WO2015113027A2 - Cathéters à flexibilité accrue et dispositifs, systèmes et procédés associés - Google Patents

Cathéters à flexibilité accrue et dispositifs, systèmes et procédés associés Download PDF

Info

Publication number
WO2015113027A2
WO2015113027A2 PCT/US2015/013029 US2015013029W WO2015113027A2 WO 2015113027 A2 WO2015113027 A2 WO 2015113027A2 US 2015013029 W US2015013029 W US 2015013029W WO 2015113027 A2 WO2015113027 A2 WO 2015113027A2
Authority
WO
WIPO (PCT)
Prior art keywords
shaft
segment
longitudinal axis
neuromodulation
along
Prior art date
Application number
PCT/US2015/013029
Other languages
English (en)
Other versions
WO2015113027A3 (fr
Inventor
Rudy Beasley
Rajesh DHAMODHARASAMY
Justin Goshgarian
Vincent Ku
Bhavin NASIT
Original Assignee
Medtronic Ardian Luxembourg S.A.R.L.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Medtronic Ardian Luxembourg S.A.R.L. filed Critical Medtronic Ardian Luxembourg S.A.R.L.
Priority to EP15703210.3A priority Critical patent/EP3099263A2/fr
Publication of WO2015113027A2 publication Critical patent/WO2015113027A2/fr
Publication of WO2015113027A3 publication Critical patent/WO2015113027A3/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/00234—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery
    • A61B2017/00292—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery mounted on or guided by flexible, e.g. catheter-like, means
    • A61B2017/003—Steerable
    • A61B2017/00305—Constructional details of the flexible means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/00234—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery
    • A61B2017/00292—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery mounted on or guided by flexible, e.g. catheter-like, means
    • A61B2017/003—Steerable
    • A61B2017/00305—Constructional details of the flexible means
    • A61B2017/00309—Cut-outs or slits
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00831—Material properties
    • A61B2017/00867—Material properties shape memory effect
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00053—Mechanical features of the instrument of device
    • A61B2018/00214—Expandable means emitting energy, e.g. by elements carried thereon
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00345—Vascular system
    • A61B2018/00404—Blood vessels other than those in or around the heart
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00434—Neural system
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00505—Urinary tract
    • A61B2018/00511—Kidney
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00577—Ablation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2/958—Inflatable balloons for placing stents or stent-grafts

Definitions

  • the present technology is related to catheters, in particular, at least some embodiments are related to neuromodulation catheters having one or more cuts and/or other features that enhance flexibility, such as to facilitate intravascular delivery via transradial or other suitable percutaneous transluminal approaches.
  • the sympathetic nervous system is a primarily involuntary bodily control system typically associated with stress responses. Fibers of the SNS extend through tissue in almost every organ system of the human body and can affect characteristics such as pupil diameter, gut motility, and urinary output. Such regulation can have adaptive utility in maintaining homeostasis or in preparing the body for rapid response to en vironmental factors. Chronic activation of the SNS, however, is a common maladaptive response that can drive the progression of many disease states. Excessive activation of the renal SNS in particular has been identified experimentally and in humans as a likely contributor to the complex pathophysiology of hypertension, states of volume overload (e.g., heart failure), and progressive renal disease.
  • states of volume overload e.g., heart failure
  • Sympathetic nerves of the kidneys terminate in the renal blood vessels, the juxtaglomerular apparatus, and the renal tubules, among other structures. Stimulation of the renal sympathetic nerves can cause, for example, increased renin release, increased sodium reabsQiptlon, and reduced renal blood flow. These and other neural-regulated components of renal function are considerably stimulated in disease states characterized by heightened sympathetic tone. For example, reduced renal blood flow and glomerular filtration rate as a result of renal sympathetic efferent stimulation is likely a cornerstone of the loss of renal function in cardio-renal syndrome, (i.e., renal dysfunction as a progressive complication of chronic heart failure).
  • Pharmacologic strategies to thwart the consequences of renal sympathetic stimulation include centrally-acting sympatholytic drugs, beta blockers (e.g., to reduce renin release), angiotensin-converting enzyme inhibitors and receptor blockers (e.g., to block the action of angiotensin II and aldosterone activation consequent to renin release), and diuretics (e.g., to counter the renal sympathetic mediated sodium and water retention).
  • beta blockers e.g., to reduce renin release
  • angiotensin-converting enzyme inhibitors and receptor blockers e.g., to block the action of angiotensin II and aldosterone activation consequent to renin release
  • diuretics e.g., to counter the renal sympathetic mediated sodium and water retention.
  • FIG. 1 is a partially schematic perspective view illustrating a therapeutic system including a neuromodulation catheter configured in accordance with an embodiment of the present technology.
  • FIG. 2 is an enlarged partially cut-away side view of a shaft of the neuromodulation catheter shown in FIG. I illustrating a hypotube of the shaft and a cut extending along a helical path having varying pitch along the length of the shaft.
  • FIG. 3 is a two-dimensional representation of the helical path juxtaposed with a corresponding segment of the shaft shown in FIG. 2.
  • FIGS. 4 and 5 are two-dimensional representations of different portions of the cut shown in FIG. 2.
  • FIG. 6 is a partially schematic view of a neuromodulation catheter including a shaft having first and second shaft segments with different flexibilities configured in accordance with an embodiment of the present technology .
  • FIG. 7 A is a two-dimensional representation of a helical path juxtaposed with the first shaft segment shown in FIG. 6.
  • FIG. 7B is an enlargement of a portion of FIG. 7 A illustrating changes in slope along the helical path shown in FIG. 7A.
  • FIGS. 8, 9 and 10 are two-dimensional representations of different portions of a cut extending along the helical path shown in FIG. 7A.
  • FIGS. I I, 12A, 17, 19, 21 and 23 are two-dimensional representations of helical paths juxtaposed with corresponding shaft segments configured in accordance with several embodiments of the present technology.
  • FIG. 12B is an enlargement of a portion of FIG. 12A. illustrating changes in slope along the helical path shown in FIG. 12 A.
  • FIGS. 13-16 are two-dimensional representations of different portions of a cut extending along the helical path shown in FIG. 12A.
  • FIGS. 18, 20, 22 and 24 are two-dimensional representations of portions of cuts extending along the helical paths shown in FIGS. 17, 19, 21 and 23, respectively,
  • FIGS. 25-28 are two-dimensional representations of portions of cuts configured in accordance with several embodiments of the present technology.
  • FIGS. 29-31 are perspective views of shaft segments having guide wire exit openings with different positions relative to cuts configured in accordance with several embodiments of the present technology.
  • FIGS. 32 and 33 are perspective views of shaft segments including helically wound elongate members configured in accordance with several embodiments of the present technology.
  • FIGS. 34 and 35 are side profile views of helically wound elongate members having windings with different average helix angles configured in accordance with several embodiments of the present technology.
  • FIG. 36 is a side profile view of a helically wound elongate member having windings with different average helix angles on either side of a transition region configured in accordance with an embodiment of the present technology.
  • Neuromodulation catheters configured in accordance with at least some embodiments of the present technology include elongate shafts having one or more cuts and/or other features that enhance flexibility (e.g., bendability or other responsiveness to lateral force) without unduly compromising desirable axial stiffness (e.g., pushability or other responsiveness to axial force) and/or desirable torsional stiffness (e.g., torqueability or other responsiveness to torsional force).
