultrasound transducer 54 near the distal tip of catheter 12 may allow the user to view the inside of vessels and also ensure that the tip of catheter 12 is not positioned in an undesired location (e.g., in the atrium of the heart).
- ultrasound transducer 54 may allow visualization of a heart valve, which could indicate that the catheter 12 has entered the atrium and may need to be retracted.
- the ultrasound images may provide information (e.g., calculated or visual) about the diameter of blood vessels and/or blood flow within the vessels. The user may then use vessel diameter information, blood flow, and real time images of the inside of the patient's vessels to position catheter 12 in a desired position.
- information e.g., calculated or visual
- CVP measurements from pressure sensor 90 may further aid in positioning catheter 12 within the patient. Normal values may vary between 4-12 cm H 2 O.
- the CVP waveform may change based on the location, relative to the patient's heart, of the port (e.g., 46 , 48 , or 50 ) in communication with pressure sensor 90 . In one example, CVP measurements may decline as the relevant port approaches the patient's heart. A user may read the changing CVP waveforms to help position the catheter 12 in a desired location relative to the patient's heart.
- the CVP waveform has several components.
- the (a) wave corresponds to the right atrial contraction and correlates with the P wave on the ECG.
- the (c) wave corresponds to the cusp of the tricuspid valve protruding backwards through the atrium, as the right ventricle begins to contract.
- the (c) wave correlates with the end of the QRS complex on the ECG.
- the (x) descent corresponds to the movement of the right ventricle, which descends as it contracts. The downward movement decreases the pressure in the right atrium. At this stage, there is also atrial diastolic relaxation, which further decreases the right atrial pressure.
- the (x) descent happens before the T wave on the ECG.
- the (v) wave occurs as blood fills the right atrium and hits the tricuspid valve, causing a back-pressure wave.
- the (v) wave occurs after the T wave of the ECG.
- the (y) descent is a pressure decrease caused by the tricuspid valve opening in early ventricular diastole and occurs before the P wave of the ECG.
- the amplitudes of a, c, x, v, y may change depending on the position of the catheter with respect to the heart.
- the signature change of the CVP waveform can guide in the placement of catheter 12 .
- a method for positioning intravascular catheter 12 may include positioning catheter 12 in a first position in a venous system of a patient, wherein catheter 12 includes a plurality of electrodes 34 and at least one lumen extending from a proximal end of catheter 12 to a distal end of catheter 12 , and each electrode 34 of the plurality of electrodes 34 is configured to emit electrical signals to stimulate a nerve; measuring a central venous pressure of the patient using a pressure sensor 90 fluidly connected to the at least one lumen; and based on the central venous pressure, adjusting catheter 12 to a second position different from the first position.
- Nerve signals acquired by electrodes 34 also may be used to aid in positioning catheter 12 within a patient.
- the electrical signal from a nerve may be amplified by amplification module 78 and processed by nerve signal processing/filtering module 80 .
- the amplified and filtered signals from one or more electrodes 34 then may be compared to an expected signal from the targeted nerve (e.g., left or right phrenic nerve) to identify electrodes 34 in close proximity to the target nerve and to identify the optimal one or more electrodes for nerve stimulation. For example, electrodes 34 returning a higher strength and/or higher quality signal may be located closer to the target nerve.
- Phrenic nerve activity can be recorded using bipolar or monopolar electrodes.
- Phrenic nerve discharge can be amplified and filtered (e.g., 100 Hz to 5 kHz), and a moving average can be obtained using a third-order Paynter filter with a 20 or 50 ms time constant.
- Phrenic nerve discharge also can be filtered at 10 Hz to 5 kHz for analysis of spectral composition. A sampling rate of 1-10 kHz can be used to capture the nerve activity.
- the parameters acquired during nerve activity sensing can be used to detect if the signal is from the phrenic nerve or another nerve.
- Sensed parameters can include a number of physiological parameters, such as amplitude, inspiration duration, and/or breathing rate. For example, if the sensed amplitude shows proximity of the electrodes 34 to the nerve and the nerve is a phrenic nerve, the duration of pulses in a train should match the sensed inspiration duration, and the frequency of the trains should match the sensed breathing rate.
- the sensed signals from a nerve can be compared to known nerve signatures (e.g., of phrenic nerves) to confirm that the nerve signal is from the desired nerve.
- Electrodes 34 may be used to acquire ECG signals, with hub 36 optionally being used as a reference electrode.
- the ECG signal (e.g., morphology, amplitudes, and spectral content) may vary depending on the location, relative to the patient's heart, of the electrodes being used to measure the signal. Monitoring changes in the ECG signal as catheter 12 is being positioned may aid in identifying desired or undesired placement. For example, it may be undesired for catheter 12 to be placed in the atrium of the patient's heart.
- one of the distal electrodes 34 on catheter 12 may be designated as a probe.
- Other electrodes along the length of catheter 12 and in some cases in contact with the skin of the patient, may be used to detect an ECG signal, which can optionally be displayed by control unit 14 via screen 18 .
- Catheter 12 may be advanced through superior vena cava 24 towards the heart. As catheter 12 enters a region proximate the right atrium, or enters the right atrium, the P-wave portion of the ECG may become elevated and create an augmented peaked P-wave, indicating that the tip of the catheter 12 lies in or very close to the right atrium.
- the positive deflection in the P-wave occurs when current flows to the probing electrode, and a negative deflection when it flows away.
- the P-wave depolarizes down the right atrium from the SA node, away from an electrode 34 in superior vena cava 24 , and is therefore negative.
- the amplitude of the P-wave is related to the inverse square rule, whereby the amplitude is inversely proportional to the square of the distance from the current source.
- the P-wave increases greatly in negative amplitude as catheter 12 approaches the atrium. When the tip enters the atrium, it is just beyond the SA node, and the first portion of the P-wave depolarizes towards it. This results in a brief, small positive deflection followed instantly by a deep negative deflection.
- a distal combination of electrodes 34 e.g., a distal pair
- a proximal combinations of electrodes 34 e.g., a proximal pair
- the P-waves can be compared using standard signal processing techniques and a delta value can be determined as the catheter 12 is advanced through the vessel (e.g. superior vena cava 24 ) towards the heart. As catheter 12 is advanced in close proximity to or into the atrium, the delta value will change significantly, exceeding a predetermined value.
- the system 10 can provide an indicator to the operator, as described previously, and catheter 12 can be withdrawn 1 to 2 cm.
- This method can also utilize one or more reference electrodes 34 located along the length of the catheter or positioned externally on the patient's body.
- the impedance presented to injected current may be dependent on the conductivity of the fluid, or adjacent tissue, in the local area between a pair of sensing electrodes 34 .
- the conductivity further may depend on the cross-sectional area of the blood vessel at the site of the sending electrodes 34 .
- the impedance of an electrode 34 may vary depending on the medium in which it is resting. For example, an electrode 34 placed in a relatively large body of conductive fluid may have a lower impedance than one resting against a vessel wall. The impedance of an electrode 34 can therefore be used to determine whether it is adjacent to a vessel wall or resting in a larger body of conductive fluid.
- Electrodes 34 that are on a proximal portion of catheter 12 may have a higher impedance than other electrodes 34 , because the proximal portion of catheter 12 may be positioned in tissue (e.g., fatty) near an insertion site, rather than resting in the fluid of a blood vessel. Electrodes 34 farther down the shaft of catheter 12 , towards a central portion of catheter 12 , might have progressively lower impedances as the diameter of the vessel increases (e.g., as the vessel approaches superior vena cava 24 ). Electrodes 34 on the portion of catheter 12 that is floating in fluid in superior vena cava 24 might have a low impedance.
- Electrodes 34 on the distal portion of catheter 12 might be in direct contact with the vessel wall and therefore may have a higher impedance.
- a graph of the impedances of all of the electrodes 34 in this example may have a U-shaped curvature, as impedances may be higher at each end of catheter 12 and lower towards the central portion of catheter 12 .
- the change in impedance of an electrode 34 as it progresses through the patient's vessels can provide information about the location of that electrode 34 .
- the differences in impedances of electrodes 34 along the length of catheter 12 may provide information about the placement of catheter 12 .
- catheter 12 may be placed in a vessel that varies in diameter, with distal electrodes 34 resting in a desired vessel (e.g., in superior vena cava 24 ).
- the impedances of different, more proximal electrodes would be expected to vary depending on their position in the venous system.
- catheter 12 when placed in a desired position, would be expected to include: 1) electrodes 34 whose impedances are reduced as the electrodes 34 approach the wall of a vessel (e.g., superior vena cava 24 ); and 2) electrodes 34 having impedance profiles with a desired shape.
- measured impedances may be compared to impedance thresholds or profiles stored in data storage 79 , to determine if one or more electrodes 34 are properly placed.
- the impedances of distal electrodes can be compared to the impedances of proximal electrodes as the catheter 12 is advanced through superior vena cava 24 towards the atrium. As the distal electrodes enter the atrium, the difference between the distal and proximal impedance measurements may exceed a predetermined threshold allowing the system 10 to provide an indication to the operator. Catheter 12 can then be withdrawn (or advanced depending on the application) to the desired location. Signal filtering, processing, and analytical techniques known in the art can be used to assess the impedance measurements in real time.
- a catheter 12 that is under-inserted may have few or no electrodes 34 resting in the desired vessel (e.g., superior vena cava 24 ), which would result in electrode impedance profiles having different shapes than the desired shape.
- a catheter 12 that is over-inserted may have one or more electrodes 34 that are close to, or in contact with, the atrium, which may also result in impedance profiles having different shapes than the desired shape.
- the impedance of one or more electrodes 34 is monitored as catheter 12 is inserted into the patient and electrodes 34 move through the patient's venous system. Changes in the impedance profiles can be displayed to the health professional performing the insertion, and the impedance profiles can be used to confirm proper placement of catheter 12 .
- catheter 12 may include a strain gauge and/or an accelerometer (not shown). Either the strain gauge or the accelerometer may be placed at or near the distal end of catheter 12 , in one of the lumens. The strain gauge could detect flex in a distal portion of catheter 12 , and the accelerometer could detect movement/acceleration of the distal portion of catheter 12 . Information from the strain gauge and/or accelerometer could be used to determine whether the distal end of catheter 12 is in the atrium (e.g., heartbeats may cause movement of the distal end of catheter 12 ). The strain gauge or the accelerometer could be an integral, permanent part of catheter 12 or could be positioned in a lumen of catheter 12 temporarily during positioning of catheter 12 .
- Nerve signals acquired by sensing electrodes 34 may be used to select electrodes 34 for nerve stimulation. Electrodes 34 that are closer to a target nerve may sense nerve activity having a higher amplitude, while electrodes 34 that are farther from a target nerve may sense nerve activity having a lower amplitude. If a greater diaphragm response is desired, electrodes 34 that are closer to the nerve, as determined based on received nerve activity signals, may be selected for nerve stimulation. In other cases, if less diaphragm response is desired, electrodes 34 that are farther from the nerve, as determined based on received nerve activity signals, may be selected for nerve stimulation.
- Typical nerve signals for, e.g., phrenic nerves follow a pattern that has distinct characteristics (e.g., spectral characteristics and modulation over time).
- the sensed nerve signals from different electrodes 34 can be analyzed for their spectral and temporal characteristics.
- the optimal electrodes 34 can be selected based on the amplitude of the signal and how strongly the signal correlates to the typical pattern.
- a fast Fourier transform can be used to provide a correlation factor to a reference signal in near real-time.
- the sensed signals can be frequency filtered in the frequency range of interest, based on the typical characteristics of the phrenic nerve signal, and then analyzed over time to observe periods or bursts of activity in the frequency range of interest.
- the processed nerve activity waveforms additionally may be used to determine parameters for nerve stimulation.
- the processed waveforms may provide information regarding intrinsic breath rate (e.g., if the patient is attempting to breathe on his/her own) and nerve signal amplitude.
- the stimulation parameters may be adjusted based on the breath rate of previous stimulated breaths (e.g., to increase or decrease the breath rate, as sensed by the sensing electrodes) and nerve activity resulting from stimulation during previous breaths (e.g., to increase or decrease the strength of stimulation).
- Various parameters that may be adjusted include stimulation pulse amplitude, stimulation pulse width, stimulation pulse frequency, stimulation duration, and the interval between stimulations/pulse trains (e.g., stimulated breath rate). Accordingly, sensed nerve activity signals may be used to determine and adjust the nerve stimulation parameters in a closed-loop system.
- Impedance information may be used to determine a breath rate of the patient in order to adjust nerve stimulation parameters (e.g., stimulation pulse amplitude, stimulation pulse width, stimulation pulse frequency, stimulation duration, and the interval between stimulations/pulse trains (e.g., stimulated breath rate)).
- nerve stimulation parameters e.g., stimulation pulse amplitude, stimulation pulse width, stimulation pulse frequency, stimulation duration, and the interval between stimulations/pulse trains (e.g., stimulated breath rate)
- Electrical impedance of lung tissue changes as a function of air content. Accordingly, the electrical impedance of the thorax changes during inhalation and exhalation.
- the thorax presents an electrical impedance that includes two components: a relatively constant value and a varying value.
- Changes in impedance may result from the following two effects during inspiration: 1) there is an increase in the gas volume of the chest in relation to the fluid volume, which may cause conductivity to decrease, and 2) the length of the conductance path (e.g., between two electrodes) increases when the lungs expand. These effects may cause impedance to increase during inspiration. There is an approximately linear correlation between the impedance changes and the volume of respirated air.
- the varying component of impedance i.e., respirative impedance
- This varying voltage component can then be used to determine the person's breathing rate.
- increasing stimulation pulse amplitude, width and/or frequency may increase lung volume during a stimulated breath.
- Increasing stimulation duration may increase lung volume and/or increase the amount of time air remains in the lungs during a stimulated breath, allowing for an extended gas exchange period.
- Increasing the stimulated breath rate may allow for additional gas exchange periods over a given period of time, which may increase the amount and/or speed of gas exchange.
- system 10 may assist a user in one or more of positioning a transvascular catheter, selecting optimal electrodes for nerve stimulation, or selecting or adjusting parameters for nerve stimulation.
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Veterinary Medicine (AREA)
- Public Health (AREA)
- General Health & Medical Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Cardiology (AREA)
- Surgery (AREA)
- Molecular Biology (AREA)
- Medical Informatics (AREA)
- Pathology (AREA)
- Biophysics (AREA)
- Physics & Mathematics (AREA)
- Neurology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Physiology (AREA)
- Neurosurgery (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Pulmonology (AREA)
- Electrotherapy Devices (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Abstract
A method for positioning an intravascular catheter may include inserting the intravascular catheter into a venous system of a patient, wherein the catheter includes a plurality of electrodes, and multiple electrodes of the plurality of electrodes are configured to emit electrical signals; positioning a distal portion of the catheter in a first position; using one or more electrodes of the plurality of electrodes to acquire an ECG signal; based on the acquired ECG signal, adjusting the distal portion of the catheter to a second position different from the first position; identifying at least one first electrode of the plurality of electrodes to stimulate a first nerve; identifying at least one second electrode of the plurality of electrodes to stimulate a second nerve; and stimulating at least one of the first and second nerves to cause a contraction of a respiratory muscle.
Description
- This disclosure relates to systems, devices, and methods for one or more of positioning an intravascular nerve stimulation catheter, selecting electrodes for nerve stimulation, or stimulating nerves.
- Electrical stimulation of nerves may be used to control muscle activity or to generate or attenuate sensations. Nerves and muscles may be stimulated by placing electrodes in, around, or near the nerves and muscles and by activating the electrodes by means of an implanted or external source of energy (e.g., electricity).
- The diaphragm muscle provides an important function for the respiration of human beings. The phrenic nerves normally transmit signals from the brain to cause the contractions of the diaphragm muscle necessary for breathing. However, various conditions can prevent appropriate signals from being delivered to the phrenic nerves. These include: permanent or temporary injury or disease affecting the spinal cord or brain stem; Amyotrophic Lateral Sclerosis (ALS); decreased day or night ventilatory drive (e.g., central sleep apnea, Ondine's curse); and decreased ventilatory drive while under the influence of anesthetic agents and/or mechanical ventilation. These conditions affect a significant number of people.
- Intubation and positive pressure mechanical ventilation (MV) may be used for periods of several hours or several days, sometimes weeks, to help critically ill patients breathe while in intensive care units (ICU). Some patients may be unable to regain voluntary breathing and thus require prolonged or permanent mechanical ventilation. Although mechanical ventilation can be initially lifesaving, it has a range of significant problems and/or side effects. Mechanical ventilation:
-
- often causes ventilator-induced lung injury (VILI) and alveolar damage, which can lead to accumulation of fluid in the lungs and increased susceptibility to infection (ventilator-associated pneumonia, VAP);
- commonly requires sedation to reduce discomfort and anxiety in acutely intubated patients;
- leads to rapid atrophy of the disused diaphragm muscle (ventilator-induced diaphragm dysfunction, VIDD);
- can adversely affect venous return because the lungs are pressurized and the diaphragm is inactive;
- interferes with eating and speaking;
- requires apparatus that is not readily portable; and
- increases the risk of dying if the patient fails to regain normal breathing and becomes ventilator-dependent.
- A patient who is sedated and connected to a mechanical ventilator cannot breathe normally because the central neural drive to the diaphragm and accessory respiratory muscles are suppressed. Inactivity leads to muscle disuse atrophy and an overall decline in well-being. Diaphragm muscle atrophy occurs rapidly and can be a serious problem to the patient. According to a published study of organ donor patients (Levine et al., New England Journal of Medicine, 358: 1327-1335, 2008), after only 18 to 69 hours of mechanical ventilation, all diaphragm muscle fibers had shrunk on average by 52-57%. Muscle fiber atrophy results in muscle weakness and increased fatigability. Therefore, ventilator-induced diaphragm atrophy could cause a patient to become ventilator-dependent. It has been estimated that over 600,000 U.S. patients will be ventilator-dependent and require prolonged mechanical ventilation by the year 2020. Zilberberg et al., “Growth in adult prolonged acute mechanical ventilation: implications for healthcare delivery,” Crit Care Med., 2008 May, 36(5): 1451-55.
- Embodiments of the present disclosure relate to, among other things, systems, devices, and methods for one or more of positioning an intravascular nerve stimulation catheter, selecting electrodes for nerve stimulation, or stimulating nerves. Each of the embodiments disclosed herein may include one or more of the features described in connection with any of the other disclosed embodiments.
- In one example, a method for positioning an intravascular catheter may include inserting the intravascular catheter into a venous system of a patient, wherein the catheter includes a plurality of electrodes, and multiple electrodes of the plurality of electrodes are configured to emit electrical signals; positioning a distal portion of the catheter in a first position; using one or more electrodes of the plurality of electrodes to acquire an ECG signal; based on the acquired ECG signal, adjusting the distal portion of the catheter to a second position different from the first position; identifying at least one first electrode of the plurality of electrodes to stimulate a first nerve; identifying at least one second electrode of the plurality of electrodes to stimulate a second nerve; and stimulating at least one of the first and second nerves to cause a contraction of a respiratory muscle.
- Any method described herein may additionally or alternatively include one or more of the following features or steps: inserting the intravascular catheter into the venous system may include inserting the intravascular catheter into: 1) at least one of a left subclavian, axillary, cephalic, cardiophrenic, brachial, radial, or left jugular vein, and 2) a superior vena cava; the first position may be proximate an atrium of a heart of the patient, and the second position may be in a superior vena cava; the ECG signal may be a first ECG signal, and the method may further comprise using one or more electrodes of the plurality of electrodes to acquire a second ECG signal; the one or more electrodes used to acquire the first ECG signal may be positioned on a proximal portion of the catheter and may be configured to stimulate the first nerve, and the one or more electrodes used to acquire the second ECG signal may be positioned on a distal portion of the catheter and may be configured to stimulate the second nerve; the method may further include comparing the first ECG signal to the second ECG signal, and based on the comparison, adjusting the distal portion of the catheter to the second position; the second position may be farther from a heart of the patient than the first position; the method may further include using one or more electrodes of the plurality of electrodes to sense at least one of an impedance or nerve activity; or each of the at least one first electrode and the at least one second electrode may be a combination of electrodes.
- In another example, a method for positioning an intravascular catheter may include inserting the intravascular catheter into: 1) at least one of a left subclavian vein or a left jugular vein, and 2) a superior vena cava, wherein the catheter includes a plurality of electrodes, and the plurality of electrodes includes a proximal set of electrodes positioned proximate a left phrenic nerve and a distal set of electrodes positioned proximate a right phrenic nerve; using one or more electrodes of the plurality of electrodes to acquire an ECG signal; based on a change in the ECG signal, withdrawing the catheter away from a heart of a patient; stimulating the left phrenic nerve using one or more electrodes of the proximal set of electrodes; and stimulating the right phrenic nerve using one or more electrodes of the distal set of electrodes.
- Any method described herein may additionally or alternatively include one or more of the following features or steps: the change in the ECG signal may be a change in an amplitude of a P-wave, and the change may occur as a distal end of the catheter enters a region proximate an atrium of the heart; the step of withdrawing the catheter away from the heart may cause a change in the amplitude of the P-wave; the ECG signal may be a first ECG signal acquired by one or more electrodes of the proximal set of electrodes, and the method may further include using one or more electrodes of the distal set of electrodes to acquire a second ECG signal; the method may further include determining a difference between a P-wave of the first ECG signal and a P-wave of the second ECG signal, and withdrawing the catheter away from the heart of the patient when the difference exceeds a predetermined value; the difference may exceed the predetermined value when the catheter is advanced into an atrium of the heart; a hub coupled to the catheter and positioned exterior to the patient may be used with the one or more electrodes of the plurality of electrodes to acquire the ECG signal; or the method may further include monitoring the ECG signal as a distal end of the catheter is inserted into the at least one of the left subclavian vein or the left jugular vein and advanced into the superior vena cava.
- In yet another example, a method for positioning an intravascular catheter may include inserting the intravascular catheter into a venous system of a patient, wherein the catheter includes a plurality of proximal electrodes and a plurality of distal electrodes; using one or more electrodes of the plurality of proximal electrodes to acquire a first ECG signal, and using one or more electrodes of the plurality of distal electrodes to acquire a second ECG signal; comparing the first ECG signal to the second ECG signal; based on the comparison between the first ECG signal and the second ECG signal, adjusting a position of the catheter; stimulating the first nerve using one or more of the plurality of proximal electrodes; and stimulating the second nerve using one or more of the plurality of distal electrodes.
- Any method described herein may additionally or alternatively include one or more of the following features or steps: the first nerve may be a left phrenic nerve, and the second nerve may be a right phrenic nerve; comparing the first ECG signal to the second ECG signal may include comparing an amplitude of a portion of the first ECG signal to an amplitude of a portion of the second ECG signal; the step of comparing may occur a plurality of times during the inserting step; adjusting the position of the catheter may include moving the catheter away from a heart; at least one of stimulating the first nerve or stimulating the second nerve may cause a contraction of a diaphragm; or the method may further include sensing activity of the first nerve using one or more of the proximal electrodes and sensing activity of the second nerve using one or more of the distal electrodes
- In another example, a method for positioning an intravascular catheter may include inserting the intravascular catheter into: 1) at least one of a left subclavian vein or a left jugular vein, and 2) a superior vena cava, wherein the catheter includes a plurality of proximal electrodes configured to be positioned proximate a left phrenic nerve and a plurality of distal electrodes configured to be positioned proximate a right phrenic nerve; at multiple positions of the catheter during the inserting step, using one or more electrodes of the plurality of proximal electrodes to acquire a first ECG signal, and using one or more electrodes of the plurality of distal electrodes to acquire a second ECG signal; comparing the first ECG signal to the second ECG signal at several of the multiple positions; based on the comparisons of the first ECG signal to the second ECG signal, determining a desired position of the catheter for nerve stimulation; stimulating the left phrenic nerve using one or more of the plurality of proximal electrodes; and stimulating the right phrenic nerve using one of more of the plurality of distal electrodes.
- Any method described herein may additionally or alternatively include one or more of the following features or steps: the method may further include advancing a distal end of the catheter into a region proximate an atrium of a heart; one of the multiple positions may be a position in which the distal end of the catheter is proximate the atrium of the heart, and in the position, the comparison may indicate a difference between an amplitude of the first ECG signal and an amplitude of the second ECG signal that exceeds a predetermined value; the method may further include moving the catheter away from the heart; stimulating the left phrenic nerve may cause a diaphragm contraction, and stimulating the right phrenic nerve may cause a diaphragm contraction; the proximal electrodes used to acquire the first ECG signal may be configured to stimulate the left phrenic nerve, and the distal electrodes used to acquire the second ECG signal may be configured to stimulate the right phrenic nerve.
- It may be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the invention, as claimed. As used herein, the terms “comprises,” “comprising,” or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements, but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. The term “exemplary” is used in the sense of “example,” rather than “ideal.”
- The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate exemplary embodiments of the present disclosure and together with the description, serve to explain the principles of the disclosure.
-
FIG. 1 illustrates a nerve stimulation system with an intravascular catheter positioned within a patient, according to an exemplary embodiment. -
FIG. 2 illustrates a nerve stimulation system having a portable control unit, according to an exemplary embodiment. -
FIG. 3 illustrates a wireless configuration of a nerve stimulation system, according to an exemplary embodiment. -
FIG. 4 illustrates an intravascular catheter having a helical portion, according to an exemplary embodiment. -
FIG. 5 illustrates an intravascular catheter having an optical fiber camera, according to an exemplary embodiment. -
FIG. 6 illustrates an intravascular catheter having an ultrasound transducer, according to an exemplary embodiment. -
FIG. 7 illustrates a block diagram of a nerve stimulation system having an intravascular catheter and a control unit, according to an exemplary embodiment. - When electrically stimulating nerves or muscles, a variety of goals may be considered. First, it may be desirable to place the electrodes in proximity to the phrenic nerves. Second, it may be desirable to avoid placing electrodes in close proximity to the sinoatrial (SA) node, atrioventricular (AV) node, or the His-Purkinje system located in heart tissue, as electrical stimulation of these anatomical features may cause arrhythmia. Third, when using a device that includes multiple electrodes, it may be desirable to identify particular electrodes that are in close proximity to the nerve. Identifying the proper electrodes may minimize the electrical charge required to effectively stimulate the nerves. Finally, as with any medical procedure, the risk of injury to the patient increases with the length and complexity of the medical procedure. Accordingly, it may be desirable to minimize the length of any procedure to electrically stimulate nerves or muscles.
- There remains a need for cost-effective, practical, surgically simple, and minimally invasive devices and methods that address one or more of the above goals and can include one or more of a variety of functions, including: determining whether a nerve is the target nerve, stimulating breathing, delivering treatment (e.g., medications), sensing electrical signals from the body (e.g., ECG), sensing internal vascular blood pressure, heart rate, and electrical impedance, and performing tests, such as detecting respiration rate and blood gas levels (e.g, CO2, O2). There is also a need for devices and methods to help patients wean from mechanical ventilation and regain the ability to breathe naturally.
- Accordingly, the present disclosure is drawn to systems, devices, and methods for one or more of positioning an intravascular catheter for nerve stimulation, selecting electrodes for nerve stimulation, and stimulating nerves. In particular, embodiments of the present disclosure may use various positioning features to obtain information useful for positioning a transvascular nerve stimulation catheter, or may use information gathered by sensors to select electrodes and parameters for nerve stimulation.
-
FIG. 1 illustrates asystem 10 that includes a transvascularnerve stimulation catheter 12 and acontrol unit 14.Catheter 12 may include a plurality ofelectrodes 34.Catheter 12 may be operably connected (e.g., hardwired, wireless, etc.) to acontrol unit 14. Thecontrol unit 14 may be programmed to perform any of the functions described herein in connection withsystem 10. In some embodiments, thecontrol unit 14 may include aremote controller 16 to allow a patient or health professional to control operation of thecontrol unit 14 at a distance from thecontrol unit 14. Thecontroller 16 may include a handheld device, as illustrated inFIG. 1 . In some examples,controller 16 may include a footswitch/pedal, a voice-activated, touch-activated, or pressure-activated switch, or any other form of a remote actuator. Thecontrol unit 14 may include atouch screen 18 and may be supported by acart 20. - During use, a proximal portion of
catheter 12 may be positioned in a leftsubclavian vein 22, and a distal portion ofcatheter 12 may be positioned in asuperior vena cava 24. Positioned in this manner,electrodes 34 on the proximal portion ofcatheter 12 may be positioned proximate a leftphrenic nerve 26, andelectrodes 34 on the distal portion ofcatheter 12 may be positioned proximate a rightphrenic nerve 28. Left and rightphrenic nerves diaphragm 30. Accordingly,catheter 12 may be positioned to electrically stimulate one or both of the left and rightphrenic nerves diaphragm muscle 30 to initiate or support a patient breath. In other embodiments, the proximal portion ofcatheter 12 may be positioned in a leftjugular vein 32, and the distal portion ofcatheter 12 may be positioned insuperior vena cava 24. - In further examples,
catheter 12 can be placed into and advanced through other vessels providing access to the locations adjacent the target nerve(s) (e.g., phrenic nerves), such as: the jugular, axillary, cephalic, cardiophrenic, brachial, or radial veins. In addition,catheter 12 may use other forms of stimulation energy, such as ultrasound, to activate the target nerves. In some examples, thesystem 10 can target other respiratory muscles (e.g., intercostal) either in addition to, or alternatively to, thediaphragm 30. The energy can be delivered via one or more methods including transvascular, subcutaneous, nerve cuffs, transdermal stimulation, or other techniques known in the field. -
FIG. 2 illustrates an alternative example ofsystem 10, in which controlunit 14′ is portable.Portable control unit 14′ may include all of the functionality ofcontrol unit 14 ofFIG. 1 , but it may be carried by a patient or other user to provide the patient with more mobility. In addition to carrying thecontrol unit 14′, the patient can wearcontrol unit 14′ on a belt, on other articles of clothing, or around his/her neck, for example. In other examples,control unit 14′ may be mounted to a patient's bed to minimize the footprint ofsystem 10 in the area around the patient, or to provide portable muscle stimulation in the event a bed-ridden patient needs to be transported or moved to another location. - Similar to
FIG. 1 , the system ofFIG. 2 may include acontroller 16, shown as ahandheld controller 16.Handheld controller 16 may includebuttons buttons electrodes 34 ofcatheter 12 are directed to stimulate one or more of thephrenic nerves phrenic nerves diaphragm 30, causing the patient to inhale a greater volume of air, thereby providing a greater amount of oxygen to the patient. Sigh breaths may increase patient comfort. - In other examples,
buttons -
FIG. 3 illustrates another example ofsystem 10 in which acontrol unit 14″ is implanted in the patient, along withcatheter 12.System 10 may further includeremote controller 16 and aprogrammer 98 that communicates withcontrol unit 14″ wirelessly. In this embodiment, each ofprogrammer 98,control unit 14″, andremote controller 16 may include awireless transceiver Control unit 14″ may include all of the electronics, software, and functioning logic necessary to perform the functions described herein. Implantingcontrol unit 14″ as shown inFIG. 3 may allowcatheter 12 to function as a permanent breathing pacemaker.Programmer 98 may allow the patient or health professional to modify or otherwise program the nerve stimulation or sensing parameters.Remote controller 16 may be used as described in connection withFIGS. 1 and 2 . In other examples,remote controller 16 may be in the form of a smartphone, tablet, watch or other wearable device. - Referring to
FIGS. 1-3 ,catheter 12 may include a stimulation array comprising a plurality ofelectrodes 34 or other energy delivery elements. In one example,electrodes 34 may be surface electrodes located on an outer wall ofcatheter 12. In another example,electrodes 34 may be positioned radially inward relative to the outer wall of catheter 12 (e.g., exposed through openings in the outer wall). In yet another example, theelectrodes 34 may include printed electrodes as described in U.S. Pat. No. 9,242,088, which is incorporated by reference herein (see below). -
Electrodes 34 may extend partially around the circumference ofcatheter 12. This “partial” electrode configuration may allowelectrodes 34 to target a desired nerve for stimulation, while minimizing application of electrical charge to undesired areas of the patient's anatomy (e.g., other nerves or the heart). As shown inFIG. 1 ,catheter 12 may include aproximal set 35 ofelectrodes 34 configured to be positioned proximate to and stimulate leftphrenic nerve 26 and adistal set 37 ofelectrodes 34 configured to be positioned proximate to and stimulate rightphrenic nerve 28. As shown inFIG. 5 ,electrodes 34 may be arranged in rows extending along the length ofcatheter 12. In one example, proximal set 35 may include two rows, anddistal set 37 may include two rows. - Furthermore, the catheters described herein may include any features of the nerve stimulation devices described in the following documents, which are all incorporated by reference herein in their entireties: U.S. Pat. No. 8,571,662 (titled “Transvascular Nerve Stimulation Apparatus and Methods,” issued Oct. 29, 2013); U.S. Pat. No. 9,242,088 (titled “Apparatus and Methods for Assisted Breathing by Transvascular Nerve Stimulation,” issued Jan. 26, 2016); U.S. Pat. No. 9,333,363 (titled “Systems and Related Methods for Optimization of Multi-Electrode Nerve Pacing,” issued May 10, 2016); U.S. application Ser. No. 14/383,285 (titled “Transvascular Nerve Stimulation Apparatus and Methods,” filed Sep. 5, 2014); or U.S. application Ser. No. 14/410,022 (titled “Transvascular Diaphragm Pacing Systems and Methods of Use,” filed Dec. 19, 2014). In addition, the control units described herein can have any of the functionality of the control units described in the above-referenced patent documents (e.g., the control units described herein can implement the methods of nerve stimulation described in the incorporated documents).