  • a neuromodulation catheter configured in accordance with a particular embodiment of the present technology is sufficiently flexible in some respects to facilitate deployment via a relatively long and/or tortuous intravascular path without excessive resistance, while still being sufficiently stiff in other respects so as to allow intravascular navigation or other suitable manipulation via an extracorporeal handle.
  • Desirable axial stiffness can include, for example, the capability of the shaft to be advanced or withdrawn along the length of an intravascular path without significantly buckling or elongating.
  • Desirable torsional stiffness can include, for example, the capability of the shaft to distaily transfer rotational motion (e.g., from a handle at a proximal end portion of the shaft to a neuromodulation element operably connected to the shaft via a distal end portion of the shaft) with close correspondence (e.g., at least about one-to-one correspondence).
  • desirable torsional stiffness can include the capability of the shaft to distaily transfer rotational motion without causing whipping and/or diametrical deformation of the shaft.
  • Desirable axial and torsional stiffness together can facilitate predictable and control led transmi ssion of axi al and torsional force from the proximal end portion of the shaft toward the distal end portion of the shaft while a neuromodulation catheter is in use.
  • Metal hypodermic (needle) tubing aka hypotubing
  • hypotubing is commonly incorporated into small-diameter shafts of medical catheters to utilize the wire-like physical properties of such material along with the useable lumen extending therethrough.
  • solid-walled metal tubing also has known limitations regarding flexibility and kink resistance, and various designs have utilized slits, slots or other openings in the tubing wall to achieve improvements in flexibility.
  • Such modifications to the wall structure have always brought about compromises in physical properties in tension, compression, and torsion.
  • imparting flexibility can require unduly sacrificing axial stiffness and/or torsional stiffness.
  • creating a continuous helical cut in a relatively rigid hypotube of a shaft tends to increase the flexibility of the shaft, but, in some instances, the resulting coils between turns of the cut may also tend to separate to an undesirable degree in response to tension on the shaft and/or torsion on the shaft in at least one circumferential direction, in some cases, this separation can cause a permanent or temporary change in the length of the shaft (e.g., undesirable elongation of the shaft), a permanent or temporary diametrical deformation of the shaft (e.g., undesirable flattening of a cross-section of the shaft), and/or torsional whipping.
  • Such shaft behavior can interfere with intravascular navigation and/or have other undesirable effects on neuromodulation procedures.
  • neuromodulation catheters configured in accordance with at least some embodiments of the present technology can be well-suited for intravascular delivery to treatment locations (e.g., treatment locations within or otherwise proximate to a renal artery of a human patient) via transradial approaches (e.g., approaches that include the radial artery, the subclavian artery, and the descending aorta).
  • transradial approaches are typically more tortuous and longer than femoral approaches and at least some other commonly used approaches.
  • Transradial approaches can be desirable for accessing certain anatomy, but other types of approaches (e.g., femoral approaches) may be desirable in particularly tortuous anatomy or vessels having relatively small diameters. In some instances, however, use of transradial approaches can provide certain advantages over use of femoral approaches. In some cases, for example, use of transradial approaches can be associated with increased patient comfort, decreased bleeding, and/or faster sealing of the percutaneous puncture site relative to use of femoral approaches.
  • neuromodulation catheters configured in accordance with at least some embodiments of the present technology can be well suited for intravascular delivery via one or more other suitable approaches, such as other suitable approaches that are shorter or longer than transradial approaches and other suitable approaches that are less tortuous or more tortuous than transradial approaches.
  • neuromodulation catheters configured in accordance with at least some embodiments of the present technology can be well suited for intravascular delivery via brachial approaches and/or femoral approaches.
  • the combination of flexibility and desirable axial and torsional stiffness associated with neuromodulation catheters configured in accordance with at least some embodiments of the present technology can be beneficial, such as to accommodate anatomical differences between patients and/or to reduce vessel trauma during delivery, among other potential benefits.
  • FIGS. 1-36 Specific details of several embodiments of the present technology are described herein with reference to FIGS. 1-36. Although many of the embodiments are described herein with respect to devices, systems, and methods for intravascular renal neuromodulation, other applications and other embodiments in addition to those described herein are within the scope of the present technology. For example, at least some embodiments may be useful for intraluminal neuromodulation, for extravascular neuromodulation, for non-renal neuromodulation, and'Or for use in therapies other than neuromodulation. It should be noted that other embodiments in addition to those disclosed herein are within the scope of the present technology. For example, in still other embodiments, the technology described herein may be used in devices, systems and methods for stent delivery and balloon angioplasty.
  • embodiments of the present technology can have different configurations, components, and/or procedures than those shown or described herein.
  • a person of ordinary skill in the art will understand that embodiments of the present technology can have configurations, components, and/or procedures in addition to those shown or described herein and that these and other embodiments can be without several of the configurations, components, and'Or procedures shown or described herein without deviating from the present technology.
  • distal and proximal define a position or direction with respect to a clinician or a clinician's control device (e.g., a handle of a neuromodulation catheter).
  • distal and disally refer to a position distant from or in a direction away from a clinician or a clinician's control device.
  • proximal and proximally refer to a position near or in a direction toward a clinician or a clinician's control device.
  • FIG. 1 is a partially schematic perspective view illustrating a therapeutic system 100 configured in accordance with an embodiment of the present technology.
  • the system 100 can include a neuromodulation catheter 102, a console 104, and a cable 106 extending therebetween.
  • the neuromodulation catheter 102 can include an elongate shaft 108 having a proximal end portion 108a and a distal end portion 108b.
  • a handle 110 of the neuromodulation catheter 102 can be operably connected to the shaft 108 via the proximal end portion 108a, and a neuromodulation element 112 (shown schematically) of the neuromodulation catheter 102 can be operably connected to the shaft 108 via the distal end portion 108b.
  • the shaft 108 can be configured to locate the neuromodulation element 1 12 intravascuiarly at a treatment location within or otherwise proximate to a body lumen (e.g., a blood vessel, a duct, an airway, or another natural!)' occurring lumen within the human body), and the neuromodulation element 1 12 can be configured to provide or support a neuromodulation treatment at the treatment location.
  • a body lumen e.g., a blood vessel, a duct, an airway, or another natural
  • the shaft 108 and the neuromodulation element 112 can be 2, 3, 4, 5, 6, or 7 French or one or more other suitable sizes.
  • intravascular delivery of the neuromodulation catheter 102 includes percutaneously inserting a guide wire (not shown) into a body lumen of a patient and moving the shaft 108 and the neuromodulation element 1 12 along the guide wire until the neuromodulation element 1 12 reaches a suitable treatment location.
  • the neuromodulation catheter 102 can be a steerable or non-steerable device configured for use without a guide wire.
  • the neuromodulation catheter 102 can be configured for delivery via a guide catheter or sheath (not shown) or in another suitable manner.
  • the console 104 can be configured to control, monitor, supply, and/or otherwise support operation of the neuromodulation catheter 102.
  • the neuromodulation catheter 102 can be self-contained or otherwise configured for operation without connection to the console 104.
  • the console 104 can be configured to generate a selected form and/or magnitude of energy for delivery to tissue at the treatment location via the neuromodulation element 1 12 (e.g., via one or more energy delivery elements (not shown) of the neuromodulation element 1 12),
  • the console 104 can have different configurations depending on the treatment modality of the neuromodulation catheter 102.
  • the console 104 can include an energy generator (not shown) configured to generate radio frequency (RF) energy (e.g., monopolar and/or bipolar RF energy), pulsed energy, microwave energy, optical energy, ultrasound energy (e.g., intravaseularly delivered ultrasound, extracorporeal ultrasound, and/or high-intensity focused ultrasound (HIFUj), cryotherapeutic energy, direct heat energy, chemicals (e.g., drugs and/or other agents), radiation (e.g., infrared, visible, and/or gamma radiation), and/or another suitable type of energy.
  • RF radio frequency
  • RF radio frequency
  • the console 104 can include a refrigerant reservoir (not shown) and can be configured to supply the neuromodulation catheter 102 with refrigerant.
  • the console 104 can include a chemical reservoir (not shown) and can be configured to supply the neuromodulation catheter 102 with one or more chemicals.
  • the system 100 includes a control device 1 14 along the cable 106.
  • the control device 114 can be configured to initiate, terminate, and/or adjust operation of one or more components of the neuromodulation catheter 102 directly and/or via the console 104.
  • the control device 1 14 can be absent or can have another suitable location (e.g., within the handle 110).
  • the console 104 can be configured to execute an automated control algorithm 1 16 and/or to receive control instructions from an operator.
  • the console 104 can be configured to provide feedback to an operator before, during, and/or after a treatment procedure via an evaluation/feedback algorithm 118.
  • FIG. 2 is an enlarged partially cut-away side view of the shaft 108 illustrating a hypotube 120 concentrically disposed within an outside wall 121.
  • the hypotube 120 can be configured to reinforce the shaft 108 against collapsing from lateral compression.
  • the hypotube 120 can be made of a relatively strong material (e.g., nickel titanium (NiTi or nitinol)), stainless steel (e.g., 304 stainless steel), or another suitable metal).
  • the Irypotube 120 may be disposed within all or a portion of the shaft 108.
  • the hypotube 120 may only be disposed at a distal section of the shaft 108, and a proximal section of the shaft 108 may have a different arrangement and/or configuration, lubes made of relatively strong materials tend to be relati vely stiff (e.g., resistant to bending) when unmodified.
  • the shaft 108 can include a cut 122 extending at least partially through a wall thickness of the hypotube 120, the outside wall 121, or another suitable portion of the shaft 108.
  • the shaft 108 can have a longitudinal axis 124 and the cut 122 can follow a helical path 126 that extends about the longitudinal axis 124 (e.g., a coiled, spiral, or other similar form having two or more turns consistently or variably spaced along the longitudinal axis 124).
  • the cut 122 can be continuous or discontinuous along the helical path 126.
  • the shaft 108 can be cut along more than one helical path (e.g., a double helix having two or more helical paths having the same "hand" or chirality and spaced apart along the longitudinal axis 124),
  • the cut 122 can be formed, for example, using laser etching, electrical discharge machining, chemical etching, or other suitable techniques.
  • the hypotube 120 has an outer diameter of 0.813 mm (0.032 inch) and an inner diameter of 0.635 mm (0.025 inch). In other embodiments, the hypotube 120 can have other suitable dimensions.
  • FIG. 3 is a two-dimensional representation of the helical path 126 juxtaposed with a corresponding segment 127 of the shaft 108.
  • FIG. 3 is a representation of the helical path 126 and the corresponding segment 127 of the shaft 108 with the x-axis in FIG. 3 corresponding to the longitudinal axis 124 of the shaft 108 and the y-axis in FIG. 3 corresponding to the circumference of the shaft 108.
  • FIG. 3 is a two-dimensional representation of the helical path 126 juxtaposed with a corresponding segment 127 of the shaft 108.
  • FIG. 3 is a representation of the helical path 126 and the corresponding segment 127 of the shaft 108 with the x-axis in FIG. 3 corresponding to the longitudinal axis 124 of the shaft 108 and the y-axis in FIG. 3 corresponding to the circumference of the shaft 108.
  • FIG. 3 is a representation of the helical path 126 and the corresponding segment 127 of the
  • the helical path 126 can include a first portion 126a, a second portion 126b, and a third portion 126c (arranged distal to proximal).
  • the first portion 126a, the second portion 126b, and the third portion 126c can extend around portions of the longitudinal axis 124 corresponding to a first portion 127a, a second portion 127b, and a third portion 127c of the segment 127, respectively.
  • the first portion 127a is distal to the second and third portions 127b, 127c, and the second portion 127b is between the first and third portions 127a, 127c.
  • the first, second, and third portions 127a- 127c can be reversed or have another suitable arrangement.
  • the first, second, and third portions 127a- 127c can be directly adjacent to one another or spaced apart from one another along the longitudinal axis 124.
  • first portion 127a can be directly adjacent to or spaced apart from a distalmost portion of the shaft 108 (e.g., a junction between the shaft 108 and the neuromodulation element 1 12), and the third portion 127c can be directly adjacent to or spaced apart from a proximalmost portion of the shaft 108 (e.g., a junction between the shaft 108 and the handle 1 10).
  • first, second, and third portions 126a- 126c of the helical path 126 can have different slopes when transposed t vo-dimensionaliy.
  • slopes can correspond to the axial density (e.g., frequency or pitch angle) of features (e.g., turns, shapes, types, sizes, dimensions, or other suitable features) of the cut 122 along the longitudinal axis 124.
  • the first portion 126a can have a greater slope than the second portion 126b
  • the third portion 126c can be curved with a slope that gradually transitions between the slopes of the first and second portions 126a, 126b.
  • the cut 122 can have a greater axial density of features at a portion of the longitudinal axis 124 corresponding to the first portion 127a of the segment 127 than along a portion of the longitudinal axis 124 corresponding to the third portion 127c of the segment 127.
  • the axial density of features of the cut 122 along the longitudinal axis 124 can increase gradually or in another suitable manner along the second portion 127b from the third portion 127c toward the first portion 127a.
  • gradually increasing or otherwise transitioning the axial density of turns, shapes, slope, type, size/dimension, or other suitable features of the cut 122 may reduce focused stress on the shaft 108, which can reduce or eliminate kinking or other undesirable behavior of the shaft 108 during movement (e.g., bending).
  • a greater axial density of features can correspond to greater flexibility than a lesser axial density of features.
  • a distance along the longitudinal axis 124 between the neuromodulator! element 1 12 and the segment 127 or a portion thereof e.g., the first, second, or third portions 127a-c
  • the segment 127 or portion thereof tends to be disposed in or near a particular anatomical location when the neuromodulation catheter 102 is in use.
  • the distance along the longitudinal axis 124 between the neuromodulation element 112 and the segment 127 or portion thereof can be selected such that the segment or portion thereof tends to be at least proximate to a relatively sharply angled or otherwise relatively tortuous anatomic region of an approach (e.g., a transradial or other suitable approach) when the neuromodulation element 1 12 is at a selected treatment location (e.g., a treatment location within or otherwise proximate to a renal artery of a human patient).
  • a selected treatment location e.g., a treatment location within or otherwise proximate to a renal artery of a human patient.