- During nerve stimulation, one or
more electrodes 34 may be selected from the proximal set 35 for stimulation of leftphrenic nerve 26, and one ormore electrodes 34 may be selected from thedistal set 37 for stimulation of rightphrenic nerve 28.Catheter 12 may stimulate nerves using monopolar, bipolar, or tripolar electrode combinations, or using any other suitable combination ofelectrodes 34. In some examples, a second or third stimulation array can be used to stimulate other respiratory muscles. When multiple nerves or muscles are being stimulated, the controller and sensors described herein may be used to coordinate stimulation to achieve the desired muscle activation, breath, or level of respiratory support. -
Catheter 12 may further include one or more lumens. Each lumen may extend from a proximal end ofcatheter 12 to a distal end ofcatheter 12, or to a location proximate the distal end ofcatheter 12. The lumens may contain medical devices, such as a guidewire or an optical fiber camera. Furthermore, the one or more lumens may be used for any suitable purpose, such as drawing blood samples or providing a pathway for delivering medications into the patient. In some examples, lumens may contain or be fluidly connected to sensors, such as blood gas sensors or pressure sensors. - In this disclosure, the
figures illustrating catheter 12 may each illustrate different features and different combinations of features. However,catheter 12 may include any combination of the features that are described herein. Accordingly, the features ofcatheter 12 are not limited to the specific combinations shown in the various figures. - Referring to
FIG. 2 , ahub 36 may be connected to the proximal end ofcatheter 12.Hub 36 may include a conductive surface and can act as a reference electrode during monopolar stimulation or sensing. In some embodiments,hub 36 may be sutured on a patient's skin. In addition,hub 36 may be used as an ECG electrode. -
FIG. 4 illustratescatheter 12 inserted into leftjugular vein 32 andsuperior vena cava 24. As described above,catheter 12 includes a plurality ofelectrodes 34, withproximal electrodes 34 positioned near leftphrenic nerve 26 anddistal electrodes 34 positioned near rightphrenic nerve 28.Catheter 12 may further include three lumens (not shown) that connect withextension lumens hub 36. The distal portion ofcatheter 12 may be configured to assume ahelical shape 44 when positioned within the patient.Helical shape 44 may help anchorcatheter 12 to the vessel wall to stabilizecatheter 12 during nerve stimulation. Furthermore,helical shape 44 may allowelectrodes 34 to be positioned at different radial positions within the vessel, which may be useful when selecting electrodes for nerve stimulation. For example, in certain instances it may be desirable to stimulate the nerve withelectrodes 34 that are closer to the nerve (e.g., to obtain a stronger diaphragm response), and in other instances it may be desirable to stimulate the nerve withelectrodes 34 that are farther away from the nerve (e.g., to obtain a weaker diaphragm response, or prevent stimulation of the vagus nerve). - In one example,
helical shape 44 may be obtained by using a stiffening wire inserted into a lumen ofcatheter 12 via anextension lumen catheter 12 configured to assume thehelical shape 44 may include materials having a lower stiffness than other portions ofcatheter 12. For example, the materials alonghelical shape 44 may be thinner or more flexible than the materials along the remaining length ofcatheter 12. In another example,catheter 12 may include a temperature-activated shape memory material (e.g., Nitinol) along a portion of its length, such that the shape-memory material ofcatheter 12 may have a substantially straight shape at room temperature and may assume a helical shape when heated within the patient's body. - In some examples, the proximal portion of
catheter 12 additionally or alternatively may have a feature, similar to the distal portion ofcatheter 12, to allow it to assume a helical shape when positioned within left jugular vein 32 (or left subclavian vein 22). Any proximal helical shape may be obtained or result from any of the features described in connection withhelical shape 44. If both the proximal and distal portions ofcatheter 12 assume a helical shape when positioned within the patient, both the proximal anddistal electrodes 34 may be fixed relative to the left and rightphrenic nerves catheter 12 may further include a helical shape along a central portion ofcatheter 12. In one example, the diameter of an expanded helical shape in the central portion may be less than the diameter of the vessel wall, so that the central helical shape is not fixed relative to the vessel wall. Accordingly, the central helical portion may allowcatheter 12 to freely expand and contract in length within the vessel as body movements cause the distance between the proximal helix and the distal helix (which may be fixed relative to the vessel walls) to vary. The central helical shape may be obtained or result from any of the features described in connection withhelical shape 44. - Referring to
FIG. 5 , each of theextension lumens proximal-most port catheter 12 may terminate in one or more distal ports. In one example, internal lumens that communicate withlumens distal port 48,medial port 50, andproximal port 52, respectively.Lumens FIG. 5 illustrates anoptical fiber camera 46 inserted intolumen 38, extending through a corresponding internal lumen, and exiting fromdistal port 48. -
FIG. 6 illustrates another example ofcatheter 12.Catheter 12 is similar to the catheter ofFIG. 5 , exceptelectrodes 34 may be formed by conductive inks (such as silver, gold, graphine, or carbon flakes suspended in polymer or other media) printed on the surface ofcatheter 12, as described in U.S. Pat. No. 9,242,088, incorporated by reference herein (see above). These conductive inks may be deposited and adhered directly ontocatheter 12 and sealed, except for the exposedelectrodes 34, with an outer polyurethane or other flexible insulative film. The exposedelectrodes 34 may be coated (e.g., with titanium nitride) for purposes such as one or more of: enhancing electrical properties, such as conductivity and surface area; providing corrosion resistance; and reducing the potential for formation of silver oxide, which could be toxic. As can be seen inFIG. 6 , the conductive ink trace of distal electrodes may travel proximally alongcatheter 12 past the moreproximal electrodes 34.FIG. 6 further illustratescatheter 12 having anultrasound transducer 54 at a distal end ofcatheter 12, which will be described further below. -
FIG. 7 illustrates a block diagram of the various components ofsystem 10. Theelectrodes 34 a-34 j,hub 36, andlumens catheter 12 described herein.Catheter 12 may have any number of electrodes and any number of lumens. Five lumens are illustrated inFIG. 7 , but in different examples, the catheter may include one, two, three, four, or more than five lumens. In one example,catheter 12 may have three lumens (e.g.,extension lumens catheter 12 may include four lumens, with onelumen 58 holding or fluidly connected to apressure sensor 90, onelumen 60 holding or fluidly connected to ablood gas sensor 62, and the other two lumens holding a guidewire or optical fiber camera and/or being used for fluid delivery or blood sample extraction. It should be understood that any lumen ofsystem 10 may contain or be fluidly connected to any of the devices (e.g., sensors, guidewire, optical fiber camera) described herein and/or may be used for any of the functions described herein (e.g., fluid delivery, blood sample extraction). -
System 10 may include acontroller 64, which may be part of any of the control units described herein. Each of the components ofsystem 10 may be operably coupled to thecontroller 64, andcontroller 64 may manage operation ofelectrodes 34 during nerve stimulation, control the gathering of information by various sensors andelectrodes 34, and control fluid delivery or extraction. It should be understood that the various modules described herein may be part of a computing system and are separated inFIG. 7 for explanatory purposes only; it is not necessary for the modules to be physically separate. -
Electrodes 34 a-34 j may be electronically coupled to switchingelectronics 56, which may be communicably coupled tocontroller 64. As shown inFIG. 7 , a portion ofelectrodes 34 may bedistal electrodes 34 a-34 d, and a portion ofelectrodes 34 may beproximal electrodes 34 g-34 j.Other electrodes 34, such aselectrodes catheter 12, may be used for stimulating either left or rightphrenic nerves Hub 36 also may be connected to switchingelectronics 56 and may be used as an electrode. -
Electrodes 34 a-34 j may be used for both electrically stimulating nerves and for gathering physiological information. When being used for nerve stimulation, a first combination of electrodes (e.g., one, two, three, or more electrodes) may be electrically coupled to a firststimulation module channel 70 for stimulation of a first nerve (e.g., the right phrenic nerve) and a second combination of electrodes (e.g., one, two, three, or more electrodes) may be electrically coupled to a secondstimulation module channel 72 for stimulation of a second nerve (e.g., the left phrenic nerve). Electrical signals may be sent from the first and secondstimulation module channels system 10 may include more than two stimulation module channels. -
Electrodes 34 a-34 f may be further configured to sense physiological information from a patient, such as nerve activity, ECG, or electrical impedance, as will be described further below. When being used for sensing, one or more ofelectrodes 34 a-34 f may be electronically coupled to a signal acquisition module 68. Signal acquisition module 68 may receive signals fromelectrodes 34. -
Switching electronics 56 may selectively coupleelectrodes 34 to firststimulation module channel 70, secondstimulation module channel 72, or signal acquisition module 68. For example, if an electrode 34 (e.g.,electrode 34 a) is being used to acquire a signal, such as an ECG signal, thatelectrode 34 may be coupled via switchingelectronics 56 to signal acquisition module 68. Similarly, if a pair of electrodes (e.g.,electrodes phrenic nerve 28, those electrodes may be coupled via switchingelectronics 56 to firststimulation module channel 70. Finally, if a pair of electrodes (e.g.,electrodes phrenic nerve 26, those electrodes may be coupled via switchingelectronics 56 to secondstimulation module channel 72.Switching electronics 56 may change whichelectrodes 34 are used for stimulation and which are used for sensing at any given time. In one example, anyelectrode 34 can be used for nerve stimulation and anyelectrode 34 can be used for sensing functions described herein. In other words, eachelectrode 34 may be configured to stimulate nerves, and eachelectrode 34 may be configured to sense physiological information. - Signal acquisition module 68 may further be coupled to one or more sensors configured to gather physiological information from a patient. For example,
system 10 may include one or more ofblood gas sensor 62 orpressure sensor 90. These sensors may be located in lumens ofcatheter 12, outside of the patient in fluid communication with a lumen, on an outer surface ofcatheter 12, or in any other suitable location. In one example,blood gas sensor 62 may be housed in or fluidly connected to lumen 60, whilepressure sensor 90 may be housed in or fluidly connected to lumen 58.Blood gas sensor 62 may measure the amount of O2 or CO2 in the patient's blood.Pressure sensor 90 may measure the central venous pressure (CVP) of the patient. - Signal acquisition module 68 may transmit the signals received from one or more of
electrodes 34,blood gas sensor 62, and/orpressure sensor 90 to the appropriate processing/filtering module ofsystem 10. For example, signals frompressure sensor 90 may be transmitted to a central venous pressure signal processing/filtering module 84, where the signals are processed and filtered to aid in interpretation of CVP information. Similarly, signals fromblood gas sensor 62 may be transmitted to a blood gas signal processing/filtering module 86 for processing and filtering to determine blood gas levels. Signals fromelectrodes 34, when they are used for sensing, may be sent to nerve signal processing/filtering module 80, ECG signal processing/filtering module 82, or impedance signal processing/filtering module 88, as appropriate. Signals fromelectrodes 34 or other sensors may be sent toamplification module 78, if necessary, to amplify the signals prior to being sent to the appropriate processing/filtering module. -
Controller 64 may further communicate withdisplay 74, which may serve as a user interface and may have a touch screen 18 (seeFIG. 1 ).System 10 may further include software/firmware 76, which may contain the instructions necessary for carrying out the various functions described herein. Finally,system 10 may includedata storage 79, for storing information gathered during sensing operations ofcatheter 12, and/or for storing instructions related to the operation of any of the modules or instructions for carrying out any of the functions described herein.Catheter 12 may contain unique identification features (e.g., RFID), and in the event thesystem 10 described herein (e.g., having one or more of controllers/programmers system 10 to uniquely identify each patient and access that patient's stored patient data. -
Catheter 12 may include a variety of positioning features that may help a user to positioncatheter 12 within a patient. Some positioning features may be visualization aids, such asoptical fiber camera 46 shown inFIG. 5 orultrasound transducer 54 shown inFIG. 6 . Other positioning features may be sensors to sense physiological parameters, such aspressure sensor 90.Electrodes 34, which can be used to stimulate a nerve, also may be used as sensors to gather information that can then be used to positioncatheter 12. For example,electrodes 34 may gather information related to nerve activity (e.g., the left or right phrenic nerve), ECG signals, and/or impedance. Accordingly, asensing electrode 34 may be considered a positioning feature. Each of the positioning features and how they are used to help positioncatheter 12 will be described in further detail below. -
Catheter 12 may include any combination of positioning features, including one or more visualization aids, sensors (e.g., pressure), or electrodes capable of sensing various types of information. Similarly, the control units described herein, whether on a cart, wearable on a patient, or wireless, may be configured to process information gathered by the various positioning features described herein (e.g., visualization aids, sensors, and electrodes), as well as perform the various computerized functions described herein. - Referring back to
FIG. 5 ,optical fiber camera 46 may be positioned withinextension lumen 38 and its corresponding internal lumen withincatheter 12, either temporarily or as an integral, permanent component ofcatheter 12. It should be understood thatoptical fiber camera 46 could be inserted into any of theextension lumens ports Optical fiber camera 46 may be used to aid in positioning ofcatheter 12 within the patient. For example, images fromoptical fiber camera 46 may be transmitted in real time to a health professional or other user during a procedure, who may rely on the images to guidecatheter 12 through the patient's vessels and/or to adjust the position of the catheter within the vessels. - Referring back to
FIG. 6 ,ultrasound transducer 54 may be used in addition to or instead ofoptical fiber camera 46 to obtain information useful for positioningcatheter 12 within the patient.Ultrasound transducer 54 may be secured temporarily or permanently to the exterior ofcatheter 12, as shown inFIG. 6 , or may be positioned temporarily or permanently within a lumen of catheter 12 (e.g., positioned to extend from the distal end of a lumen of catheter 12).Positioning ultrasound transducer 54 near the distal tip ofcatheter 12 may allow the user to view the inside of vessels and also ensure that the tip ofcatheter 12 is not positioned in an undesired location (e.g., in the atrium of the heart). For example,ultrasound transducer 54 may allow visualization of a heart valve, which could indicate that thecatheter 12 has entered the atrium and may need to be retracted. - In addition to allowing a user to see the inside of the patient's vessels, the ultrasound images may provide information (e.g., calculated or visual) about the diameter of blood vessels and/or blood flow within the vessels. The user may then use vessel diameter information, blood flow, and real time images of the inside of the patient's vessels to position
catheter 12 in a desired position. - CVP measurements from
pressure sensor 90 may further aid inpositioning catheter 12 within the patient. Normal values may vary between 4-12 cm H2O. The CVP waveform may change based on the location, relative to the patient's heart, of the port (e.g., 46, 48, or 50) in communication withpressure sensor 90. In one example, CVP measurements may decline as the relevant port approaches the patient's heart. A user may read the changing CVP waveforms to help position thecatheter 12 in a desired location relative to the patient's heart. - The CVP waveform has several components. The (a) wave corresponds to the right atrial contraction and correlates with the P wave on the ECG. The (c) wave corresponds to the cusp of the tricuspid valve protruding backwards through the atrium, as the right ventricle begins to contract. The (c) wave correlates with the end of the QRS complex on the ECG. The (x) descent corresponds to the movement of the right ventricle, which descends as it contracts. The downward movement decreases the pressure in the right atrium. At this stage, there is also atrial diastolic relaxation, which further decreases the right atrial pressure. The (x) descent happens before the T wave on the ECG. The (v) wave occurs as blood fills the right atrium and hits the tricuspid valve, causing a back-pressure wave. The (v) wave occurs after the T wave of the ECG. The (y) descent is a pressure decrease caused by the tricuspid valve opening in early ventricular diastole and occurs before the P wave of the ECG. The amplitudes of a, c, x, v, y may change depending on the position of the catheter with respect to the heart. The signature change of the CVP waveform can guide in the placement of
catheter 12. - In one example, a method for positioning
intravascular catheter 12 may include positioningcatheter 12 in a first position in a venous system of a patient, whereincatheter 12 includes a plurality ofelectrodes 34 and at least one lumen extending from a proximal end ofcatheter 12 to a distal end ofcatheter 12, and eachelectrode 34 of the plurality ofelectrodes 34 is configured to emit electrical signals to stimulate a nerve; measuring a central venous pressure of the patient using apressure sensor 90 fluidly connected to the at least one lumen; and based on the central venous pressure, adjustingcatheter 12 to a second position different from the first position. - Nerve signals acquired by
electrodes 34 also may be used to aid inpositioning catheter 12 within a patient. The electrical signal from a nerve may be amplified byamplification module 78 and processed by nerve signal processing/filtering module 80. The amplified and filtered signals from one ormore electrodes 34 then may be compared to an expected signal from the targeted nerve (e.g., left or right phrenic nerve) to identifyelectrodes 34 in close proximity to the target nerve and to identify the optimal one or more electrodes for nerve stimulation. For example,electrodes 34 returning a higher strength and/or higher quality signal may be located closer to the target nerve. - More specifically, phrenic nerve activity can be recorded using bipolar or monopolar electrodes. Phrenic nerve discharge can be amplified and filtered (e.g., 100 Hz to 5 kHz), and a moving average can be obtained using a third-order Paynter filter with a 20 or 50 ms time constant. Phrenic nerve discharge also can be filtered at 10 Hz to 5 kHz for analysis of spectral composition. A sampling rate of 1-10 kHz can be used to capture the nerve activity.
- The parameters acquired during nerve activity sensing can be used to detect if the signal is from the phrenic nerve or another nerve. Sensed parameters can include a number of physiological parameters, such as amplitude, inspiration duration, and/or breathing rate. For example, if the sensed amplitude shows proximity of the
electrodes 34 to the nerve and the nerve is a phrenic nerve, the duration of pulses in a train should match the sensed inspiration duration, and the frequency of the trains should match the sensed breathing rate. Furthermore, the sensed signals from a nerve can be compared to known nerve signatures (e.g., of phrenic nerves) to confirm that the nerve signal is from the desired nerve. - Electrodes 34 (e.g., two or three) may be used to acquire ECG signals, with
hub 36 optionally being used as a reference electrode. The ECG signal (e.g., morphology, amplitudes, and spectral content) may vary depending on the location, relative to the patient's heart, of the electrodes being used to measure the signal. Monitoring changes in the ECG signal ascatheter 12 is being positioned may aid in identifying desired or undesired placement. For example, it may be undesired forcatheter 12 to be placed in the atrium of the patient's heart. - In one example, one of the
distal electrodes 34 oncatheter 12 may be designated as a probe. Other electrodes along the length ofcatheter 12, and in some cases in contact with the skin of the patient, may be used to detect an ECG signal, which can optionally be displayed bycontrol unit 14 viascreen 18.Catheter 12 may be advanced throughsuperior vena cava 24 towards the heart. Ascatheter 12 enters a region proximate the right atrium, or enters the right atrium, the P-wave portion of the ECG may become elevated and create an augmented peaked P-wave, indicating that the tip of thecatheter 12 lies in or very close to the right atrium. The operator can observe the change in P-wave, or thecontrol unit 14 can utilize an algorithm to detect the change and provide a visual, audible or other signal to the operator. For example, an LED oncatheter hub 36,control unit 14, orremote controller 16 can change from green to yellow and then to red as the P-wave changes indicate that thecatheter 12 is approaching and then is positioned within the right atrium. Thecatheter 12 can then be withdrawn slowly until the P-wave starts to diminish. Thecatheter 12 can then be withdrawn a further 1-2 cm, thereby positioning the catheter tip in the distal portion ofsuperior vena cava 24. - In this example, the positive deflection in the P-wave occurs when current flows to the probing electrode, and a negative deflection when it flows away. The P-wave depolarizes down the right atrium from the SA node, away from an
electrode 34 insuperior vena cava 24, and is therefore negative. The amplitude of the P-wave is related to the inverse square rule, whereby the amplitude is inversely proportional to the square of the distance from the current source. Thus, the P-wave increases greatly in negative amplitude ascatheter 12 approaches the atrium. When the tip enters the atrium, it is just beyond the SA node, and the first portion of the P-wave depolarizes towards it. This results in a brief, small positive deflection followed instantly by a deep negative deflection. - Alternatively, a distal combination of electrodes 34 (e.g., a distal pair) and a proximal combinations of electrodes 34 (e.g., a proximal pair) can be used to obtain, respectively, a distal and proximal ECG signal having a P-wave. The P-waves can be compared using standard signal processing techniques and a delta value can be determined as the
catheter 12 is advanced through the vessel (e.g. superior vena cava 24) towards the heart. Ascatheter 12 is advanced in close proximity to or into the atrium, the delta value will change significantly, exceeding a predetermined value. Thesystem 10 can provide an indicator to the operator, as described previously, andcatheter 12 can be withdrawn 1 to 2 cm. This method can also utilize one ormore reference electrodes 34 located along the length of the catheter or positioned externally on the patient's body. -
Electrodes 34 also may be used to measure impedance, which can provide information relevant topositioning catheter 12. Impedance may be measured between any twoelectrodes 34 ofcatheter 12. In one example, however, impedance may be measured between: a) either aproximal-most electrode 34 orhub 36, and b) a distal-most electrode. - The impedance presented to injected current may be dependent on the conductivity of the fluid, or adjacent tissue, in the local area between a pair of
sensing electrodes 34. The conductivity further may depend on the cross-sectional area of the blood vessel at the site of the sendingelectrodes 34. The impedance of anelectrode 34 may vary depending on the medium in which it is resting. For example, anelectrode 34 placed in a relatively large body of conductive fluid may have a lower impedance than one resting against a vessel wall. The impedance of anelectrode 34 can therefore be used to determine whether it is adjacent to a vessel wall or resting in a larger body of conductive fluid. - In one example, when
catheter 12 is inserted into a patient,electrodes 34 that are on a proximal portion ofcatheter 12 may have a higher impedance thanother electrodes 34, because the proximal portion ofcatheter 12 may be positioned in tissue (e.g., fatty) near an insertion site, rather than resting in the fluid of a blood vessel.Electrodes 34 farther down the shaft ofcatheter 12, towards a central portion ofcatheter 12, might have progressively lower impedances as the diameter of the vessel increases (e.g., as the vessel approaches superior vena cava 24).Electrodes 34 on the portion ofcatheter 12 that is floating in fluid insuperior vena cava 24 might have a low impedance.Electrodes 34 on the distal portion ofcatheter 12, at or near the tip ofcatheter 12, might be in direct contact with the vessel wall and therefore may have a higher impedance. A graph of the impedances of all of theelectrodes 34 in this example may have a U-shaped curvature, as impedances may be higher at each end ofcatheter 12 and lower towards the central portion ofcatheter 12. The change in impedance of anelectrode 34 as it progresses through the patient's vessels can provide information about the location of thatelectrode 34. In addition, the differences in impedances ofelectrodes 34 along the length ofcatheter 12 may provide information about the placement ofcatheter 12. - In one example,
catheter 12 may be placed in a vessel that varies in diameter, withdistal electrodes 34 resting in a desired vessel (e.g., in superior vena cava 24). The impedances of different, more proximal electrodes would be expected to vary depending on their position in the venous system. In one example,catheter 12, when placed in a desired position, would be expected to include: 1)electrodes 34 whose impedances are reduced as theelectrodes 34 approach the wall of a vessel (e.g., superior vena cava 24); and 2)electrodes 34 having impedance profiles with a desired shape. In one example, measured impedances may be compared to impedance thresholds or profiles stored indata storage 79, to determine if one ormore electrodes 34 are properly placed. - In another example, the impedances of distal electrodes can be compared to the impedances of proximal electrodes as the
catheter 12 is advanced throughsuperior vena cava 24 towards the atrium. As the distal electrodes enter the atrium, the difference between the distal and proximal impedance measurements may exceed a predetermined threshold allowing thesystem 10 to provide an indication to the operator.Catheter 12 can then be withdrawn (or advanced depending on the application) to the desired location. Signal filtering, processing, and analytical techniques known in the art can be used to assess the impedance measurements in real time. - A
catheter 12 that is under-inserted may have few or noelectrodes 34 resting in the desired vessel (e.g., superior vena cava 24), which would result in electrode impedance profiles having different shapes than the desired shape. In addition, acatheter 12 that is over-inserted may have one ormore electrodes 34 that are close to, or in contact with, the atrium, which may also result in impedance profiles having different shapes than the desired shape. In one example, the impedance of one ormore electrodes 34 is monitored ascatheter 12 is inserted into the patient andelectrodes 34 move through the patient's venous system. Changes in the impedance profiles can be displayed to the health professional performing the insertion, and the impedance profiles can be used to confirm proper placement ofcatheter 12. - In one example, a method for positioning
intravascular catheter 12 may include positioningcatheter 12 in a first position in a venous system of a patient, whereincatheter 12 includes a plurality ofelectrodes 34, and eachelectrode 34 of the plurality ofelectrodes 34 is configured to emit electrical signals to stimulate a phrenic nerve; measuring an impedance between afirst electrode 34 of the plurality ofelectrodes 34 and a second electrode; and based on the measured impedance, adjustingcatheter 12 to a second position different from the first position. - In other examples,
catheter 12 may include a strain gauge and/or an accelerometer (not shown). Either the strain gauge or the accelerometer may be placed at or near the distal end ofcatheter 12, in one of the lumens. The strain gauge could detect flex in a distal portion ofcatheter 12, and the accelerometer could detect movement/acceleration of the distal portion ofcatheter 12. Information from the strain gauge and/or accelerometer could be used to determine whether the distal end ofcatheter 12 is in the atrium (e.g., heartbeats may cause movement of the distal end of catheter 12). The strain gauge or the accelerometer could be an integral, permanent part ofcatheter 12 or could be positioned in a lumen ofcatheter 12 temporarily during positioning ofcatheter 12. - Nerve signals acquired by sensing
electrodes 34 may be used to selectelectrodes 34 for nerve stimulation.Electrodes 34 that are closer to a target nerve may sense nerve activity having a higher amplitude, whileelectrodes 34 that are farther from a target nerve may sense nerve activity having a lower amplitude. If a greater diaphragm response is desired,electrodes 34 that are closer to the nerve, as determined based on received nerve activity signals, may be selected for nerve stimulation. In other cases, if less diaphragm response is desired,electrodes 34 that are farther from the nerve, as determined based on received nerve activity signals, may be selected for nerve stimulation. - Typical nerve signals for, e.g., phrenic nerves, follow a pattern that has distinct characteristics (e.g., spectral characteristics and modulation over time). To select
electrodes 34 for nerve stimulation, the sensed nerve signals fromdifferent electrodes 34 can be analyzed for their spectral and temporal characteristics. Ofelectrodes 34 having sensed signal patterns matching typical phrenic nerve activity, theoptimal electrodes 34 can be selected based on the amplitude of the signal and how strongly the signal correlates to the typical pattern. In one example, a fast Fourier transform can be used to provide a correlation factor to a reference signal in near real-time. In another example, the sensed signals can be frequency filtered in the frequency range of interest, based on the typical characteristics of the phrenic nerve signal, and then analyzed over time to observe periods or bursts of activity in the frequency range of interest. - In one example, a method for selecting one or more electrodes for nerve stimulation may include inserting
intravascular catheter 12 into: a) at least one of leftsubclavian vein 22 or leftjugular vein 32, and b)superior vena cava 24, whereincatheter 12 includes a plurality ofelectrodes 34, and eachelectrode 34 of the plurality ofelectrodes 34 is configured to emit electrical signals to stimulate a nerve; using one ormore electrodes 34 of the plurality ofelectrodes 34 to acquire an electrical signal emitted from the nerve; based on the acquired electrical signal, selecting anelectrode 34 or an electrode combination for a nerve stimulation; and using the selectedelectrode 34 or electrode combination, stimulating the nerve. - The processed nerve activity waveforms additionally may be used to determine parameters for nerve stimulation. The processed waveforms may provide information regarding intrinsic breath rate (e.g., if the patient is attempting to breathe on his/her own) and nerve signal amplitude. The stimulation parameters may be adjusted based on the breath rate of previous stimulated breaths (e.g., to increase or decrease the breath rate, as sensed by the sensing electrodes) and nerve activity resulting from stimulation during previous breaths (e.g., to increase or decrease the strength of stimulation). Various parameters that may be adjusted include stimulation pulse amplitude, stimulation pulse width, stimulation pulse frequency, stimulation duration, and the interval between stimulations/pulse trains (e.g., stimulated breath rate). Accordingly, sensed nerve activity signals may be used to determine and adjust the nerve stimulation parameters in a closed-loop system.