  • the relatively sharply angled or otherwise relatively tortuous region can be a region within or otherwise proximate to a subclavian artery (e.g., a portion of a subclavian artery adjacent to the descending aorta), an ostium of a renal artery, or another suitable anatomical feature.
  • the axial density of features of the cut 122 along the l ength of the shaft 108 and the relative flexibilities of shaft 108 along its length can be selected to facilitate transradial catheterization or deployment of the neuromodulation catheter 102 via another suitable approach.
  • an axial density of features of the cut 122 along the longitudinal axis 124 varies along the length of the shaft 108 (e.g., to tailor the shaft 108 to the tortuosity or other geometry of different portions of a transradial or other suitable approach).
  • the axial density of features of the cut 122 can be consistent along the length of the shaft 108 (e.g., to increase the overall flexibility of the shaft 108).
  • FIG. 4 is a two-dimensional representation of a portion of the cut 122 at the first portion 126a of the helical path 126.
  • a two-dimensional representation is as if the shaft were rolled over a flat surface to leave an imprint of the cut shape therein.
  • this type of two-dimensional representation can be used as input for an automated manufacturing process used to form cut shapes along a path in a tubular workpiece.
  • the shaft 108 can include two or more first cut shapes 128 and two or more second cut shapes 130 interspersed along the helical path 126, with the first and second cut shapes 128, 130 forming portions of the cut 122.
  • the first cut shapes 128 can be configured to at least partially interlock to thereby resist deformation in response to a set of three types of feree acting on the shaft 108
  • the second cut shapes 130 can be configured to at least partially interlock to thereby resist deformation in response to a different, complementary set of three types of force acting on the shaft 108.
  • the sets can be different combinations of (a) compression along the longitudinal axis 124, (b) tension along the longitudinal axis 124, (c) torsion in a first circumferential direction perpendicular to the longitudinal axis 124, and (d) torsion in a second, opposite circumferential direction perpendicular to the longitudinal axis 124.
  • the first cut shapes 128 can be configured to at least partially resist deformation in response to compression on the shaft 108, tension on the shaft 108, and torsion on the shaft 108 in the first circumferential direction
  • the second cut shapes 130 can be configured to at least partially resist deformation in response to compression on the shaft 108, torsion on the shaft 108 in the first circumferential direction, and torsion on the shaft 108 in a second circumferential direction opposite to the first circumferential direction.
  • the first cut shapes 128 can be less resistant to deformation in response to torsion on the shaft 108 in the second circumferential direction than the second cut shapes 130.
  • the second cut shapes 130 can be less resistant to deformation in response to tension on the shaft 108 than the first cut shapes 128.
  • the first and second cut shapes 128, 130 can provide the shaft 108 with sufficient resistance to deformation in response to all types of axial and torsional force that may act on the shaft 108 during use of the neuromodulation catheter 102,
  • the first and second cut shapes 128, 130 are sinusoidal and have amplitudes with different (e.g., perpendicular) orientations relative to the longitudinal axis 124.
  • the first and second cut shapes 128, 130 can have other suitable forms.
  • the individual first cut shapes 128 can include a first peak 132 (e.g., a first finger) and a second peak 134 (e.g., a second finger) with a first interface 136 therebetween.
  • the first interface 136 can be perpendicular to the longitudinal axis 124 (FIG. 2).
  • the individual second cut shapes 130 can include a third peak 138 (e.g., a third finger) and a fourth peak 139 (e.g., a fourth finger) with a second interface 140 therebetween.
  • the second interface 140 can be parallel to the longitudinal axis 124.
  • the first and second interfaces 136, 140 can have other suitable angles relative to the longitudinal axis 124, such as other suitable angles in which an angle between the first interface 136 and the longitudinal axis 124 is greater than an angle between the second interface 140 and the longitudinal axis 124.
  • the orientations of the first and second peaks 132, 134 can be reversed and/or in some or all of the second cut shapes 130 the orientations of the third and fourth peaks 138, 139 can be reversed.
  • the first and second peaks 132, 134 extend vertically downward and upward, respectively and the third and fourth peaks 138, 139 extend to the right and to the left, respective!)'.
  • the first and second peaks 132, 134 can extend vertically upward and downward, respectively and the third and fourth peaks 138, 139 can extend to the left and to the right, respectively.
  • Other cut shapes with chiraiity described herein can be similarly modified. With reference again to FIG.
  • the first and second cut shapes 128, 130 can be configured to at least partially resist deformation in response to forces perpendicular to the first and second interfaces 136, 140, respectively.
  • such forces can cause the first and second peaks 132, 134 or the third and fourth peaks 138, 139 to at least partially interlock and thereby prevent or reduce widening of the cut 122.
  • FIG. 5 is a two-dim.ensi.onal representation of a portion of the cut 122 at the second portion 126b of the helical path 126.
  • an average length of the first interfaces 136, an average length of the second interfaces 140, or both can be different at different portions of the helical path 126.
  • the average length of the second interfaces 140 can be greater among the second cut shapes 130 along the third portion 126c of the helical path 126 and the third portion 127c of the segment 127 of the shaft 108 than among the second cut shapes 130 along the first portion 126a of the helical path 126 and the first portion 127a of the segment 127.
  • the average length of the first interfaces 136, the second interfaces .140, or both are selected based on different axial densities of features of the cut 122 at different segments of the shaft 108. For example, when the axial density is greater, the lengths of the first and second interfaces 136, 140 can be more restricted than when the axial density is lower (e.g., so as to avoid overlapping at adjacent turns).
  • enhancing the flexibility of a shaft using a helical cut may reduce axial and torsional stiffness of the shaft to some degree even when cut shapes or features configured in accordance with embodiments of the present technology are present. Accordingly, it can be useful to include a cut along a segment of a shaft that is intended to extend through particularly tortuous anatomy, while leaving another segment of the shaft uncut or having a cut that imparts relatively little flexibility to the shaft. In this way, while the axial and torsional stiffness of the shaft may be compromised to some degree in favor of enhanced flexibility along a part of the shaft for which the enhanced flexibility is needed, the degree to which the overall axial and torsional stiffness of the shaft is compromised may be minimized or at least reduced.
  • FIG. 6, is a partially schematic view of a neuromodulation catheter 141 including a shaft 142 having first and second shaft segments 143, 144 with different flexibilities configured in accordance with an embodiment of the present technology.
  • the second shaft segment .144 can be proximal to the first shaft segment .143 and can be less flexible (e.g., more resistant to deflection in response to lateral force) than the first shaft segment 143.
  • the usefulness of enhanced flexibility may tend to diminish proximally.
  • the first shaft segment 143 may need to extend through a junction between a subclavian artery and the descending aorta in order to deliver the neuromodulation element 112 to a treatment location within a renal artery of a patient.
  • the second shaft segment 144 may remain proximal to this junction.
  • the shaft 142 includes a cut (not shown) at the first shaft segment 143 and a different cut (not shown) at the second shaft segment 144 that imparts significantly less flexibility to the shaft 142 than the cut at the first shaft segment 143.
  • the first shaft segment 143, the second shaft segment 144, or both can be uncut. This may be the case, for example, when the relative flexibilities of the first and second shaft segments 143, 144 are influenced by factors in addition to or instead of the presence of cuts.
  • the location of a transition between the first and second shaft segments 143, 144 can be selected so that the second shaft segment 144 remains proximal to the subclavian artery when the shaft 142 extends along a transradial approach.
  • the first and second shaft segments 143, 144 together make up the entire length of the shaft 142 from the handle 1 10 to the neuromodulation element 112.
  • the shaft 142 may include additional segments.
  • the first shaft segment 143 can be directly adjacent to or otherwise proximate to (e.g., within about 3 cm (1 .181 inches) of) the neuromodulation element 112.
  • the second shaft segment 144 can be directly adjacent to or otherwise proximate to (e.g., within about 3 cm (1.181 inches) of) the handle 1 10.
  • the first shaft segment 143 has a length from about 30 cm (11.81 inches) to about 80 cm (31.5 inches) (e.g., from about 40 cm (15.75 inches) to about 70 cm (27.56 inches)) and the second shaft segment 144 has a length greater than about 40 cm (15.75 inches) (e.g., greater than about 50 cm (19.69 inches)).
  • the first shaft segment 143 has a length of about 50 cm (19.69 inches) and the second shaft segment 144 has a length of about 80 cm (31 .5 inches).
  • the first and second shaft segments 143, 144 can have other suitable lengths.
  • the shaft 142 can include a cut having a greater axial density of features at the first shaft segment 143 than at the second shaft segment 144.
  • the axial density of features at the second shaft segment 144 can be relatively low when the second shaft segment 144 is cut in a manner that imparts relatively little flexibility to the shaft 142 or the axial density can be zero when the second shaft segment 144 is uncut.
  • the transition from the first shaft segment 143 to the second shaft segment 144 can be gradual or abrupt.
  • a gradual transition in axial density may reduce focused stress and thereby reduce kinking or other undesirable behavior during movement (e.g., bending) of the shaft 142.
  • Such gradual transitioning can include, for example, changing the axial density of features continuously or incrementally.
  • FIG. 7A is a two-dimensional representation of a helical path 146 juxtaposed with the first shaft segment 143 shown in FIG. 6, Similar to the helical path 126 shown in FIG. 3, the slope of the helical path 146, when transposed two-dimensional ly, can correspond to an axial density of features along a longitudinal axis 145 of the shaft 142.
  • the helical path 146 can have portions 146a-c (arranged distal to proximal) corresponding, respectively, to portions 143a-c of the first shaft segment 143,
  • FIG. 7B is an enlargement of a portion of FIG. 7A illustrating changes in slope along the helical path 146. As shown in FIG.
  • the slope of the helical path 146 can be consistent along the portion 146a at a first value, consistent along the portion 146b at a second, lesser value, and consistent along the portion 146c at a third, still lesser value.
  • the first value can be, for example, from about 15 degrees to about 40 degrees.
  • the second value can be, for example, from about 2 degrees to about 6 degrees less than the first value.
  • the third value can be, for example, from about 2 degrees to about 6 degrees less than the second value.
  • the first value is about 40 degrees
  • the second value is about 36 degrees
  • the third value is about 32 degrees.
  • the length of the portion 143a can be, for example, from about 20 cm (7.874 inches) to about 70 cm (27,56 inches) or from about 30 cm (11.81 inches) to about 60 cm (23.62 inches).
  • the individual lengths of the portions 143b, 143c can be, for example, from about 2 cm (0.7874 inch) to about 7 cm (2.756 inches).
  • the length of the portion 143a is 40 cm ( 15.75 inches) and the individual lengths of the portions are 5 cm (1 .969 inches).
  • the helical path 146, the shaft 142, and portions thereof may have other suitable dimensions, such as dimensions within about 10%, 20% or 30% of the dimensions in the illustrated embodiment.
  • FIGS. 8, 9 and 10 are two-dimensional representations of different portions of a cut 147 extending along the helical path 146.
  • the portions of the cut 147 shown in FIGS, 8, 9 and 10 can be positioned at the portions 146a, 146b, 146c of the helical path 146, respectively.
  • the features of the cut 147 can be similar to the features described above with reference to FIG. 5.
  • the cut 147 can have dimensions A-l, B-l , C-l, and D-l at the portion 146a of the helical path 146.
  • the cut 147 can have dimensions A-2, B-2, C-2, and D-2 at the portion 146b of the helical path 146.
  • the cut 147 can have dimensions A-3, B-3, C-3, and D-3 at the portion 146c of the helical path 146.
  • a ⁇ l is 0.813 mm (0.032 inch);
  • A-2 and A-3 individually are 0.09144 cm (0.036 inch);
  • B-l, B-2 and B-3 individually are 0.02286 cm (0.009 inch);
  • C-l is 0.3048 cm (0.120 inch);
  • C-2 is 0.381 cm (0.150 inch);
  • C-3 is 0.3429 cm (0.135 inch);
  • D-l is 40 degrees;
  • D-2 is 32 degrees;
  • D-3 is 36 degrees; the radius of curvature of the cut 147 at the ends of the individual first, second, third, and fourth peaks 132, 134, 138,
  • the cut 147 can have other suitable dimensions, such as dimensions within about 10%, 20% or 30% of the dimensions in the illustrated embodiment.
  • the width of the cut 147 can be, for example, from about 0.001016 cm (0.0004 inch) to about 0.003556 cm (0.0014 inch), from about 0.001524 cm (0.0006 inch) to about 0.003048 cm (0.0012 inch), or within another suitable range.
  • A-l can be less than A-2 and A-3. Similarly, the length of the second interface
  • the lengths of the second interfaces 140 increase abruptly in a proximal direction along the longitudinal axis 145.
  • the lengths of the second interfaces 140 can increase gradually in a proximal direction along the longitudinal axis 145.
  • the lengths of the second interfaces 140 can increase gradually along all or a portion of the length of the first shaft segment 143.
  • the lengths of the second interfaces 140 can remain consistent.
  • FIGS. 11, 12A, 17, 19, 21 and 23 are two-dimensional representations of helical paths 148, 151, 156, 162, 180, 193, respectively, juxtaposed with corresponding shaft segments 149, 153, 158, 164, 182, 194, respectively, in accordance with several embodiments of the present technology.
  • FIG. 12B is an enlargement of a portion of FIG. 1.2 A illustrating changes in slope along the helical path .151.
  • FIGS. 13-16 are two-dimensional representations of different portions of a cut 154 extending along the helical path 151.
  • the helical paths 146, 148, 151, 156, 162, 180, 193 shown in FIGS. 7A, 11, 12A, 17, 19, 21 and 23 illustrate several additional examples of transitions in axial densities of features along longitudinal axes 145 corresponding to shaft segments.
  • the slope of the helical path 146 decreases proximally in two steps.
  • the slope of a helical path can decrease proximally in more than two steps (e.g., three steps, four steps, or a greater number of steps).
  • the slope of the helical path 151 decreases proximally in three steps.
  • the slope of the helical path 151 decreases proximally in seven steps.
  • the slope of a helical path can decrease proximally in a continuous or nearly continuous manner such that all or a portion of the helical path is curved.
  • the slope of the helical path 148 decreases continuously in a proximal direction along the entire length of the corresponding shaft segment 149.
  • the locations of the steps along the longitudinal axis 145 of the corresponding shaft segment can have various suitable positions.