- Impedance information may be used to determine a breath rate of the patient in order to adjust nerve stimulation parameters (e.g., stimulation pulse amplitude, stimulation pulse width, stimulation pulse frequency, stimulation duration, and the interval between stimulations/pulse trains (e.g., stimulated breath rate)). Electrical impedance of lung tissue changes as a function of air content. Accordingly, the electrical impedance of the thorax changes during inhalation and exhalation. The thorax presents an electrical impedance that includes two components: a relatively constant value and a varying value. Changes in impedance may result from the following two effects during inspiration: 1) there is an increase in the gas volume of the chest in relation to the fluid volume, which may cause conductivity to decrease, and 2) the length of the conductance path (e.g., between two electrodes) increases when the lungs expand. These effects may cause impedance to increase during inspiration. There is an approximately linear correlation between the impedance changes and the volume of respirated air. The varying component of impedance (i.e., respirative impedance) generates a varying voltage component when current is injected (e.g., by electrodes 34). This varying voltage component can then be used to determine the person's breathing rate.
- Information from
blood gas sensor 62 may be used by a health professional, or bycontroller 64, to adjust stimulation parameters. For example, if blood O2 levels are low (or blood CO2 levels are high)controller 64 may send a signal toelectrodes 34 to emit stimulation signals having a higher charge (amplitude×pulse width) or frequency, and may stimulate a sigh breath. Conversely, if blood O2 levels are high (or blood CO2 levels are low),controller 64 may causeelectrodes 34 to emit stimulation signals having a lower charge or frequency. Based on information fromblood gas sensor 62, the following parameters can be adjusted: stimulation pulse amplitude, stimulation pulse width, stimulation pulse frequency, stimulation duration, and the interval between stimulations/pulse trains (e.g., stimulated breath rate). - For any of the parameter adjustments described herein, increasing stimulation pulse amplitude, width and/or frequency may increase lung volume during a stimulated breath. Increasing stimulation duration may increase lung volume and/or increase the amount of time air remains in the lungs during a stimulated breath, allowing for an extended gas exchange period. Increasing the stimulated breath rate may allow for additional gas exchange periods over a given period of time, which may increase the amount and/or speed of gas exchange.
- The
system 10 andcatheter 12 described herein may include any combination of sensing features. For example,catheter 12 may be configured to sense ECG, impedance, nerve activity, blood gas levels, and CVP, and thesystem 10 may be configured to positioncatheter 12,select electrodes 34 for stimulation, and select stimulation parameters based on one or more types of information received by sensors orelectrodes 34. - Accordingly, the various visualization and sensing functions of
system 10 may assist a user in one or more of positioning a transvascular catheter, selecting optimal electrodes for nerve stimulation, or selecting or adjusting parameters for nerve stimulation. - While principles of the present disclosure are described herein with reference to illustrative embodiments for particular applications, it should be understood that the disclosure is not limited thereto. Those having ordinary skill in the art and access to the teachings provided herein will recognize additional modifications, applications, embodiments, and substitution of equivalents all fall within the scope of the embodiments described herein. Accordingly, the invention is not to be considered as limited by the foregoing description.
Claims (30)
1. A method for positioning an intravascular catheter, comprising:
inserting the intravascular catheter into a venous system of a patient, wherein the catheter includes a plurality of electrodes, and multiple electrodes of the plurality of electrodes are configured to emit electrical signals;
positioning a distal portion of the catheter in a first position;
using one or more electrodes of the plurality of electrodes to acquire a first ECG signal and a second ECG signal;
determining a difference between the first ECG signal and the second ECG signal;
comparing the difference to a value;
based on the comparison of the difference to the value, adjusting the distal portion of the catheter to a second position different from the first position;
identifying at least one first electrode of the plurality of electrodes to stimulate a first nerve;
identifying at least one second electrode of the plurality of electrodes to stimulate a second nerve; and
stimulating at least one of the first and second nerves to cause a contraction of a respiratory muscle.
2. The method of claim 1 , wherein inserting the intravascular catheter into the venous system includes inserting the intravascular catheter into: 1) at least one of a left subclavian, axillary, cephalic, cardiophrenic, brachial, radial, or left jugular vein, and 2) a superior vena cava.
3. The method of claim 1 , wherein the first position is proximate an atrium of a heart of the patient, and the second position is in a superior vena cava.
4. (canceled)
5. The method of claim 1 , wherein the first ECG signal is acquired by one or more electrodes that are positioned on a proximal portion of the catheter and are configured to stimulate the first nerve, and the second ECG signal is acquired by one or more electrodes that are positioned on a distal portion of the catheter and are configured to stimulate the second nerve.
6. (canceled)
7. The method of claim 1 , wherein the second position is farther from a heart of the patient than the first position.
8. The method of claim 1 , further comprising using one or more electrodes of the plurality of electrodes to sense at least one of an impedance or nerve activity.
9. The method of claim 1 , wherein each of the at least one first electrode and the at least one second electrode is a combination of electrodes.
10. A method for positioning an intravascular catheter, comprising:
inserting the intravascular catheter into: 1) at least one of a left subclavian vein or a left jugular vein, and 2) a superior vena cava, wherein the catheter includes a plurality of electrodes, and the plurality of electrodes includes a proximal set of electrodes positioned proximate a left phrenic nerve and a distal set of electrodes positioned proximate a right phrenic nerve;
using one or more electrodes of the plurality of electrodes to acquire a first ECG signal and a second ECG signal;
determining a difference between the first ECG signal and the second ECG signal;
comparing the difference to a value;
based on the comparison of the difference to the value, withdrawing the catheter away from a heart of a patient;
stimulating the left phrenic nerve using one or more electrodes of the proximal set of electrodes; and
stimulating the right phrenic nerve using one or more electrodes of the distal set of electrodes.
11. (canceled)
12. The method of claim 10 , wherein the step of withdrawing the catheter away from the heart causes a change in an amplitude of a P-wave of the first ECG signal or the second ECG signal.
13. The method of claim 10 , wherein the first ECG signal is acquired by one or more electrodes of the proximal set of electrodes, and the second ECG signal is acquired by one or more electrodes of the distal set of electrodes.
14. The method of claim 10 , a wherein the difference between the first ECG signal and the second ECG signal is a difference between a P-wave of the first ECG signal and a P-wave of the second ECG signal.
15. The method of claim 10 , wherein the difference exceeds the value when the catheter is advanced into an atrium of the heart.
16. The method of claim 10 , wherein a hub coupled to the catheter and positioned exterior to the patient is used with the one or more electrodes of the plurality of electrodes to acquire the ECG signal.
17. The method of claim 10 , further comprising monitoring the first ECG signal and the second ECG signal as a distal end of the catheter is inserted into the at least one of the left subclavian vein or the left jugular vein and advanced into the superior vena cava.
18. A method for positioning an intravascular catheter, comprising:
inserting the intravascular catheter into a venous system of a patient, wherein the catheter includes a plurality of proximal electrodes and a plurality of distal electrodes;
using one or more electrodes of the plurality of proximal electrodes to acquire a first ECG signal, and using one or more electrodes of the plurality of distal electrodes to acquire a second ECG signal;
determining a difference between the first ECG signal and the second ECG signal;
comparing the difference to a value;
based on the comparison of the difference to the value, adjusting a position of the catheter;
stimulating the first nerve using one or more of the plurality of proximal electrodes; and
stimulating the second nerve using one or more of the plurality of distal electrodes.
19. The method of claim 18 , wherein the first nerve is a left phrenic nerve, and the second nerve is a right phrenic nerve.
20. The method of claim 18 , wherein the difference between the first ECG signal and the second ECG signal is a difference between an amplitude of a portion of the first ECG signal and an amplitude of a portion of the second ECG signal.
21. The method of claim 18 , wherein the steps of determining the difference and comparing occur a plurality of times during the inserting step.
22. The method of claim 18 , wherein adjusting the position of the catheter includes moving the catheter away from a heart.
23. The method of claim 18 , wherein at least one of stimulating the first nerve or stimulating the second nerve causes a contraction of a diaphragm.
24. The method of claim 18 , further comprising sensing activity of the first nerve using one or more of the proximal electrodes and sensing activity of the second nerve using one or more of the distal electrodes.
25. A method for positioning an intravascular catheter, comprising:
inserting the intravascular catheter into: 1) at least one of a left subclavian vein or a left jugular vein, and 2) a superior vena cava, wherein the catheter includes a plurality of proximal electrodes configured to be positioned proximate a left phrenic nerve and a plurality of distal electrodes configured to be positioned proximate a right phrenic nerve;
at multiple positions of the catheter during the inserting step, using one or more electrodes of the plurality of proximal electrodes to acquire a first ECG signal, and using one or more electrodes of the plurality of distal electrodes to acquire a second ECG signal;
determining a difference between the first ECG signal and the second ECG signal at several of the multiple positions;
comparing each difference to a value;
based on the comparisons of each difference to the value, determining a desired position of the catheter for nerve stimulation;
stimulating the left phrenic nerve using one or more of the plurality of proximal electrodes; and
stimulating the right phrenic nerve using one of more of the plurality of distal electrodes.
26. The method of claim 25 , further comprising advancing a distal end of the catheter into a region proximate an atrium of a heart.
27. The method of claim 26 , wherein one of the multiple positions is a position in which the distal end of the catheter is proximate the atrium of the heart, and in the position, the comparison indicates a difference between an amplitude of the first ECG signal and an amplitude of the second ECG signal that exceeds the value.
28. The method of claim 27 , further comprising moving the catheter away from the heart.
29. The method of claim 25 , wherein stimulating the left phrenic nerve causes a diaphragm contraction, and stimulating the right phrenic nerve causes a diaphragm contraction.
30. The method of claim 25 , wherein the proximal electrodes used to acquire the first ECG signal are configured to stimulate the left phrenic nerve, and the distal electrodes used to acquire the second ECG signal are configured to stimulate the right phrenic nerve.