  • the portion 143a of the first shaft segment 143 spans over half the length of the first shaft segment 143.
  • the portions 143b, 143 c of first shaft segment 143 are of equal length and together span less than a quarter of the length of the first shaft segment 143.
  • the portions 153a-! 53d of the shaft segment 153 each have different lengths along the longitudinal axis 145 of the shaft segment 153, with their lengths decreasing proximally from the portion 153a to the portion 153d.
  • the portions 164a- 164c of the shaft segment 164 each have different lengths along the longitudinal axis 145 of the shaft segment 164, with their lengths decreasing proximally from the portion 164a to the portion 164c.
  • the portions 182a- 182c of the shaft segment 182 each have different lengths along the longitudinal axis 145 of the shaft segment 182, with their lengths decreasing proximally from the portion 182a to the portion 182c.
  • the embodiment illustrated in FIG. 19 the portions 164a- 164c of the shaft segment 164 each have different lengths along the longitudinal axis 145 of the shaft segment 164, with their lengths decreasing proximally from the portion 182a to the portion 182c.
  • the portions 194a 194c of the shaft segment 194 each have different lengths along the longitudinal axis 145 of the shaft segment 194, with their l engths decreasing proximally from the portion 194a to the portion 194c.
  • the portions 158a-158h of the shaft segment 158 have approximately equal lengths along the longitudinal axis 145 of the shaft segment 158.
  • the slopes of the helical path 151 along its portions 151a, 151b, 151 c, and 15 I d are 36 degrees, 32.5 degrees, 27 degrees, and 23 degrees, respectively, and the lengths of the portions 153a, 153b, 153c, and 153d of the shaft segment 153 are 30 cm (1 1 .812 inches), 9.855 cm (3.880 inches), 5.885 cm (2.317 inches), and 4.092 cm (1.61 1 inches), respectively, in the embodiment shown in FIG.
  • the slopes of the helical path 156 along its portions 156a, 156b, 156c, 156d, 156e, 1 6f, I56g, and 1 6h are 36 degrees, 32 degrees, 27 degrees and 23 degrees, 20 degrees, 17.7 degrees, 15.8 degrees, and 15 degrees, respectively, and the lengths of the portions 158a, 158b, 158c, 158d, 158e, 158f, and 158g of the shaft segment 158 are 65 mm (2.559 inches), 62.2 mm (2.449 inches), 62.5 mm (2.461 inches), 62.5 mm (2.461 inches), 62.6 mm (2.465 inches), 62.5 mm (2.461 inches), 62.5 mm (2.461 inches), and 62.5 mm (2.461 inches), respectively.
  • the slopes of the helical path 162 along its portions 162a, 162b, and 162c are 36 degrees, 32 degrees, and 27 degrees, respectively, and the lengths of the portions 164a, 164b, and 164c of the shaft segment 164 are 180 mm (7.087 inches), 174 mm (6.85 inches), and 146 mm (5.748 inches), respectively.
  • the slopes of the helical path 180 along its portions 180a, 180b, and 180c are 29.5 degrees, 27 degrees, and 24.9 degrees, respectively, and the lengths of the portions 182a, 182b, and 182c of the shaft segment 182 are 179 mm (7.047 inches), 174 mm (6.85 inches), and 145 mm (5.709 inches), respectively. Similar to the embodiment shown in FIG. 21 , in the embodiment shown in FIG.
  • the slopes of the helical path 193 along its portions 193a, 193b, and 193c are 29.5 degrees, 27 degrees, and 24.9 degrees, respectively, and the lengths of the portions 194a, 194b, and 194c of the shaft segment 194 are 179 mm (7.047 inches), 174 mm (6.85 inches), and 145 mm (5.709 inches), respectively.
  • the helical paths 151, 156, 162, 180, 193 can have other suitable dimensions, such as dimensions within about 10%, 20% or 30% of the dimensions in the illustrated embodiments.
  • the portions of the cut 154 shown in FIGS. 13, 14, 15, and 16, respectively can be positioned at the portions 153a, 153b, 153c, and 153d, respectively, of the shaft segment 153.
  • the features of the cut 154 can be similar to the features described above with reference to FIGS. 5 and 8-10.
  • the cut 154 can have dimensions A-4, B-4, C-4, and D-4 at the portion 15 la of the helical path 151 .
  • the cut 154 can have dimensions A-5, B-5, C-5, and D-5 at the portion 151b of the helical path 151.
  • FIG. 13 the cut 154 can have dimensions A-5, B-5, C-5, and D-5 at the portion 151b of the helical path 151.
  • the cut 154 can have dimensions A-6, B ⁇ 6, C-6, and D ⁇ 6 at the portion 1 1c of the helical path 151. As shown in FIG. 16, the cut 154 can have dimensions A-7, B-7, C-7, and D-7 at the portion 15 Id of the helical path 151.
  • A-4 and A-5 individually are 0.0762 cm (0.030 inch); A-6 is 0.0889 cm (0.035 inch); A-7 is 0.1143 cm (0.045 inch); B-4, B-5, B-6, and B-7 individually are 0.0381 cm (0.015 inch); C-4, C-5, and C-6 individually are 0.508 cm (0.200 inch); C-7 is 0.635 cm (0.250 inch); D-5 is 36 degrees (corresponding to a pitch of 3.5 mm (0.1378 inch) per revolution); D-6 is 32.5 degrees (corresponding to a pitch of 4.0 mm (0.1575 inch) per revolution); D-7 is 27 degrees (corresponding to a pitch of 5.0 mm (0, 1969 inch) per revolution); D-8 is 23 degrees (corresponding to a pitch of 6.0 mm (0.2362 inch) per revolution); the portions 151a, 151b, 151c, and !
  • the 51d of the helical path 151 includes 73, 23, 13, and 7 pairs, respectively, of the first and second cut shapes 128, 130; the radius of curvature of the cut 154 at the ends of the individual first, second, third, and fourth peaks 132, 134, 138, 139 is 0.02032 cm (0.008 inch); and the radius of curvature of the cut 154 where the second cut shape 130 meets the helical path 151 toward an adjacent second cut shape 130 is 0,0254 cm (0,010 inch).
  • the cut 154 can have other suitable dimensions, such as dimensions within about 10%, 20% or 30% of the dimensions in the illustrated embodiment.
  • the width of the cut 154 can be, for example, from about 0.001016 cm (0.0004 inch) to about 0.003556 cm (0.0014 inch), from about 0.001524 cm (0.0006 inch) to about 0.003048 cm (0.0012 inch), or within another suitable range.
  • the features of the cut 160 shown in FIG. 18 can be similar to the features described above with reference to FIGS. 5, 8-10, and 13-16.
  • the cut 160 can have dimensions D-8, E-8, F-8, and G-8.
  • D-8 is 36 degrees (corresponding to a pitch of 3.5 mm (0.1378 inch) per revolution), 32 degrees (corresponding to a pitch of 4.0 mm (0.1575 inch) per revolution), 27 degrees (corresponding to a pitch of 5.0 mm (0.1969 inch) per revolution), 23 degrees (corresponding to a pitch of 6.0 mm (0.2362 inch) per revolution), 20 degrees (corresponding to a pitch of 7.0 mm (0.2756 inch) per revolution), 17.7 degrees (corresponding to a pitch of 8.0 mm (0.315 inch) per revolution), 15.8 degrees (corresponding to a pitch of 9.0 mm (0.3543 inch) per revolution), and 15 degrees (corresponding to a pitch of 9.5 mm (0.374 inch) per revolution), respectively; at the individual portions 156a-156h of the helical path 156, E ⁇ 8 is 36 degrees (corresponding to a pitch of 3.5 mm (0.1378 inch) per revolution), 32 degrees (corresponding to a pitch of 4.0 mm (0.1575 inch) per revolution), 27 degrees (corresponding to
  • the width of the cut 160 can be, for example, from about 0.001016 cm (0.0004 inch) to about 0.003556 cm (0.0014 inch), from about 0.001524 cm (0,0006 inch) to about 0.003048 cm (0.0012 inch), or within another suitable range.
  • the cuts 166, 184, 195 shown in FIGS. 20, 22 and 24 include repeating series of cut shapes 168, 186, 196, respectively. Unlike the cuts 122, 147, 154, 160 described above with reference to FIGS. 5, 8-10, 13-16, and 18, the cuts 166, 184, 195 do not include alternating patterns of different types of cut shapes. Instead of using combinations of different types of cut shapes to impart resistance to complementary sets of fewer than all types of axial and torsional force that may act on a shaft segment, the individual cuts 166, 184, 195 may rely on a single type of cut shape that imparts resistance to all or nearly all types of axial and torsional force that may act on a shaft segment.
  • a single type of cut shape that imparts resistance to all or nearly all types of axial and torsional force that may act on a shaft segment can often be disposed at a greater axi al density than a comparable combination of cut shapes (e.g., a pair of the first and second cut shapes 128, 130 shown in FIGS, 5, 8-10, 13-16, and 18). In at least some cases, this may facilitate relatively gradual changes in flexibility along the longitudinal axis of a shaft segment,
  • the cut shapes 168 can include a first peak 170 (e.g., a first finger), a second peak 172 (e.g., a second finger), and an interface 174 therebetween.
  • the first and second peaks 170, 172 can curve away from the helical path 162 in different (e.g., opposite) directions.
  • the first peak 170 extends away from the helical path 162 to one side and the second peak 172 extends away from the helical path 162 to the opposite side. Both the first and second peaks 170, 172 begin extending from the helical path 162 oriented perpendicularly to the helical path 162.
  • the first peak 170 transitions toward extending parallel to the helical path in a distally leaning direction and the second peak transitions toward extending parallel to the helical path in a proximal ly leaning direction.
  • the first peak 170 partially encircles a first tab 176 and the second peak 172 partially encircles a second tab 178.
  • the first and second peaks 170, 172 are rounded and hook-shaped. In other embodiments, the first and second peaks 170, 172 can have other suitable forms,
  • the cut 1 6 can have dimensions D-9 and G-9.
  • D-9 is 36 degrees (corresponding to a pitch of 3,5 mm (0.1378 inch) per revolution), 32 degrees (corresponding to a pitch of 4.0 mm (0.1575 inch) per revolution), and 27 degrees (corresponding to a pitch of 5.0 mm (0.1969 inch) per revolution), respectively;
  • G ⁇ 9 is 0.1092 cm (0,043 inch), 0,1499 cm (0.059 inch), and 0.1524 cm (0,060 inch), respectively;
  • the individual portions 164a, 164b, and 164c of the helical path 162 include 70, 49, and 37, respectively, of the cut shapes 168; and the radius of curvature of the individual first and second tabs 176, 178 is 0.0127 cm (0.005 inch).
  • the cut 166 can have other suitable dimensions, such as dimensions within about 10%, 20% or 30% of the dimensions in the illustrated embodiment.
  • the width of the cut 166 can be, for example, from about 0.001016 cm (0.0004 inch) to about 0.003556 cm (0.0014 inch), from about 0,001524 cm (0,0006 inch) to about 0.003048 cm (0.0012 inch), or within another suitable range.
  • the cut shapes 186 can include a single peak 188 (e.g., a finger) that extends away from the helical path 180 and defines a tab 190 having a neck 191 and a head 192, with the head 192 being positioned further from the helical path 180 than the neck 191.
  • the neck 191 can be narrower than the head 192 along a line parallel to the helical path 180. This configuration can allow portions of the shaft segment 182 along opposite sides of the cut 184 to at least partially interlock thereby preventing or reducing undesirable widening of the cut 184.
  • the peaks 188 and the tabs 190 can extend away from the helical path 180 in the same direction from one cut shape 186 to the next along the helical path 180.
  • the peaks 188 and the tabs 190 extend away from the helical path 180 leaning proximally.
  • the peaks 188 and the tabs 190 can extend away from the helical path 180 leaning distaliy.
  • the peaks 188 and the tabs 190 can extend away from the helical path 180 in different (e.g., opposite) directions from one cut shape 186 to the next along the helical path 180.
  • the cut 184 can have dimensions D-10, G-10, H-10, 1-10, and J-10.
  • H-10 is the distance from the helical path 180 to a focal centerpoint of a curved portion of the cut shape 186 adjacent to the head 192.
  • I- 10 is the distance between focal centerpoints of curved portions of the cut shape 186 adjacent to opposite sides of the transition between the head 192 and the neck 191 .
  • J-10 is the distance between focal centerpoints of curved, portions of the cut shape 186 adjacent to opposite sides of the neck 191.
  • D-10 is 29.5 degrees (corresponding to a pitch of 4.5 mm (0.1772 inch) per revolution), 27 degrees (corresponding to a pitch of 5.0 mm (0.1969 inch) per revolution), and 24.9 degrees (corresponding to a pitch of 5.5 mm (0.2165 inch) per revolution), respectively;
  • G-10 is 1.098 mm (0.04323 inch), 1 .488 mm (0.05858 inch), and 1.523 mm (0.05996 inch), respecti vely;
  • H-10 is 0.225 mm (0.008858 inch);
  • at the individual portions 182a- 182c of the helical path 182, 1- 10 is 0.697 mm (0.02744 inch); at the individual portions 182a- 182c of the helical path 182, J
  • the width of the cut 184 can be, for example, from about 0.001016 cm (0.0004 inch) to about 0.003556 cm (0.0014 inch), from about 0.001524 cm (0.0006 inch) to about 0.003048 cm (0.0012 inch), or within another suitable range.
  • the cut shapes 196 can include a single peak 197 (e.g., a finger) that extends away from the helical path 193 and defines a tab 198 having a neck 199 and a head 200, with the head 200 being positioned further from the helical path 193 than the neck 199.
  • the neck 199 can be narrower than the head 200 along a line parallel to the helical path 193.
  • the configuration shown in FIG. 24 can allow portions of the shaft segment 194 along opposite sides of the cut 195 to at least partially interlock thereby preventing or reducing undesirable widening of the cut 195.
  • the peaks 197 and the tabs 198 can extend away from the helical path 193 in the same direction from one cut shape 196 to the next along the helical path 193.
  • the peaks 197 and the tabs 198 extend away from the helical path 193 leaning proximally.
  • the peaks 197 and the tabs 198 can extend away from the helical path 193 leaning distally.
  • the peaks 197 and the tabs 198 can extend away from the helical path 193 in different (e.g., opposite) directions from one cut shape 196 to the next along the helical path 193.