Priority Applications (10)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US15/666,989 US10195429B1 (en) | 2017-08-02 | 2017-08-02 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US15/704,439 US10039920B1 (en) | 2017-08-02 | 2017-09-14 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
PCT/US2018/043661 WO2019027757A2 (en) | 2017-08-02 | 2018-07-25 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
EP18752951.6A EP3661589A2 (en) | 2017-08-02 | 2018-07-25 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
CN201880062545.1A CN111225710A (en) | 2017-08-02 | 2018-07-25 | Systems and methods for intravascular catheter positioning and/or neural stimulation |
JP2020505459A JP7175027B2 (en) | 2017-08-02 | 2018-07-25 | Systems and methods for intravascular catheter placement and/or nerve stimulation |
AU2018309630A AU2018309630A1 (en) | 2017-08-02 | 2018-07-25 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US16/222,299 US11090489B2 (en) | 2017-08-02 | 2018-12-17 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US16/802,711 US10926087B2 (en) | 2017-08-02 | 2020-02-27 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US17/371,316 US20210330968A1 (en) | 2017-08-02 | 2021-07-09 | Intravascular catheter methods |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US15/666,989 US10195429B1 (en) | 2017-08-02 | 2017-08-02 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
Related Child Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US15/704,439 Continuation US10039920B1 (en) | 2017-08-02 | 2017-09-14 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US16/222,299 Continuation US11090489B2 (en) | 2017-08-02 | 2018-12-17 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
Publications (2)
Publication Number | Publication Date |
---|---|
US10195429B1 US10195429B1 (en) | 2019-02-05 |
US20190038897A1 true US20190038897A1 (en) | 2019-02-07 |
Family
ID=63013876
Family Applications (5)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US15/666,989 Active US10195429B1 (en) | 2017-08-02 | 2017-08-02 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US15/704,439 Active US10039920B1 (en) | 2017-08-02 | 2017-09-14 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US16/222,299 Active 2037-08-30 US11090489B2 (en) | 2017-08-02 | 2018-12-17 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US16/802,711 Active US10926087B2 (en) | 2017-08-02 | 2020-02-27 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US17/371,316 Pending US20210330968A1 (en) | 2017-08-02 | 2021-07-09 | Intravascular catheter methods |
Family Applications After (4)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US15/704,439 Active US10039920B1 (en) | 2017-08-02 | 2017-09-14 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US16/222,299 Active 2037-08-30 US11090489B2 (en) | 2017-08-02 | 2018-12-17 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US16/802,711 Active US10926087B2 (en) | 2017-08-02 | 2020-02-27 | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
US17/371,316 Pending US20210330968A1 (en) | 2017-08-02 | 2021-07-09 | Intravascular catheter methods |
Country Status (6)
Country | Link |
---|---|
US (5) | US10195429B1 (en) |
EP (1) | EP3661589A2 (en) |
JP (1) | JP7175027B2 (en) |
CN (1) | CN111225710A (en) |
AU (1) | AU2018309630A1 (en) |
WO (1) | WO2019027757A2 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2022179976A1 (en) * | 2021-02-23 | 2022-09-01 | B. Braun Melsungen Ag | Method for checking a position and/or an orientation of a catheter tip of a catheter |
Families Citing this family (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP3228351B1 (en) | 2012-03-05 | 2019-06-05 | Lungpacer Medical Inc. | Transvascular nerve stimulation apparatus |
CN104684614B (en) | 2012-06-21 | 2017-10-17 | 西蒙·弗雷泽大学 | The diaphragm pacing system and application method of intravascular |
EP4115942B1 (en) | 2017-06-30 | 2024-04-24 | Lungpacer Medical Inc. | System for prevention, moderation, and/or treatment of cognitive injury |
US10195429B1 (en) | 2017-08-02 | 2019-02-05 | Lungpacer Medical Inc. | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
EP3877043A4 (en) | 2018-11-08 | 2022-08-24 | Lungpacer Medical Inc. | Stimulation systems and related user interfaces |
EP3934746A1 (en) * | 2019-03-04 | 2022-01-12 | Boston Scientific Neuromodulation Corporation | User-weighted closed loop adjustment of neuromodulation treatment |
WO2020232333A1 (en) | 2019-05-16 | 2020-11-19 | Lungpacer Medical Inc. | Systems and methods for sensing and stimulation |
EP3983057A4 (en) | 2019-06-12 | 2023-07-12 | Lungpacer Medical Inc. | Circuitry for medical stimulation systems |
CN112451854A (en) * | 2020-12-01 | 2021-03-09 | 中国康复研究中心 | Implanted diaphragm pacemaker and control method thereof |
DE102021110445A1 (en) | 2021-02-17 | 2022-09-01 | Stimit Ag | Stimulation methods for electromagnetically or electrically controlled self-respiration |
WO2023194399A1 (en) * | 2022-04-08 | 2023-10-12 | Koninklijke Philips N.V. | Electrical traces along core wire for intraluminal physiology sensing guidewire and associated devices, systems, and methods |
Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8706235B2 (en) * | 2011-07-27 | 2014-04-22 | Medtronic, Inc. | Transvenous method to induce respiration |
Family Cites Families (487)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1693734A (en) | 1923-06-29 | 1928-12-04 | Mcintosh Electrical Corp | Switching means for effecting electrotherapeutic treatment |
US2532788A (en) | 1948-01-03 | 1950-12-05 | Stanley J Sarnoff | Artificial respiration by electronic stimulation |
US2664880A (en) | 1951-11-23 | 1954-01-05 | Jr Nathaniel B Wales | Electric stimulator for artificial respiration |
US3348548A (en) | 1965-04-26 | 1967-10-24 | William M Chardack | Implantable electrode with stiffening stylet |
US3470876A (en) | 1966-09-28 | 1969-10-07 | John Barchilon | Dirigible catheter |
US3835864A (en) | 1970-09-21 | 1974-09-17 | Rasor Ass Inc | Intra-cardiac stimulator |
US3769984A (en) | 1971-03-11 | 1973-11-06 | Sherwood Medical Ind Inc | Pacing catheter with frictional fit lead attachment |
US3817241A (en) | 1972-02-16 | 1974-06-18 | Henry And Carol Grausz | Disposable central venous catheter and method of use |
US3938502A (en) | 1972-02-22 | 1976-02-17 | Nicolaas Bom | Apparatus with a catheter for examining hollow organs or bodies with the ultrasonic waves |
US3804098A (en) | 1972-04-17 | 1974-04-16 | Medronic Inc | Body implantable lead |
US3896373A (en) | 1972-11-30 | 1975-07-22 | Stein Paul D | Method and apparatus for determining cross-sectional area of a blood conduit and volumetric flow therethrough |
US3847157A (en) | 1973-06-18 | 1974-11-12 | J Caillouette | Medico-surgical tube |
US3851641A (en) | 1973-11-29 | 1974-12-03 | J Toole | Method and apparatus for determining internal impedance of animal body part |
US3983881A (en) | 1975-05-21 | 1976-10-05 | Telectronics Pty. Limited | Muscle stimulator |
US4054881A (en) | 1976-04-26 | 1977-10-18 | The Austin Company | Remote object position locater |
US4114601A (en) | 1976-08-09 | 1978-09-19 | Micro Tec Instrumentation, Inc. | Medical and surgical implement detection system |
US4072146A (en) | 1976-09-08 | 1978-02-07 | Howes Randolph M | Venous catheter device |
USRE31873F1 (en) | 1976-09-08 | 1988-11-15 | Venous catheter device | |
US4143872A (en) | 1977-04-07 | 1979-03-13 | Hudson Oxygen Therapy Sales Company | Lung volume exerciser |
US4173228A (en) | 1977-05-16 | 1979-11-06 | Applied Medical Devices | Catheter locating device |
US4249539A (en) | 1979-02-09 | 1981-02-10 | Technicare Corporation | Ultrasound needle tip localization system |
US4317078A (en) | 1979-10-15 | 1982-02-23 | Ohio State University Research Foundation | Remote position and orientation detection employing magnetic flux linkage |
US4380237A (en) | 1979-12-03 | 1983-04-19 | Massachusetts General Hospital | Apparatus for making cardiac output conductivity measurements |
US4643201A (en) | 1981-02-02 | 1987-02-17 | Medtronic, Inc. | Single-pass A-V lead |
US4416289A (en) | 1981-05-07 | 1983-11-22 | Mccormick Laboratories, Inc. | Circuits for determining very accurately the position of a device inside biological tissue |
US4431005A (en) | 1981-05-07 | 1984-02-14 | Mccormick Laboratories, Inc. | Method of and apparatus for determining very accurately the position of a device inside biological tissue |
US4445501A (en) | 1981-05-07 | 1984-05-01 | Mccormick Laboratories, Inc. | Circuits for determining very accurately the position of a device inside biological tissue |
US4407294A (en) | 1982-01-07 | 1983-10-04 | Technicare Corporation | Ultrasound tissue probe localization system |
US4431006A (en) | 1982-01-07 | 1984-02-14 | Technicare Corporation | Passive ultrasound needle probe locator |
US4681117A (en) | 1983-02-15 | 1987-07-21 | Brodman Richard F | Intracardiac catheter and a method for detecting myocardial ischemia |
US4573481A (en) | 1984-06-25 | 1986-03-04 | Huntington Institute Of Applied Research | Implantable electrode array |
US4586923A (en) | 1984-06-25 | 1986-05-06 | Cordis Corporation | Curving tip catheter |
US4587975A (en) | 1984-07-02 | 1986-05-13 | Cardiac Pacemakers, Inc. | Dimension sensitive angioplasty catheter |
US4697595A (en) | 1984-07-24 | 1987-10-06 | Telectronics N.V. | Ultrasonically marked cardiac catheters |
YU132884A (en) | 1984-07-26 | 1987-12-31 | Branko Breyer | Electrode cateter with ultrasonic marking |
US4674518A (en) | 1985-09-06 | 1987-06-23 | Cardiac Pacemakers, Inc. | Method and apparatus for measuring ventricular volume |
US4683890A (en) | 1985-12-23 | 1987-08-04 | Brunswick Manufacturing Co., Inc. | Method and apparatus for controlled breathing employing internal and external electrodes |
US4827935A (en) | 1986-04-24 | 1989-05-09 | Purdue Research Foundation | Demand electroventilator |
US4771788A (en) | 1986-07-18 | 1988-09-20 | Pfizer Hospital Products Group, Inc. | Doppler tip wire guide |
US4852580A (en) | 1986-09-17 | 1989-08-01 | Axiom Medical, Inc. | Catheter for measuring bioimpedance |
US4830008A (en) | 1987-04-24 | 1989-05-16 | Meer Jeffrey A | Method and system for treatment of sleep apnea |
US4819662A (en) | 1987-10-26 | 1989-04-11 | Cardiac Pacemakers, Inc. | Cardiac electrode with drug delivery capabilities |
US4860769A (en) | 1987-11-12 | 1989-08-29 | Thomas J. Fogarty | Implantable defibrillation electrode |
CA1330285C (en) | 1987-12-22 | 1994-06-21 | Geoffrey S. Martin | Triple lumen catheter |
US4840182A (en) | 1988-04-04 | 1989-06-20 | Rhode Island Hospital | Conductance catheter |
US4944088A (en) | 1988-05-25 | 1990-07-31 | Medtronic, Inc. | Ring electrode for multiconductor pacing leads |
US4951682A (en) | 1988-06-22 | 1990-08-28 | The Cleveland Clinic Foundation | Continuous cardiac output by impedance measurements in the heart |
US4905698A (en) | 1988-09-13 | 1990-03-06 | Pharmacia Deltec Inc. | Method and apparatus for catheter location determination |
US4911174A (en) | 1989-02-13 | 1990-03-27 | Cardiac Pacemakers, Inc. | Method for matching the sense length of an impedance measuring catheter to a ventricular chamber |
US4957110A (en) | 1989-03-17 | 1990-09-18 | C. R. Bard, Inc. | Steerable guidewire having electrodes for measuring vessel cross-section and blood flow |
US4934049A (en) | 1989-07-07 | 1990-06-19 | Medtronic, Inc. | Method for fabrication of a medical electrode |
US4989617A (en) | 1989-07-14 | 1991-02-05 | Case Western Reserve University | Intramuscular electrode for neuromuscular stimulation system |
US5036848A (en) | 1989-10-16 | 1991-08-06 | Brunswick Biomedical Technologies, Inc. | Method and apparatus for controlling breathing employing internal and external electrodes |
US5005587A (en) | 1989-11-13 | 1991-04-09 | Pacing Systems, Inc. | Braid Electrode leads and catheters and methods for using the same |
US5254088A (en) | 1990-02-02 | 1993-10-19 | Ep Technologies, Inc. | Catheter steering mechanism |
US5042143A (en) | 1990-02-14 | 1991-08-27 | Medtronic, Inc. | Method for fabrication of implantable electrode |
US5115818A (en) | 1990-02-14 | 1992-05-26 | Medtronic, Inc. | Implantable electrode |
CH681351A5 (en) | 1990-04-12 | 1993-03-15 | Hans Baer Dr | |
US5265604A (en) | 1990-05-14 | 1993-11-30 | Vince Dennis J | Demand - diaphragmatic pacing (skeletal muscle pressure modified) |
US5056519A (en) | 1990-05-14 | 1991-10-15 | Vince Dennis J | Unilateral diaphragmatic pacer |
US5383923A (en) | 1990-10-20 | 1995-01-24 | Webster Laboratories, Inc. | Steerable catheter having puller wire with shape memory |
DE9015857U1 (en) | 1990-11-21 | 1991-02-07 | B. Braun Melsungen Ag, 3508 Melsungen, De | |
US5224491A (en) | 1991-01-07 | 1993-07-06 | Medtronic, Inc. | Implantable electrode for location within a blood vessel |
US5170802A (en) | 1991-01-07 | 1992-12-15 | Medtronic, Inc. | Implantable electrode for location within a blood vessel |
US5345936A (en) | 1991-02-15 | 1994-09-13 | Cardiac Pathways Corporation | Apparatus with basket assembly for endocardial mapping |
US5465717A (en) | 1991-02-15 | 1995-11-14 | Cardiac Pathways Corporation | Apparatus and Method for ventricular mapping and ablation |
US5456254A (en) | 1991-02-15 | 1995-10-10 | Cardiac Pathways Corp | Flexible strip assembly having insulating layer with conductive pads exposed through insulating layer and device utilizing the same |
US5146918A (en) | 1991-03-19 | 1992-09-15 | Medtronic, Inc. | Demand apnea control of central and obstructive sleep apnea |
US5184621A (en) | 1991-05-29 | 1993-02-09 | C. R. Bard, Inc. | Steerable guidewire having electrodes for measuring vessel cross-section and blood flow |
JP2582010B2 (en) | 1991-07-05 | 1997-02-19 | 芳嗣 山田 | Monitoring device for respiratory muscle activity |
US5241957A (en) | 1991-11-18 | 1993-09-07 | Medtronic, Inc. | Bipolar temporary pacing lead and connector and permanent bipolar nerve wire |
US5324322A (en) | 1992-04-20 | 1994-06-28 | Case Western Reserve University | Thin film implantable electrode and method of manufacture |
US5843028A (en) | 1992-05-11 | 1998-12-01 | Medical Innovations Corporation | Multi-lumen endoscopic catheter |
US5411025A (en) | 1992-06-30 | 1995-05-02 | Cordis Webster, Inc. | Cardiovascular catheter with laterally stable basket-shaped electrode array |
DE69315704T3 (en) | 1992-10-01 | 2002-08-01 | Cardiac Pacemakers Inc | STENT-LIKE STRUCTURE FOR DEFLICTION ELECTRODES |
JP3526598B2 (en) | 1992-12-04 | 2004-05-17 | シー・アール・バード・インコーポレーテッド | Catheter and independent handle / actuator for independent proximal and distal control |
US5368564A (en) | 1992-12-23 | 1994-11-29 | Angeion Corporation | Steerable catheter |
US5330522A (en) | 1992-12-29 | 1994-07-19 | Siemens Pacesetter, Inc. | Ring electrode for a multilumen lead and method of constructing a multilumen lead |
US5706809A (en) | 1993-01-29 | 1998-01-13 | Cardima, Inc. | Method and system for using multiple intravascular sensing devices to detect electrical activity |
US5813399A (en) | 1993-03-16 | 1998-09-29 | Puritan Bennett Corporation | System and method for closed loop airway pressure control during the inspiratory cycle of a breath in a patient ventilator using the exhalation valve as a microcomputer-controlled relief valve |
WO1994027603A1 (en) | 1993-06-01 | 1994-12-08 | Cortex Pharmaceuticals, Inc. | Alkaline and acid phosphatase inhibitors in treatment of neurological disorders |
US5348536A (en) | 1993-08-02 | 1994-09-20 | Quinton Instrument Company | Coextruded catheter and method of forming |
US5607462A (en) | 1993-09-24 | 1997-03-04 | Cardiac Pathways Corporation | Catheter assembly, catheter and multi-catheter introducer for use therewith |
US5486159A (en) | 1993-10-01 | 1996-01-23 | Mahurkar; Sakharam D. | Multiple-lumen catheter |
US5555618A (en) | 1993-10-12 | 1996-09-17 | Arrow International Investment Corp. | Method of making electrode-carrying catheter |
US5417208A (en) | 1993-10-12 | 1995-05-23 | Arrow International Investment Corp. | Electrode-carrying catheter and method of making same |
US5524632A (en) | 1994-01-07 | 1996-06-11 | Medtronic, Inc. | Method for implanting electromyographic sensing electrodes |
US5527358A (en) | 1994-01-21 | 1996-06-18 | Medtronic, Inc. | Temporary medical electrical lead |
JP3269125B2 (en) | 1994-01-28 | 2002-03-25 | 東レ株式会社 | Atopic dermatitis drug |
US5476498A (en) | 1994-08-15 | 1995-12-19 | Incontrol, Inc. | Coronary sinus channel lead and method |
US5549655A (en) | 1994-09-21 | 1996-08-27 | Medtronic, Inc. | Method and apparatus for synchronized treatment of obstructive sleep apnea |
US5604231A (en) | 1995-01-06 | 1997-02-18 | Smith; Carr J. | Pharmaceutical compositions for prevention and treatment of ulcerative colitis |
US5678535A (en) | 1995-04-21 | 1997-10-21 | Dimarco; Anthony Fortunato | Method and apparatus for electrical stimulation of the respiratory muscles to achieve artificial ventilation in a patient |
US5584873A (en) | 1995-05-08 | 1996-12-17 | Medtronic, Inc. | Medical lead with compression lumens |
WO1997014473A1 (en) | 1995-10-18 | 1997-04-24 | Novartis Ag | Thermopile powered transdermal drug delivery device |
US6198970B1 (en) | 1995-10-27 | 2001-03-06 | Esd Limited Liability Company | Method and apparatus for treating oropharyngeal respiratory and oral motor neuromuscular disorders with electrical stimulation |
EP0955881B1 (en) | 1995-11-17 | 2001-05-23 | New York University | Apparatus and method for pressure and temperature waveform analysis |
US5697377A (en) | 1995-11-22 | 1997-12-16 | Medtronic, Inc. | Catheter mapping system and method |
US5716392A (en) | 1996-01-05 | 1998-02-10 | Medtronic, Inc. | Minimally invasive medical electrical lead |
US6096728A (en) | 1996-02-09 | 2000-08-01 | Amgen Inc. | Composition and method for treating inflammatory diseases |
US5772693A (en) | 1996-02-09 | 1998-06-30 | Cardiac Control Systems, Inc. | Single preformed catheter configuration for a dual-chamber pacemaker system |
US5665103A (en) | 1996-03-07 | 1997-09-09 | Scimed Life Systems, Inc. | Stent locating device |
US6166048A (en) | 1999-04-20 | 2000-12-26 | Targacept, Inc. | Pharmaceutical compositions for inhibition of cytokine production and secretion |
US6449507B1 (en) | 1996-04-30 | 2002-09-10 | Medtronic, Inc. | Method and system for nerve stimulation prior to and during a medical procedure |
USRE38705E1 (en) | 1996-04-30 | 2005-02-22 | Medtronic, Inc. | Method and device for electronically controlling the beating of a heart using venous electrical stimulation of nerve fibers |
US6006134A (en) | 1998-04-30 | 1999-12-21 | Medtronic, Inc. | Method and device for electronically controlling the beating of a heart using venous electrical stimulation of nerve fibers |
US20070208388A1 (en) | 1996-04-30 | 2007-09-06 | Jahns Scott E | Method and system for nerve stimulation and cardiac sensing prior to and during a medical procedure |
US7225019B2 (en) | 1996-04-30 | 2007-05-29 | Medtronic, Inc. | Method and system for nerve stimulation and cardiac sensing prior to and during a medical procedure |
US5913848A (en) | 1996-06-06 | 1999-06-22 | Luther Medical Products, Inc. | Hard tip over-the-needle catheter and method of manufacturing the same |
US5827192A (en) | 1996-08-21 | 1998-10-27 | Cleveland Clinic Foundation | Method of determining the conductivity of blood |
US5971933A (en) | 1996-09-17 | 1999-10-26 | Cleveland Clinic Foundation | Method and apparatus to correct for electric field non-uniformity in conductance catheter volumetry |
SE9603841D0 (en) | 1996-10-18 | 1996-10-18 | Pacesetter Ab | A tissue stimulating apparatus |
US5776111A (en) | 1996-11-07 | 1998-07-07 | Medical Components, Inc. | Multiple catheter assembly |
US5785706A (en) | 1996-11-18 | 1998-07-28 | Daig Corporation | Nonsurgical mapping and treatment of cardiac arrhythmia using a catheter contained within a guiding introducer containing openings |
US5782828A (en) | 1996-12-11 | 1998-07-21 | Irvine Biomedical, Inc. | Ablation catheter with multiple flexible curves |
US5755765A (en) | 1997-01-24 | 1998-05-26 | Cardiac Pacemakers, Inc. | Pacing lead having detachable positioning member |
US5916163A (en) | 1997-03-07 | 1999-06-29 | Ep Technologies, Inc. | Graphical user interface for use with multiple electrode catheters |
US5954761A (en) | 1997-03-25 | 1999-09-21 | Intermedics Inc. | Implantable endocardial lead assembly having a stent |
US5779732A (en) | 1997-03-31 | 1998-07-14 | Medtronic, Inc. | Method and apparatus for implanting a film with an exandable stent |
US5944022A (en) | 1997-04-28 | 1999-08-31 | American Cardiac Ablation Co. Inc. | Catheter positioning system |
US6869431B2 (en) | 1997-07-08 | 2005-03-22 | Atrionix, Inc. | Medical device with sensor cooperating with expandable member |
US5824027A (en) | 1997-08-14 | 1998-10-20 | Simon Fraser University | Nerve cuff having one or more isolated chambers |
US6479523B1 (en) | 1997-08-26 | 2002-11-12 | Emory University | Pharmacologic drug combination in vagal-induced asystole |
US6249708B1 (en) | 1997-08-26 | 2001-06-19 | Angeion Corporation | Fluted channel construction for a multi-conductor catheter lead |
US5922014A (en) | 1997-09-02 | 1999-07-13 | Medtronic, Inc. | Single pass lead and method of use |
US6024702A (en) | 1997-09-03 | 2000-02-15 | Pmt Corporation | Implantable electrode manufactured with flexible printed circuit |
US6123699A (en) | 1997-09-05 | 2000-09-26 | Cordis Webster, Inc. | Omni-directional steerable catheter |
US6179832B1 (en) | 1997-09-11 | 2001-01-30 | Vnus Medical Technologies, Inc. | Expandable catheter having two sets of electrodes |
US6171277B1 (en) | 1997-12-01 | 2001-01-09 | Cordis Webster, Inc. | Bi-directional control handle for steerable catheter |
US6120476A (en) | 1997-12-01 | 2000-09-19 | Cordis Webster, Inc. | Irrigated tip catheter |
US6183463B1 (en) | 1997-12-01 | 2001-02-06 | Cordis Webster, Inc. | Bidirectional steerable cathether with bidirectional control handle |
US6415187B1 (en) | 1998-02-10 | 2002-07-02 | Advanced Bionics Corporation | Implantable, expandable, multicontact electrodes and insertion needle for use therewith |
US6269269B1 (en) | 1998-04-23 | 2001-07-31 | Medtronic Inc. | Method and apparatus for synchronized treatment of obstructive sleep apnea |
US6251126B1 (en) | 1998-04-23 | 2001-06-26 | Medtronic Inc | Method and apparatus for synchronized treatment of obstructive sleep apnea |
US6161047A (en) | 1998-04-30 | 2000-12-12 | Medtronic Inc. | Apparatus and method for expanding a stimulation lead body in situ |
US6240320B1 (en) | 1998-06-05 | 2001-05-29 | Intermedics Inc. | Cardiac lead with zone insulated electrodes |
US6134478A (en) | 1998-06-05 | 2000-10-17 | Intermedics Inc. | Method for making cardiac leads with zone insulated electrodes |
US6002965A (en) | 1998-06-10 | 1999-12-14 | Katz; Amiram | Self applied device and method for prevention of deep vein thrombosis |
US6463327B1 (en) | 1998-06-11 | 2002-10-08 | Cprx Llc | Stimulatory device and methods to electrically stimulate the phrenic nerve |
US6292695B1 (en) | 1998-06-19 | 2001-09-18 | Wilton W. Webster, Jr. | Method and apparatus for transvascular treatment of tachycardia and fibrillation |
US6213960B1 (en) | 1998-06-19 | 2001-04-10 | Revivant Corporation | Chest compression device with electro-stimulation |
SE9802335D0 (en) | 1998-06-30 | 1998-06-30 | Siemens Elema Ab | Breathing Help System |
US6198974B1 (en) | 1998-08-14 | 2001-03-06 | Cordis Webster, Inc. | Bi-directional steerable catheter |
US7972323B1 (en) | 1998-10-02 | 2011-07-05 | Boston Scientific Scimed, Inc. | Steerable device for introducing diagnostic and therapeutic apparatus into the body |
FR2784300B1 (en) | 1998-10-13 | 2000-12-08 | Ela Medical Sa | IMPLANTABLE LEFT VENTRICLE STIMULATION PROBE IN THE CORONARY VENOUS NETWORK FOR ACTIVE IMPLANTABLE MEDICAL DEVICE, IN PARTICULAR "MULTI-SITE" STIMULATOR |
SE9803508D0 (en) | 1998-10-14 | 1998-10-14 | Siemens Elema Ab | Assisted Breathing System |
US6208881B1 (en) | 1998-10-20 | 2001-03-27 | Micropure Medical, Inc. | Catheter with thin film electrodes and method for making same |
US7076307B2 (en) | 2002-05-09 | 2006-07-11 | Boveja Birinder R | Method and system for modulating the vagus nerve (10th cranial nerve) with electrical pulses using implanted and external components, to provide therapy neurological and neuropsychiatric disorders |
US6212435B1 (en) | 1998-11-13 | 2001-04-03 | Respironics, Inc. | Intraoral electromuscular stimulation device and method |
EP1025822A1 (en) | 1999-02-08 | 2000-08-09 | Paul Hartmann Aktiengesellschaft | Absorption body for a hygienic article |
US6210339B1 (en) | 1999-03-03 | 2001-04-03 | Endosonics Corporation | Flexible elongate member having one or more electrical contacts |
US6161029A (en) | 1999-03-08 | 2000-12-12 | Medtronic, Inc. | Apparatus and method for fixing electrodes in a blood vessel |
DE19912635A1 (en) | 1999-03-20 | 2000-09-21 | Biotronik Mess & Therapieg | Dilatable cardiac electrode arrangement for implantation, particularly in the coronary sinus of the heart |
US6136021A (en) | 1999-03-23 | 2000-10-24 | Cardiac Pacemakers, Inc. | Expandable electrode for coronary venous leads |
US6593754B1 (en) | 1999-04-01 | 2003-07-15 | Actuant Corporation | Compact subsurface object locator |
US6216045B1 (en) | 1999-04-26 | 2001-04-10 | Advanced Neuromodulation Systems, Inc. | Implantable lead and method of manufacture |
US6126649A (en) | 1999-06-10 | 2000-10-03 | Transvascular, Inc. | Steerable catheter with external guidewire as catheter tip deflector |
EP1198271A4 (en) | 1999-06-25 | 2009-01-21 | Univ Emory | Devices and methods for vagus nerve stimulation |
EP1189649B1 (en) | 1999-06-30 | 2005-06-15 | University Of Florida Research Foundation, Inc. | Ventilator monitor system |
US6702780B1 (en) | 1999-09-08 | 2004-03-09 | Super Dimension Ltd. | Steering configuration for catheter with rigid distal device |
US6236892B1 (en) | 1999-10-07 | 2001-05-22 | Claudio A. Feler | Spinal cord stimulation lead |
US6295475B1 (en) | 1999-10-27 | 2001-09-25 | Pacesetter, Inc. | Single-pass atrial ventricular lead with multiple atrial ring electrodes and a selective atrial electrode adaptor for the coronary sinus region |
US7206636B1 (en) | 1999-11-10 | 2007-04-17 | Pacesetter, Inc. | Pacing optimization based on changes in pulse amplitude and pulse amplitude variability |
US6556873B1 (en) | 1999-11-29 | 2003-04-29 | Medtronic, Inc. | Medical electrical lead having variable bending stiffness |
US20020026228A1 (en) | 1999-11-30 | 2002-02-28 | Patrick Schauerte | Electrode for intravascular stimulation, cardioversion and/or defibrillation |
US6415183B1 (en) | 1999-12-09 | 2002-07-02 | Cardiac Pacemakers, Inc. | Method and apparatus for diaphragmatic pacing |
US6885888B2 (en) | 2000-01-20 | 2005-04-26 | The Cleveland Clinic Foundation | Electrical stimulation of the sympathetic nerve chain |
US6493590B1 (en) | 2000-02-09 | 2002-12-10 | Micronet Medical, Inc. | Flexible band electrodes for medical leads |
AU2001257582A1 (en) | 2000-03-14 | 2001-09-24 | Children's Medical Center Corporation, The | Method for improving respiratory function and inhibiting muscular degeneration |
US6397108B1 (en) | 2000-04-03 | 2002-05-28 | Medtronic Inc. | Safety adaptor for temporary medical leads |
US6638268B2 (en) | 2000-04-07 | 2003-10-28 | Imran K. Niazi | Catheter to cannulate the coronary sinus |
US6442413B1 (en) | 2000-05-15 | 2002-08-27 | James H. Silver | Implantable sensor |
US6508802B1 (en) | 2000-05-23 | 2003-01-21 | Cornell Research Foundation, Inc. | Remote sensing gene therapy delivery device and method of administering a therapeutic solution to a heart |
US6610713B2 (en) | 2000-05-23 | 2003-08-26 | North Shore - Long Island Jewish Research Institute | Inhibition of inflammatory cytokine production by cholinergic agonists and vagus nerve stimulation |
US6695832B2 (en) | 2000-06-01 | 2004-02-24 | Twincath, Llc | Multilumen catheter and methods for making the catheter |
US6719749B1 (en) | 2000-06-01 | 2004-04-13 | Medical Components, Inc. | Multilumen catheter assembly and methods for making and inserting the same |
US6584362B1 (en) | 2000-08-30 | 2003-06-24 | Cardiac Pacemakers, Inc. | Leads for pacing and/or sensing the heart from within the coronary veins |
US7555349B2 (en) | 2000-09-26 | 2009-06-30 | Advanced Neuromodulation Systems, Inc. | Lead body and method of lead body construction |
US7149585B2 (en) | 2001-03-30 | 2006-12-12 | Micronet Medical, Inc. | Lead body and method of lead body construction |
US7499742B2 (en) | 2001-09-26 | 2009-03-03 | Cvrx, Inc. | Electrode structures and methods for their use in cardiovascular reflex control |
US6757970B1 (en) | 2000-11-07 | 2004-07-06 | Advanced Bionics Corporation | Method of making multi-contact electrode array |
SE0004141D0 (en) | 2000-11-13 | 2000-11-13 | Siemens Elema Ab | Method of adaptive triggering of breathing devices and a breathing device |
US7212867B2 (en) | 2000-12-07 | 2007-05-01 | Medtronic, Inc. | Directional brain stimulation and recording leads |
US7519421B2 (en) | 2001-01-16 | 2009-04-14 | Kenergy, Inc. | Vagal nerve stimulation using vascular implanted devices for treatment of atrial fibrillation |
US6445953B1 (en) | 2001-01-16 | 2002-09-03 | Kenergy, Inc. | Wireless cardiac pacing system with vascular electrode-stents |
DE10103288A1 (en) | 2001-01-25 | 2002-08-01 | Patrick Schauerte | Vascular lock for intravascular nerve stimulation and fluid infusion |
DE10105383C2 (en) | 2001-02-06 | 2003-06-05 | Heptec Gmbh | Anti-snoring device |
ZA200306564B (en) | 2001-02-26 | 2004-10-15 | Optinose As | Nasal devices. |
US7167751B1 (en) | 2001-03-01 | 2007-01-23 | Advanced Bionics Corporation | Method of using a fully implantable miniature neurostimulator for vagus nerve stimulation |
US6585718B2 (en) | 2001-05-02 | 2003-07-01 | Cardiac Pacemakers, Inc. | Steerable catheter with shaft support system for resisting axial compressive loads |
CA2448912C (en) | 2001-05-30 | 2012-01-03 | Innersa Technology | Implantable devices having a liquid crystal polymer substrate |
JP4295086B2 (en) | 2001-07-11 | 2009-07-15 | ヌバシブ, インコーポレイテッド | System and method for determining nerve proximity, nerve orientation, and pathology during surgery |
US6569114B2 (en) | 2001-08-31 | 2003-05-27 | Biosense Webster, Inc. | Steerable catheter with struts |
US7974693B2 (en) | 2001-08-31 | 2011-07-05 | Bio Control Medical (B.C.M.) Ltd. | Techniques for applying, configuring, and coordinating nerve fiber stimulation |
EP2481338A3 (en) | 2001-09-25 | 2012-09-05 | Nuvasive, Inc. | System for performing surgical procedures and assessments |
US7168429B2 (en) | 2001-10-12 | 2007-01-30 | Ric Investments, Llc | Auto-titration pressure support system and method of using same |
US6934583B2 (en) | 2001-10-22 | 2005-08-23 | Pacesetter, Inc. | Implantable lead and method for stimulating the vagus nerve |
US6721603B2 (en) | 2002-01-25 | 2004-04-13 | Cyberonics, Inc. | Nerve stimulation as a treatment for pain |
WO2003068944A2 (en) | 2002-02-13 | 2003-08-21 | Dana-Farber Cancer Institute, Inc. | METHODS AND COMPOSITION FOR MODULATING TYPE I MUSCLE FORMATION USING PGC-1α- |
US7653438B2 (en) | 2002-04-08 | 2010-01-26 | Ardian, Inc. | Methods and apparatus for renal neuromodulation |
US7620451B2 (en) | 2005-12-29 | 2009-11-17 | Ardian, Inc. | Methods and apparatus for pulsed electric field neuromodulation via an intra-to-extravascular approach |
US20030195571A1 (en) | 2002-04-12 | 2003-10-16 | Burnes John E. | Method and apparatus for the treatment of central sleep apnea using biventricular pacing |
WO2003094855A1 (en) | 2002-05-08 | 2003-11-20 | The Regents Of The University Of California | System and method for treating cardiac arrhythmias with fibroblast cells |
US7292890B2 (en) | 2002-06-20 | 2007-11-06 | Advanced Bionics Corporation | Vagus nerve stimulation via unidirectional propagation of action potentials |
SE0202537D0 (en) | 2002-08-28 | 2002-08-28 | Siemens Elema Ab | Nerve stimulation apparatus |
US20040064069A1 (en) | 2002-09-30 | 2004-04-01 | Reynolds Brian R. | Medical device with support member |
SE0203108D0 (en) | 2002-10-22 | 2002-10-22 | Siemens Elema Ab | Multi-Electrode Catheter |
US20050033137A1 (en) | 2002-10-25 | 2005-02-10 | The Regents Of The University Of Michigan | Ablation catheters and methods for their use |
US7277757B2 (en) | 2002-10-31 | 2007-10-02 | Medtronic, Inc. | Respiratory nerve stimulation |
US7130700B2 (en) | 2002-11-19 | 2006-10-31 | Medtronic, Inc. | Multilumen body for an implantable medical device |
US20040111139A1 (en) | 2002-12-10 | 2004-06-10 | Mccreery Douglas B. | Apparatus and methods for differential stimulation of nerve fibers |
US7613515B2 (en) | 2003-02-03 | 2009-11-03 | Enteromedics Inc. | High frequency vagal blockage therapy |
EP1599232B1 (en) | 2003-02-21 | 2013-08-14 | Electro-Cat, LLC | System for measuring cross-sectional areas and pressure gradients in luminal organs |
US7142903B2 (en) | 2003-03-12 | 2006-11-28 | Biosense Webster, Inc. | Catheter with contractable mapping assembly |
US7155278B2 (en) | 2003-04-21 | 2006-12-26 | Medtronic, Inc. | Neurostimulation to treat effects of sleep apnea |
EP3064242A1 (en) | 2003-04-28 | 2016-09-07 | Advanced Circulatory Systems Inc. | Ventilator and methods for treating head trauma and low blood circulation |
US20060111755A1 (en) | 2003-05-16 | 2006-05-25 | Stone Robert T | Method and system to control respiration by means of neuro-electrical coded signals |
US20060287679A1 (en) | 2003-05-16 | 2006-12-21 | Stone Robert T | Method and system to control respiration by means of confounding neuro-electrical signals |
US6999820B2 (en) | 2003-05-29 | 2006-02-14 | Advanced Neuromodulation Systems, Inc. | Winged electrode body for spinal cord stimulation |
CA2527909A1 (en) | 2003-06-04 | 2005-01-06 | Synecor Llc | Intravascular electrophysiological system and methods |
US7235070B2 (en) | 2003-07-02 | 2007-06-26 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Ablation fluid manifold for ablation catheter |
TW200503738A (en) | 2003-07-16 | 2005-02-01 | Tzu Chi Buddhist General Hospital | Method for extracting antineoplastic components from bupleurum scorzonerifolium |
US7840270B2 (en) | 2003-07-23 | 2010-11-23 | Synapse Biomedical, Inc. | System and method for conditioning a diaphragm of a patient |
US20050027338A1 (en) | 2003-07-29 | 2005-02-03 | Advanced Neuromodulation Systems, Inc. | Stretchable lead body, method of manufacture, and system |
US20050033136A1 (en) | 2003-08-01 | 2005-02-10 | Assaf Govari | Catheter with electrode strip |
EP1670547B1 (en) | 2003-08-18 | 2008-11-12 | Cardiac Pacemakers, Inc. | Patient monitoring system |
US7887493B2 (en) | 2003-09-18 | 2011-02-15 | Cardiac Pacemakers, Inc. | Implantable device employing movement sensing for detecting sleep-related disorders |
US7662101B2 (en) | 2003-09-18 | 2010-02-16 | Cardiac Pacemakers, Inc. | Therapy control based on cardiopulmonary status |
EP1660004A4 (en) | 2003-08-18 | 2017-05-31 | Breathe Technologies, Inc. | Method and device for non-invasive ventilation with nasal interface |
US7591265B2 (en) | 2003-09-18 | 2009-09-22 | Cardiac Pacemakers, Inc. | Coordinated use of respiratory and cardiac therapies for sleep disordered breathing |
US7502650B2 (en) | 2003-09-22 | 2009-03-10 | Cvrx, Inc. | Baroreceptor activation for epilepsy control |
US8147486B2 (en) | 2003-09-22 | 2012-04-03 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Medical device with flexible printed circuit |
US20050070981A1 (en) | 2003-09-29 | 2005-03-31 | Sumit Verma | Active fixation coronary sinus lead apparatus |
NO319063B1 (en) | 2003-10-06 | 2005-06-13 | Laerdal Medical As | Medical patient simulator |
US20080288010A1 (en) | 2003-10-15 | 2008-11-20 | Rmx, Llc | Subcutaneous diaphragm stimulation device and method for use |
US7970475B2 (en) | 2003-10-15 | 2011-06-28 | Rmx, Llc | Device and method for biasing lung volume |
US8160711B2 (en) | 2003-10-15 | 2012-04-17 | Rmx, Llc | Multimode device and method for controlling breathing |
US20080215106A1 (en) | 2003-10-15 | 2008-09-04 | Chang Lee | Thoracoscopically implantable diaphragm stimulator |
US20080288015A1 (en) | 2003-10-15 | 2008-11-20 | Rmx, Llc | Diaphragm stimulation device and method for use with cardiovascular or heart patients |
US8467876B2 (en) | 2003-10-15 | 2013-06-18 | Rmx, Llc | Breathing disorder detection and therapy delivery device and method |
US20080161878A1 (en) | 2003-10-15 | 2008-07-03 | Tehrani Amir J | Device and method to for independently stimulating hemidiaphragms |
US7979128B2 (en) | 2003-10-15 | 2011-07-12 | Rmx, Llc | Device and method for gradually controlling breathing |
US8244358B2 (en) | 2003-10-15 | 2012-08-14 | Rmx, Llc | Device and method for treating obstructive sleep apnea |
US8140164B2 (en) | 2003-10-15 | 2012-03-20 | Rmx, Llc | Therapeutic diaphragm stimulation device and method |
US20110288609A1 (en) | 2003-10-15 | 2011-11-24 | Rmx, Llc | Therapeutic diaphragm stimulation device and method |
US8265759B2 (en) | 2003-10-15 | 2012-09-11 | Rmx, Llc | Device and method for treating disorders of the cardiovascular system or heart |
US9259573B2 (en) | 2003-10-15 | 2016-02-16 | Rmx, Llc | Device and method for manipulating exhalation |
US20120158091A1 (en) | 2003-10-15 | 2012-06-21 | Rmx, Llc | Therapeutic diaphragm stimulation device and method |
US20060167523A1 (en) | 2003-10-15 | 2006-07-27 | Tehrani Amir J | Device and method for improving upper airway functionality |
US20060074449A1 (en) | 2003-11-03 | 2006-04-06 | Stephen Denker | Intravascular stimulation system with wireless power supply |
US7077823B2 (en) | 2003-11-19 | 2006-07-18 | Biosense Webster, Inc. | Bidirectional steerable catheter with slidable mated puller wires |
US7802571B2 (en) | 2003-11-21 | 2010-09-28 | Tehrani Fleur T | Method and apparatus for controlling a ventilator |
US8224456B2 (en) | 2003-11-25 | 2012-07-17 | Advanced Neuromodulation Systems, Inc. | Directional stimulation lead and orientation system |
US7519425B2 (en) | 2004-01-26 | 2009-04-14 | Pacesetter, Inc. | Tiered therapy for respiratory oscillations characteristic of Cheyne-Stokes respiration |
US7363085B1 (en) | 2004-01-26 | 2008-04-22 | Pacesetters, Inc. | Augmenting hypoventilation |
US7421296B1 (en) | 2004-01-26 | 2008-09-02 | Pacesetter, Inc. | Termination of respiratory oscillations characteristic of Cheyne-Stokes respiration |
WO2005077268A1 (en) | 2004-02-18 | 2005-08-25 | Maquet Critical Care Ab | Method and device using myoelectrical activity for optimizing a patient’s ventilatory assist |
US7569029B2 (en) | 2004-04-12 | 2009-08-04 | Clark Timothy W I | Multi-lumen catheter |
US7082331B1 (en) | 2004-04-21 | 2006-07-25 | Pacesetter, Inc. | System and method for applying therapy during hyperpnea phase of periodic breathing using an implantable medical device |
US8412348B2 (en) | 2004-05-06 | 2013-04-02 | Boston Scientific Neuromodulation Corporation | Intravascular self-anchoring integrated tubular electrode body |
US20070106357A1 (en) | 2005-11-04 | 2007-05-10 | Stephen Denker | Intravascular Electronics Carrier Electrode for a Transvascular Tissue Stimulation System |
US7747323B2 (en) | 2004-06-08 | 2010-06-29 | Cardiac Pacemakers, Inc. | Adaptive baroreflex stimulation therapy for disordered breathing |
US7591799B2 (en) | 2004-06-14 | 2009-09-22 | Biosense Webster, Inc. | Steering mechanism for bi-directional catheter |
US7225016B1 (en) | 2004-06-16 | 2007-05-29 | Pacesetter, Inc. | Implantable medical device with nerve signal sensing |
US7371220B1 (en) | 2004-06-30 | 2008-05-13 | Pacesetter, Inc. | System and method for real-time apnea/hypopnea detection using an implantable medical system |
US7962215B2 (en) | 2004-07-23 | 2011-06-14 | Synapse Biomedical, Inc. | Ventilatory assist system and methods to improve respiratory function |
EP1621247A1 (en) | 2004-07-30 | 2006-02-01 | MAN DWE GmbH | Carry out of exothermic gas-phase reactions |
US20060058852A1 (en) | 2004-09-10 | 2006-03-16 | Steve Koh | Multi-variable feedback control of stimulation for inspiratory facilitation |
US7340302B1 (en) | 2004-09-27 | 2008-03-04 | Pacesetter, Inc. | Treating sleep apnea in patients using phrenic nerve stimulation |
US9026228B2 (en) | 2004-10-21 | 2015-05-05 | Medtronic, Inc. | Transverse tripole neurostimulation lead, system and method |
US10537741B2 (en) | 2004-12-03 | 2020-01-21 | Boston Scientific Neuromodulation Corporation | System and method for choosing electrodes in an implanted stimulator device |
US20060122661A1 (en) | 2004-12-03 | 2006-06-08 | Mandell Lee J | Diaphragmatic pacing with activity monitor adjustment |
KR20070106995A (en) | 2004-12-08 | 2007-11-06 | 벤투스 메디컬, 인코포레이티드 | Respiratory devices and methods of use |
US20060130833A1 (en) | 2004-12-16 | 2006-06-22 | Magdy Younes | Treatment of obstructive sleep apnea |
US7869865B2 (en) | 2005-01-07 | 2011-01-11 | Biosense Webster, Inc. | Current-based position sensing |
US7891085B1 (en) | 2005-01-11 | 2011-02-22 | Boston Scientific Neuromodulation Corporation | Electrode array assembly and method of making same |
US8019439B2 (en) | 2005-01-11 | 2011-09-13 | Boston Scientific Neuromodulation Corporation | Lead assembly and method of making same |
US7269459B1 (en) | 2005-02-08 | 2007-09-11 | Pacesetter, Inc. | Implantable cardiac device with selectable tiered sleep apnea therapies and method |
US7255511B2 (en) | 2005-02-22 | 2007-08-14 | Dolan Kevin P | Releasable dovetail corner joint |
US7920915B2 (en) | 2005-11-16 | 2011-04-05 | Boston Scientific Neuromodulation Corporation | Implantable stimulator |
US7363086B1 (en) | 2005-03-21 | 2008-04-22 | Pacesetter, Inc. | Capture verification in respiratory diaphragm stimulation |
US20060217791A1 (en) | 2005-03-23 | 2006-09-28 | Arrow International, Inc. | Multi-lumen catheter having external electrical leads |
US7499748B2 (en) | 2005-04-11 | 2009-03-03 | Cardiac Pacemakers, Inc. | Transvascular neural stimulation device |
US7630763B2 (en) | 2005-04-20 | 2009-12-08 | Cardiac Pacemakers, Inc. | Thoracic or intracardiac impedance detection with automatic vector selection |
US7676275B1 (en) | 2005-05-02 | 2010-03-09 | Pacesetter, Inc. | Endovascular lead for chronic nerve stimulation |
US7561923B2 (en) | 2005-05-09 | 2009-07-14 | Cardiac Pacemakers, Inc. | Method and apparatus for controlling autonomic balance using neural stimulation |
US7617003B2 (en) | 2005-05-16 | 2009-11-10 | Cardiac Pacemakers, Inc. | System for selective activation of a nerve trunk using a transvascular reshaping lead |
US7949412B1 (en) | 2005-06-02 | 2011-05-24 | Advanced Bionics, Llc | Coated electrode array having uncoated electrode contacts |
US7553305B2 (en) | 2005-06-09 | 2009-06-30 | Enpath Medical, Inc. | Push-pull wire anchor |
US8036750B2 (en) | 2005-06-13 | 2011-10-11 | Cardiac Pacemakers, Inc. | System for neural control of respiration |
US20070005053A1 (en) | 2005-06-30 | 2007-01-04 | Dando Jeremy D | Ablation catheter with contoured openings in insulated electrodes |
US7879030B2 (en) | 2005-07-27 | 2011-02-01 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Multipolar, virtual-electrode catheter with at least one surface electrode and method for ablation |
US7416552B2 (en) | 2005-08-22 | 2008-08-26 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Multipolar, multi-lumen, virtual-electrode catheter with at least one surface electrode and method for ablation |
US7519426B1 (en) | 2005-10-07 | 2009-04-14 | Pacesetter, Inc. | Techniques for reducing orthostatic hypotension |
US7771388B2 (en) | 2005-10-12 | 2010-08-10 | Daniel Olsen | Steerable catheter system |
US20070112402A1 (en) | 2005-10-19 | 2007-05-17 | Duke University | Electrode systems and related methods for providing therapeutic differential tissue stimulation |
US7636600B1 (en) | 2005-10-21 | 2009-12-22 | Pacesetter, Inc. | Pressure monitoring for apnea prevention and/or therapy |
US7616990B2 (en) | 2005-10-24 | 2009-11-10 | Cardiac Pacemakers, Inc. | Implantable and rechargeable neural stimulator |
AU2006311701B2 (en) | 2005-11-08 | 2012-08-30 | Custom Medical Applications, Inc. | Reinforced catheter with articulated distal tip |
US10406366B2 (en) | 2006-11-17 | 2019-09-10 | Respicardia, Inc. | Transvenous phrenic nerve stimulation system |
US8696656B2 (en) | 2005-11-18 | 2014-04-15 | Medtronic Cryocath Lp | System and method for monitoring bioimpedance and respiration |
EP1960038B8 (en) | 2005-11-18 | 2021-04-07 | Respicardia, Inc. | System to modulate phrenic nerve to prevent sleep apnea |
US20220212005A9 (en) | 2005-11-18 | 2022-07-07 | Zoll Respicardia, Inc. | Transvenous Phrenic Nerve Stimulation System |
EP1968693A4 (en) | 2005-12-22 | 2011-04-27 | Proteus Biomedical Inc | Implantable integrated circuit |
US7672728B2 (en) | 2005-12-28 | 2010-03-02 | Cardiac Pacemakers, Inc. | Neural stimulator to treat sleep disordered breathing |
US8281792B2 (en) | 2005-12-31 | 2012-10-09 | John W Royalty | Electromagnetic diaphragm assist device and method for assisting a diaphragm function |
US7813805B1 (en) | 2006-01-11 | 2010-10-12 | Pacesetter, Inc. | Subcardiac threshold vagal nerve stimulation |
US7763034B2 (en) | 2006-01-24 | 2010-07-27 | Medtronic, Inc. | Transobturator lead implantation for pelvic floor stimulation |
US7347695B2 (en) | 2006-02-03 | 2008-03-25 | Ware Linda M | Chronic obstructive pulmonary disease simulator |
JP5256048B2 (en) | 2006-02-03 | 2013-08-07 | シネコー・エルエルシー | Intravascular devices for neuromodulation |
WO2007098367A2 (en) | 2006-02-16 | 2007-08-30 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Method and apparatus for stimulating a denervated muscle |
US7810497B2 (en) | 2006-03-20 | 2010-10-12 | Ric Investments, Llc | Ventilatory control system |
US7900626B2 (en) | 2006-04-17 | 2011-03-08 | Daly Robert W | Method and system for controlling breathing |
US20070288076A1 (en) | 2006-06-07 | 2007-12-13 | Cherik Bulkes | Biological tissue stimulator with flexible electrode carrier |
CA2622731C (en) | 2006-06-08 | 2011-06-07 | Surgical Solutions Llc | Medical device with articulating shaft |
US20080039916A1 (en) | 2006-08-08 | 2008-02-14 | Olivier Colliou | Distally distributed multi-electrode lead |
US8121692B2 (en) | 2006-08-30 | 2012-02-21 | Cardiac Pacemakers, Inc. | Method and apparatus for neural stimulation with respiratory feedback |
US8050765B2 (en) | 2006-08-30 | 2011-11-01 | Cardiac Pacemakers, Inc. | Method and apparatus for controlling neural stimulation during disordered breathing |
US20080065002A1 (en) | 2006-09-07 | 2008-03-13 | Neurosystec Corporation | Catheter for Localized Drug Delivery and/or Electrical Stimulation |
WO2008045877A2 (en) | 2006-10-10 | 2008-04-17 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Electrode tip and ablation system |
US7794407B2 (en) | 2006-10-23 | 2010-09-14 | Bard Access Systems, Inc. | Method of locating the tip of a central venous catheter |
US8388546B2 (en) | 2006-10-23 | 2013-03-05 | Bard Access Systems, Inc. | Method of locating the tip of a central venous catheter |
WO2008070145A2 (en) | 2006-12-06 | 2008-06-12 | Medtronic, Inc. | User interface with toolbar for programming electrical stimulation therapy |
WO2008070809A2 (en) | 2006-12-06 | 2008-06-12 | Spinal Modulation, Inc. | Implantable flexible circuit leads and methods of use |
US8280513B2 (en) | 2006-12-22 | 2012-10-02 | Rmx, Llc | Device and method to treat flow limitations |
US8909341B2 (en) | 2007-01-22 | 2014-12-09 | Respicardia, Inc. | Device and method for the treatment of breathing disorders and cardiac disorders |
WO2008092246A1 (en) | 2007-01-29 | 2008-08-07 | Simon Fraser University | Transvascular nerve stimulation apparatus and methods |
US20080183186A1 (en) | 2007-01-30 | 2008-07-31 | Cardiac Pacemakers, Inc. | Method and apparatus for delivering a transvascular lead |
US20080183264A1 (en) | 2007-01-30 | 2008-07-31 | Cardiac Pacemakers, Inc. | Electrode configurations for transvascular nerve stimulation |
US8244378B2 (en) | 2007-01-30 | 2012-08-14 | Cardiac Pacemakers, Inc. | Spiral configurations for intravascular lead stability |
US20080183187A1 (en) | 2007-01-30 | 2008-07-31 | Cardiac Pacemakers, Inc. | Direct delivery system for transvascular lead |
US7917230B2 (en) | 2007-01-30 | 2011-03-29 | Cardiac Pacemakers, Inc. | Neurostimulating lead having a stent-like anchor |
US7949409B2 (en) | 2007-01-30 | 2011-05-24 | Cardiac Pacemakers, Inc. | Dual spiral lead configurations |
US20080183255A1 (en) | 2007-01-30 | 2008-07-31 | Cardiac Pacemakers, Inc. | Side port lead delivery system |
US20080183265A1 (en) | 2007-01-30 | 2008-07-31 | Cardiac Pacemakers, Inc. | Transvascular lead with proximal force relief |
US7819883B2 (en) | 2007-03-13 | 2010-10-26 | Cardiac Pacemakers, Inc. | Method and apparatus for endoscopic access to the vagus nerve |
GB0707906D0 (en) | 2007-04-24 | 2007-05-30 | Apparatus for detecting the position of a catheter | |
EP2148712B1 (en) | 2007-04-27 | 2018-10-31 | Maquet Critical Care AB | Control unit and display unit for an emg controlled ventilator |
US10492729B2 (en) | 2007-05-23 | 2019-12-03 | St. Jude Medical, Cardiology Division, Inc. | Flexible high-density mapping catheter tips and flexible ablation catheter tips with onboard high-density mapping electrodes |
EP2170458A1 (en) | 2007-06-13 | 2010-04-07 | E- Pacing, Inc. | Implantable devices and methods for stimulation of cardiac or other tissues |
WO2008157180A1 (en) | 2007-06-13 | 2008-12-24 | E-Pacing, Inc. | Implantable devices and methods for stimulation of cardiac and other tissues |
US9987488B1 (en) | 2007-06-27 | 2018-06-05 | Respicardia, Inc. | Detecting and treating disordered breathing |
EP2164560B8 (en) | 2007-06-29 | 2016-10-12 | NewStim, Inc. | Systems for cardiac rhythm management using an electrode arrangement |
US20090024047A1 (en) | 2007-07-20 | 2009-01-22 | Cardiac Pacemakers, Inc. | Devices and methods for respiration therapy |
US9037239B2 (en) | 2007-08-07 | 2015-05-19 | Cardiac Pacemakers, Inc. | Method and apparatus to perform electrode combination selection |
US8265736B2 (en) | 2007-08-07 | 2012-09-11 | Cardiac Pacemakers, Inc. | Method and apparatus to perform electrode combination selection |
US7994655B2 (en) | 2007-08-17 | 2011-08-09 | Inovise Medical, Inc. | Mechanical, anatomical heart-pumping assist |
US8135471B2 (en) | 2007-08-28 | 2012-03-13 | Cardiac Pacemakers, Inc. | Method and apparatus for inspiratory muscle stimulation using implantable device |
US8527036B2 (en) | 2007-09-28 | 2013-09-03 | Maquet Critical Care Ab | Catheter positioning method and computerized control unit for implementing the method |
WO2009048610A1 (en) | 2007-10-10 | 2009-04-16 | Cardiac Pacemakers, Inc. | Respiratory stimulation for treating periodic breathing |
WO2009059033A1 (en) | 2007-10-30 | 2009-05-07 | Synapse Biomedical, Inc. | Method of improving sleep disordered breathing |
US8428726B2 (en) | 2007-10-30 | 2013-04-23 | Synapse Biomedical, Inc. | Device and method of neuromodulation to effect a functionally restorative adaption of the neuromuscular system |
JP5452500B2 (en) | 2007-11-26 | 2014-03-26 | シー・アール・バード・インコーポレーテッド | Integrated system for intravascular placement of catheters |
US8406883B1 (en) | 2007-12-27 | 2013-03-26 | Boston Scientific Neuromodulation Corporation | Lead assembly for electrical stimulation systems and methods of making and using |
US20130123891A1 (en) | 2008-02-01 | 2013-05-16 | John Swanson | High density terminal contacts for stimulation lead and stimulation system employing the same, and method of stimulation lead fabrication |
US9199075B1 (en) | 2008-02-07 | 2015-12-01 | Respicardia, Inc. | Transvascular medical lead |
US7925352B2 (en) | 2008-03-27 | 2011-04-12 | Synecor Llc | System and method for transvascularly stimulating contents of the carotid sheath |
US8052607B2 (en) | 2008-04-22 | 2011-11-08 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Ultrasound imaging catheter with pivoting head |
WO2009135082A1 (en) | 2008-04-30 | 2009-11-05 | Medtronic, Inc. | Techniques for placing medical leads for electrical stimulation of nerve tissue |
WO2009134459A2 (en) | 2008-05-02 | 2009-11-05 | The Johns Hopkins University | Portable negative pressure ventilation device and methods and software related thereto |
US9409012B2 (en) | 2008-06-19 | 2016-08-09 | Cardiac Pacemakers, Inc. | Pacemaker integrated with vascular intervention catheter |
US8239037B2 (en) | 2008-07-06 | 2012-08-07 | Synecor Llc | Intravascular implant anchors having remote communication and/or battery recharging capabilities |
EP2334372A1 (en) | 2008-07-08 | 2011-06-22 | Cardiac Pacemakers, Inc. | Systems for delivering vagal nerve stimulation |
US8734437B2 (en) | 2008-07-23 | 2014-05-27 | Boston Scientific Scimed, Inc. | Catheter having electrically conductive pathways |
JP4545210B2 (en) | 2008-09-11 | 2010-09-15 | 日本ライフライン株式会社 | Defibrillation catheter |
WO2010045222A1 (en) | 2008-10-13 | 2010-04-22 | E-Pacing, Inc. | Devices and methods for electrical stimulation of the diaphragm and nerves |
US20100114227A1 (en) | 2008-10-30 | 2010-05-06 | Pacesetter, Inc. | Systems and Methds for Use by an Implantable Medical Device for Controlling Vagus Nerve Stimulation Based on Heart Rate Reduction Curves and Thresholds to Mitigate Heart Failure |
US8386053B2 (en) | 2008-10-31 | 2013-02-26 | Medtronic, Inc. | Subclavian ansae stimulation |
WO2010057026A2 (en) | 2008-11-13 | 2010-05-20 | Proteus Biomedical, Inc. | Rechargeable stimulation lead, system, and method |
JP2012508624A (en) | 2008-11-13 | 2012-04-12 | プロテウス バイオメディカル インコーポレイテッド | Multiplexed multiple electrode nerve stimulator |
US8781578B2 (en) | 2008-11-14 | 2014-07-15 | Cardiac Pacemakers, Inc. | Mass attribute detection through phrenic stimulation |
US8644939B2 (en) | 2008-11-18 | 2014-02-04 | Neurostream Technologies General Partnership | Method and device for the detection, identification and treatment of sleep apnea/hypopnea |
US8995731B2 (en) * | 2008-11-26 | 2015-03-31 | Medtronic, Inc. | Image-based characterization of implanted medical leads |
KR101088806B1 (en) | 2009-01-07 | 2011-12-01 | 주식회사 뉴로바이오시스 | Micro-electrode Array Package using Liquid Crystal Polymer and Manufacturing Method thereof |
US20120035684A1 (en) | 2009-02-09 | 2012-02-09 | Todd Thompson | Multiplexed, Multi-Electrode Neurostimulation Devices with Integrated Circuits Having Integrated Electrodes |
US9226689B2 (en) | 2009-03-10 | 2016-01-05 | Medtronic Xomed, Inc. | Flexible circuit sheet |
US9226688B2 (en) | 2009-03-10 | 2016-01-05 | Medtronic Xomed, Inc. | Flexible circuit assemblies |
US20100268311A1 (en) | 2009-04-17 | 2010-10-21 | Ralph Cardinal | Method for Implanting Electrode on Nerve |
US8626292B2 (en) | 2009-05-27 | 2014-01-07 | Cardiac Pacemakers, Inc. | Respiration sensor processing for phrenic nerve activation detection |
US9149642B2 (en) | 2009-05-27 | 2015-10-06 | Cardiac Pacemakers, Inc. | Method and apparatus for phrenic nerve activation detection with respiration cross-checking |
US9532724B2 (en) | 2009-06-12 | 2017-01-03 | Bard Access Systems, Inc. | Apparatus and method for catheter navigation using endovascular energy mapping |
US8694123B2 (en) | 2009-06-19 | 2014-04-08 | Medtronic, Inc. | Helical electrode arrangements for medical leads |
US8340783B2 (en) | 2009-06-30 | 2012-12-25 | Medtronic, Inc. | Implantable medical device lead with selectively exposed electrodes and reinforcement member |
CA2770151A1 (en) | 2009-08-05 | 2011-02-10 | Ndi Medical, Llc | Systems and methods for maintaining airway patency |
US8644952B2 (en) | 2009-09-02 | 2014-02-04 | Cardiac Pacemakers, Inc. | Medical devices including polyisobutylene based polymers and derivatives thereof |
US8374704B2 (en) | 2009-09-02 | 2013-02-12 | Cardiac Pacemakers, Inc. | Polyisobutylene urethane, urea and urethane/urea copolymers and medical leads containing the same |
US9072899B1 (en) | 2009-09-04 | 2015-07-07 | Todd Nickloes | Diaphragm pacemaker |
US8233987B2 (en) | 2009-09-10 | 2012-07-31 | Respicardia, Inc. | Respiratory rectification |
US9468755B2 (en) | 2009-09-30 | 2016-10-18 | Respicardia, Inc. | Medical lead with preformed bias |
US8617228B2 (en) | 2009-10-23 | 2013-12-31 | Medtronic Cryocath Lp | Method and system for preventing nerve injury during a medical procedure |
US8676308B2 (en) * | 2009-11-03 | 2014-03-18 | Boston Scientific Neuromodulation Corporation | System and method for mapping arbitrary electric fields to pre-existing lead electrodes |
CN102821676B (en) | 2010-01-29 | 2016-09-07 | C·R·巴德股份有限公司 | Sacrifice conduit |
BR112012019354B1 (en) | 2010-02-02 | 2021-09-08 | C.R.Bard, Inc | METHOD FOR LOCATION OF AN IMPLANTABLE MEDICAL DEVICE |
US8753333B2 (en) | 2010-03-10 | 2014-06-17 | Covidien Lp | System for determining proximity relative to a nerve |
JP5537213B2 (en) | 2010-03-26 | 2014-07-02 | オリンパス株式会社 | Electrical stimulation electrode assembly |
US20110230945A1 (en) | 2010-03-19 | 2011-09-22 | Olympus Corporation | Electrostimulation system, and electrostimulation electrode assembly and biological implantable electrode therefor |
US10631912B2 (en) | 2010-04-30 | 2020-04-28 | Medtronic Xomed, Inc. | Interface module for use with nerve monitoring and electrosurgery |
US20110270358A1 (en) | 2010-04-30 | 2011-11-03 | Medtronic, Inc. | Implantable medical device programming using gesture-based control |
US8755889B2 (en) | 2010-04-30 | 2014-06-17 | Medtronic, Inc. | Method and apparatus to enhance therapy during stimulation of vagus nerve |
AU2011261702B2 (en) | 2010-06-03 | 2014-11-27 | Cardiac Pacemakers, Inc. | System for controlling target of neurostimulation using temporal parameters |
WO2011153024A1 (en) | 2010-06-03 | 2011-12-08 | Cardiac Pacemakers, Inc. | System for spatially selective vagus nerve stimulation |
JP4940332B2 (en) | 2010-06-15 | 2012-05-30 | 日本ライフライン株式会社 | catheter |
US20120130217A1 (en) | 2010-11-23 | 2012-05-24 | Kauphusman James V | Medical devices having electrodes mounted thereon and methods of manufacturing therefor |
CN102958562B (en) | 2010-06-30 | 2015-05-27 | Med-El电气医疗器械有限公司 | Ear implant electrode and method of manufacture |
WO2012012432A1 (en) | 2010-07-19 | 2012-01-26 | Cardiac Pacemakers, Inc. | Minimally invasive lead system for vagus nerve stimulation |
WO2012015621A1 (en) | 2010-07-29 | 2012-02-02 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using electrical stimulation systems having multi-lead-element lead bodies |
WO2012019036A1 (en) | 2010-08-06 | 2012-02-09 | Cardiac Pacemakers, Inc. | User interface system for use with multipolar pacing leads |
US8934956B2 (en) | 2010-08-31 | 2015-01-13 | Interventional Autonomics Corporation | Intravascular electrodes and anchoring devices for transvascular stimulation |
US20120078320A1 (en) | 2010-09-29 | 2012-03-29 | Medtronic, Inc. | Prioritized programming of multi-electrode pacing leads |
KR101304338B1 (en) | 2010-10-21 | 2013-09-11 | 주식회사 엠아이텍 | LCP-based electro-optrode neural interface and Method for fabricating the same |
WO2012058461A1 (en) | 2010-10-29 | 2012-05-03 | C.R.Bard, Inc. | Bioimpedance-assisted placement of a medical device |
US8391956B2 (en) | 2010-11-18 | 2013-03-05 | Robert D. Zellers | Medical device location systems, devices and methods |
US8560086B2 (en) | 2010-12-02 | 2013-10-15 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Catheter electrode assemblies and methods of construction therefor |
US8781583B2 (en) | 2011-01-19 | 2014-07-15 | Medtronic, Inc. | Vagal stimulation |
US8781582B2 (en) | 2011-01-19 | 2014-07-15 | Medtronic, Inc. | Vagal stimulation |
US8725259B2 (en) | 2011-01-19 | 2014-05-13 | Medtronic, Inc. | Vagal stimulation |
US8718763B2 (en) | 2011-01-19 | 2014-05-06 | Medtronic, Inc. | Vagal stimulation |
US8706223B2 (en) | 2011-01-19 | 2014-04-22 | Medtronic, Inc. | Preventative vagal stimulation |
US9174046B2 (en) | 2011-01-25 | 2015-11-03 | Cedric Francois | Apparatus and methods for assisting breathing |
US9550041B2 (en) | 2011-02-04 | 2017-01-24 | Advanced Pain Center, Llc. | Continuous single wire steerable catheter |
US9744349B2 (en) | 2011-02-10 | 2017-08-29 | Respicardia, Inc. | Medical lead and implantation |
US8430864B2 (en) | 2011-02-16 | 2013-04-30 | Biosense Webster, Inc. | Catheter with multiple deflections |
US8504158B2 (en) | 2011-05-09 | 2013-08-06 | Medtronic, Inc. | Phrenic nerve stimulation during cardiac refractory period |
US9446240B2 (en) * | 2011-07-11 | 2016-09-20 | Interventional Autonomics Corporation | System and method for neuromodulation |
US9615759B2 (en) | 2011-07-12 | 2017-04-11 | Bard Access Systems, Inc. | Devices and methods for ECG guided vascular access |
US20130018427A1 (en) | 2011-07-15 | 2013-01-17 | Khiem Pham | Screw Implants For Bone Fusion |
US8805511B2 (en) | 2011-07-27 | 2014-08-12 | Medtronic, Inc. | Method and apparatus to detect subcerebral ischemia |
US20130030497A1 (en) | 2011-07-27 | 2013-01-31 | Medtronic, Inc. | Nerve stimulator for reduced muscle fatigue |
US8478413B2 (en) | 2011-07-27 | 2013-07-02 | Medtronic, Inc. | Bilateral phrenic nerve stimulation with reduced dyssynchrony |
US9861817B2 (en) | 2011-07-28 | 2018-01-09 | Medtronic, Inc. | Medical device to provide breathing therapy |
US8509902B2 (en) | 2011-07-28 | 2013-08-13 | Medtronic, Inc. | Medical device to provide breathing therapy |
US10201385B2 (en) | 2011-09-01 | 2019-02-12 | Biosense Webster (Israel) Ltd. | Catheter adapted for direct tissue contact |
US9724018B2 (en) | 2011-10-27 | 2017-08-08 | Medtronic Cryocath Lp | Method for monitoring phrenic nerve function |
US8897879B2 (en) | 2011-11-04 | 2014-11-25 | Medtronic, Inc. | Method and apparatus for therapies of the cardiovascular and cardiorenal system |
EP3287067B1 (en) | 2011-11-07 | 2019-10-30 | Medtronic Ardian Luxembourg S.à.r.l. | Endovascular nerve monitoring devices and associated systems |
US9956396B2 (en) | 2012-02-08 | 2018-05-01 | Medtronic Bakken Research Center B.V. | Thin film for a lead for brain applications |
EP3228351B1 (en) | 2012-03-05 | 2019-06-05 | Lungpacer Medical Inc. | Transvascular nerve stimulation apparatus |
EP2827944B1 (en) | 2012-03-21 | 2016-05-18 | Cardiac Pacemakers, Inc. | Systems and methods for stimulation of vagus nerve |
US10413203B2 (en) | 2012-03-27 | 2019-09-17 | Cardiac Pacemakers, Inc. | Baseline determination for phrenic nerve stimulation detection |
WO2013165920A1 (en) | 2012-04-29 | 2013-11-07 | Synecor Llc | Intravascular electrode arrays for neuromodulation |
US9179972B2 (en) | 2012-05-04 | 2015-11-10 | St. Jude Medical, Atrial Fibrillation Division, Inc. | System and method for controlling delivery of ablation energy to tissue |
WO2013177145A1 (en) | 2012-05-25 | 2013-11-28 | Boston Scientific Neuromodulation Corporation | Methods for stimulating the dorsal root ganglion with a lead having segmented electrodes |
CN104684614B (en) | 2012-06-21 | 2017-10-17 | 西蒙·弗雷泽大学 | The diaphragm pacing system and application method of intravascular |
WO2014008171A1 (en) | 2012-07-02 | 2014-01-09 | Medisci L.L.C. | Method and device for respiratory and cardiorespiratory support |
US8504161B1 (en) | 2012-08-07 | 2013-08-06 | Medtronic, Inc. | Modulate vagal signals to reduce inflammation |
JP2015531628A (en) | 2012-08-20 | 2015-11-05 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Synchronization of mechanical forced inspiration exhalation and diaphragmatic pacing |
EP2722071A1 (en) | 2012-10-16 | 2014-04-23 | Sapiens Steering Brain Stimulation B.V. | A probe, especially a probe for neural applications |
US20140121716A1 (en) | 2012-10-31 | 2014-05-01 | Medtronic, Inc. | High voltage therapy diversion algorithms |
US20150290476A1 (en) | 2012-11-05 | 2015-10-15 | Jesus Arturo Cabrera | Non-invasive lung pacing |
CN102949770B (en) | 2012-11-09 | 2015-04-22 | 张红璇 | External diaphragm pacing and breathing machine synergistic air supply method and device thereof |
US9072864B2 (en) | 2012-11-28 | 2015-07-07 | Ad-Tech Medical Instrument Corporation | Catheter with depth electrode for dual-purpose use |
EP4201469A1 (en) | 2012-12-05 | 2023-06-28 | Battelle Memorial Institute | Neuromuscular stimulation cuff |
US9884179B2 (en) | 2012-12-05 | 2018-02-06 | Bbattelle Memorial Institute | Neural sleeve for neuromuscular stimulation, sensing and recording |
US10335592B2 (en) | 2012-12-19 | 2019-07-02 | Viscardia, Inc. | Systems, devices, and methods for improving hemodynamic performance through asymptomatic diaphragm stimulation |
WO2014099820A1 (en) | 2012-12-19 | 2014-06-26 | Inovise Medical, Inc. | Hemodynamic performance enhancement through asymptomatic diaphragm stimulation |
US9485873B2 (en) | 2013-03-15 | 2016-11-01 | Lawrence Livermore National Security, Llc | Depositing bulk or micro-scale electrodes |
EP2818104B1 (en) | 2013-06-25 | 2016-01-06 | VascoMed GmbH | Catheter and method for producing same |
US9427566B2 (en) | 2013-08-14 | 2016-08-30 | Syntilla Medical LLC | Implantable neurostimulation lead for head pain |
US10058697B2 (en) | 2013-08-27 | 2018-08-28 | Advanced Bionics Ag | Thermoformed electrode arrays |
US9504837B2 (en) | 2013-10-25 | 2016-11-29 | Medtronic, Inc. | Automated phrenic nerve stimulation and pacing capture threshold test |
US9205258B2 (en) | 2013-11-04 | 2015-12-08 | ElectroCore, LLC | Nerve stimulator system |
AU2014351473B2 (en) | 2013-11-22 | 2019-11-07 | Lungpacer Medical Inc. | Apparatus and methods for assisted breathing by transvascular nerve stimulation |
WO2015106116A1 (en) | 2014-01-10 | 2015-07-16 | Boston Scientific Scimed, Inc. | Medical devices with flexible circuit assemblies |
EP3566743B1 (en) | 2014-01-21 | 2021-03-10 | Lungpacer Medical Inc. | Systems for optimization of multi-electrode nerve pacing |
US9498631B2 (en) | 2014-02-20 | 2016-11-22 | Medtronic, Inc. | Automated phrenic nerve stimulation and pacing capture threshold test |
US9844644B2 (en) | 2014-03-05 | 2017-12-19 | Oscor Inc. | Intravascular sheath with mapping capabilities to deliver therapeutic devices to a targeted location within a blood vessel |
US20160310730A1 (en) | 2014-03-28 | 2016-10-27 | Antonio Garcia Martins | Stimulation system for exercising diaphragm and method of operation thereof |
US10194978B2 (en) | 2014-06-13 | 2019-02-05 | Medtronic Cryocath Lp | Supporting catheter for use for phrenic nerve pacing |
KR101654801B1 (en) | 2014-08-08 | 2016-09-07 | 서울대학교산학협력단 | Microelectrode array and package for liquid crystal polymer based neuroprostheses and manufacturing method thereof |
WO2016033245A1 (en) | 2014-08-26 | 2016-03-03 | Rmx, Llc | Devices and methods for reducing intrathoracic pressure |
US9474894B2 (en) | 2014-08-27 | 2016-10-25 | Aleva Neurotherapeutics | Deep brain stimulation lead |
CN107205641A (en) | 2014-08-29 | 2017-09-26 | 因赛飞公司 | Method and apparatus for strengthening nervous function |
US10507321B2 (en) | 2014-11-25 | 2019-12-17 | Medtronic Bakken Research Center B.V. | Multilayer structure and method of manufacturing a multilayer structure |
US20160331326A1 (en) | 2015-02-13 | 2016-11-17 | National University Of Singapore | Flexible neural strip electrodes, flexible neural ribbon electrodes and compartment based embedded nerve tissue electrode interfaces for peripheral nerves |
US10622107B2 (en) | 2015-02-13 | 2020-04-14 | Medtronic, Inc. | Tools for medical device configuration |
EP3064131A1 (en) | 2015-03-03 | 2016-09-07 | BIOTRONIK SE & Co. KG | Combined vagus-phrenic nerve stimulation apparatus |
US9872989B2 (en) | 2015-04-02 | 2018-01-23 | The Florida International University Board Of Trustees | System and method for neuromorphic controlled adaptive pacing of respiratory muscles and nerves |
CN107921255B (en) | 2015-07-30 | 2021-02-26 | 波士顿科学神经调制公司 | User interface for custom-patterned electrical stimulation |
JP7039038B2 (en) | 2015-12-14 | 2022-03-22 | スティムディア メディカル, インコーポレイテッド | Electrical stimulation for retention and restoration of diaphragmatic function |
US10537735B2 (en) | 2016-04-29 | 2020-01-21 | Viscardia, Inc. | Implantable medical devices and methods for real-time or near real-time adjustment of diaphragmatic stimulation parameters to affect pressures within the intrathoracic cavity |
US10695564B2 (en) | 2016-06-02 | 2020-06-30 | Battelle Memorial Institute | Flexible sheet for neuromuscular stimulation |
US10492713B2 (en) | 2016-06-03 | 2019-12-03 | The Cleveland Clinic Foundation | Systems and methods for monitoring a depth of neuromuscular blockade |
US10207103B2 (en) | 2016-07-05 | 2019-02-19 | Pacesetter, Inc. | Implantable thin film devices |
US10898262B2 (en) | 2016-10-25 | 2021-01-26 | Biosense Webster (Israel) Ltd. | Catheter distal end made of plastic tube and flexible printed circuit boards |
US10293164B2 (en) | 2017-05-26 | 2019-05-21 | Lungpacer Medical Inc. | Apparatus and methods for assisted breathing by transvascular nerve stimulation |
US10195429B1 (en) | 2017-08-02 | 2019-02-05 | Lungpacer Medical Inc. | Systems and methods for intravascular catheter positioning and/or nerve stimulation |
AU2019217570A1 (en) | 2018-02-06 | 2020-09-03 | Stimit Ag | Electro-magnetic induction device and method of activating a target tissue |
-
2017
- 2017-08-02 US US15/666,989 patent/US10195429B1/en active Active
- 2017-09-14 US US15/704,439 patent/US10039920B1/en active Active
-
2018
- 2018-07-25 AU AU2018309630A patent/AU2018309630A1/en active Pending
- 2018-07-25 CN CN201880062545.1A patent/CN111225710A/en active Pending
- 2018-07-25 EP EP18752951.6A patent/EP3661589A2/en active Pending
- 2018-07-25 JP JP2020505459A patent/JP7175027B2/en active Active
- 2018-07-25 WO PCT/US2018/043661 patent/WO2019027757A2/en unknown
- 2018-12-17 US US16/222,299 patent/US11090489B2/en active Active
-
2020
- 2020-02-27 US US16/802,711 patent/US10926087B2/en active Active
-
2021
- 2021-07-09 US US17/371,316 patent/US20210330968A1/en active Pending
Patent Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8706235B2 (en) * | 2011-07-27 | 2014-04-22 | Medtronic, Inc. | Transvenous method to induce respiration |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2022179976A1 (en) * | 2021-02-23 | 2022-09-01 | B. Braun Melsungen Ag | Method for checking a position and/or an orientation of a catheter tip of a catheter |
Also Published As
Publication number | Publication date |
---|---|
US20190126038A1 (en) | 2019-05-02 |
WO2019027757A2 (en) | 2019-02-07 |
US10039920B1 (en) | 2018-08-07 |
US11090489B2 (en) | 2021-08-17 |
US10195429B1 (en) | 2019-02-05 |
US20210330968A1 (en) | 2021-10-28 |
US10926087B2 (en) | 2021-02-23 |
JP7175027B2 (en) | 2022-11-18 |
EP3661589A2 (en) | 2020-06-10 |
CN111225710A (en) | 2020-06-02 |
AU2018309630A1 (en) | 2020-03-19 |
JP2020529264A (en) | 2020-10-08 |
US20200188658A1 (en) | 2020-06-18 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US10926087B2 (en) | Systems and methods for intravascular catheter positioning and/or nerve stimulation | |
US11311730B2 (en) | Systems and related methods for optimization of multi-electrode nerve pacing | |
US11883658B2 (en) | Devices and methods for prevention, moderation, and/or treatment of cognitive injury | |
JP7462946B2 (en) | Systems and methods for strengthening respiratory muscles |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: LUNGPACER MEDICAL INC., CANADA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:THAKKAR, VIRAL S.;EVANS, DOUGLAS G.;GANI, MATTHEW J.;SIGNING DATES FROM 20170802 TO 20170803;REEL/FRAME:043211/0555 |
|
STCF | Information on status: patent grant |
Free format text: PATENTED CASE |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 4TH YR, SMALL ENTITY (ORIGINAL EVENT CODE: M2551); ENTITY STATUS OF PATENT OWNER: SMALL ENTITY Year of fee payment: 4 |