  • the heads 200 of the cut shapes 196 can be flat rather than rounded.
  • the individual tabs 198 and corresponding cut shapes 196 can comprise a wedge- shaped arrangement with the tabs 198 including a wedge-shaped portion (i.e., a "tail") at the head 200 and a restricted portion at the neck 199.
  • the cut shapes 196 can form recesses or sockets (i.e., "tail sockets") complementary to the tabs 198.
  • the tabs 198 and cut shapes 196 may fit snugly with very little room between the portions of the shaft segment 194 at opposite sides of the cut 195. In other embodiments, however, there may be some space between at least a portion of at least some of the wedge-shaped portions and the complementary sockets, such as to allow some amount of relative movement between the portions of the shaft segment 194 at opposite sides of the cut 195.
  • the cut 195 can have dimensions D-l 1 , G-l 1 , -l 1, and L-l 1 .
  • the cut 195 can have other suitable dimensions, such as dimensions within about 10%, 20% or 30%) of the dimensions in the illustrated embodiment.
  • the width of the cut 195 can be, for example, from about 0.001016 cm (0.0004 inch) to about 0.003556 cm (0.0014 inch), from about 0.001524 cm (0.0006 inch) to about 0.003048 cm (0.0012 inch), or within another suitable range.
  • FIGS. 25-28 are two-dimensional representations of portions of cuts configured in accordance with several embodiments of the present technology.
  • a shaft 108 includes an uncut region 201 with the first and second cut shapes 128, 130 positioned along portions of a helical path on either side of the uncut region 201.
  • the uncut region 201 can be one of many uncut regions 201 interspersed among the first and second cut shapes 128, 130 along the helical path.
  • the first and second cut shapes 128, 130 can be portions of a continuous cut.
  • the first and second cut shapes 128, 130 can be in suitable patterns along the helical path other than one-to-one alternating patterns.
  • Suitable patterns can include, for example, random patterns, non-random patterns, two-to-one alternating patterns, two-to-two alternating patterns, and three-to-two alternating patterns, among others. Furthermore, the spacing between adjacent first and second cut shapes 128, 130 can be consistent or variable. [0062] Referring next to FIG, 27, a shaft can include two or more cut shapes 202 and two or more cut shapes 204 interspersed along a helical path. Similar to the cut shapes 168, 186 shown in FIGS. 20 and 22, the individual cut shapes 202 can be configured to fully interlock rather than partially interlock.
  • the individual cut shapes 202 can be configured to at least partially resist deformation in response to compression on the shaft, tension on the shaft, torsion on the shaft in the first circumferential direction, and torsion on the shaft in the second circumferential direction.
  • the shaft can include tabs 206 (e.g., protrusions, lobes, or other suitable structures) adjacent to the cut shapes 202, with the cut shapes 202 defining the tabs 106 by forming recesses complementary to the tabs 206.
  • the individual tabs 206 can include a flared portion 206a (e.g., a rounded head portion) and a restricted portion 206b (e.g., a rounded neck portion), or other suitable structures.
  • the cut shapes 204 can be sinusoidal and have amplitudes oriented perpendicularly to the helical path.
  • the individual cut shapes 204 can include a first peak 208 and a second peak 210 with an interface 212 therebetween that is diagonal relative to a longitudinal axis of the shaft and perpendicular to the helical path.
  • a shaft includes the cut shapes 202 without the cut shapes 204.
  • the shaft can include the cut shapes 204 without the cut shapes 202.
  • the cut shapes 202, 204 are potentially useful alone or in combmation with other cut shapes, it is expected that combinations of the first and second cut shapes 128, 130 may be more stable in some cases than the cut shapes 202, 204 alone or in combination during use of a neuromodulation catheter.
  • combinations of cut shapes that impart resistance to complementary sets of fewer than all types of axial and torsional force that may act on a shaft during use of a neuromodulation catheter may facilitate dissipation of localized stresses along a cut.
  • the cut shapes 202, 204 may advantageously allow for relatively gradual changes in flexibility along the length of a shaft segment, it will further be appreciated that catheters configured in accordance with embodiments of the present technology can include various combinations of cut shapes tailored to provide a desired level of flexibility and/or control for different applications.
  • FIGS. 29-31 are perspective views of shaft segments having guide wire exit openings with different positions relative to cuts configured in accordance with several embodiments of the present technology.
  • a shaft segment 214 having the first and second cut shapes 128, 130 has a guide wire exit opening 216 in place of a third peak 138 of one of the second cut shapes 130,
  • the guide wire exit opening 216 can be in place of the first peak 132, the second peak 134, the fourth peak 139, or a combination thereof including or not including the third peak 138.
  • FIGS. 5 and 29 in some embodiments a shaft segment 214 having the first and second cut shapes 128, 130 has a guide wire exit opening 216 in place of a third peak 138 of one of the second cut shapes 130, In other embodiments, the guide wire exit opening 216 can be in place of the first peak 132, the second peak 134, the fourth peak 139, or a combination thereof including or not including the third peak 138.
  • a shaft segment 218 having the first and second cut shapes 128, 130 can have a guide wire exit opening 220 between (e.g., about evenly between) adjacent turns of a helical path along which the first and second cut shapes 128, 130 are distributed.
  • a shaft segment 222 having the first and second cut shapes 128, 130 and the uncut region 201 e.g., as described above with reference to FIG. 25
  • the guide wire exit openings may have other suitable positions relative to the cuts.
  • the guide wire exit openings 216, 220, 224 are illustrated in FIGS. 29-31 as generally oval with their longitudinal axes aligned with longitudinal axes of the corresponding shaft segments 214, 218, 222, the guide wire exit openings 216, 220, 224 can have other suitable shapes and/or orientations.
  • neuromodulation catheters configured in accordance with at least some embodiments of the present technology can include one or more elongate members (e.g., filaments, wires, ribbons, or other suitable structures) helically wound into one or more tubular shapes. Similar to the axial density of features of a cut along a longitudinal axis of a shaft (e.g., as discussed above with reference to FIG. 3), the axial density of windings of a helically wound elongate member along a longitudinal axis of a shaft can be selected to change the flexibility of the shaft. For example, an axial density of windings along a longitudinal axis of a shaft can be selected to facilitate intravascular deliver ⁇ ?
  • elongate members e.g., filaments, wires, ribbons, or other suitable structures
  • the axial density of windings of a helically wound elongate member along a longitudinal axis of a shaft can be selected to change the flexibility of the shaft. For example, an axial density
  • an axial density of windings along a longitudinal axis of a shaft varies along the length of the shaft (e.g., to tailor the shaft to the tortuosity or other geometry of different portions of a transradial or other suitable approach).
  • the axial density of wmdmgs along a longitudinal axis of a shaft can be consistent along the length of the shaft (e.g., to increase the overall flexibility of the shaft).
  • a shaft 250 can include a first helically wound elongate member 252 having a series of first windings 254 at least partially forming a first tubular structure 256.
  • the shaft 250 can further include a second helically wound elongate member 258 having a series of second wmdmgs 260 at least partially forming a second tubular structure 262.
  • the first tubular structure 256 can be disposed within the second tubular structure 262, and the first and second tubular structures 256, 262 can be concentric,
  • At least one of the first and second helically wound elongate members 252, 258 is muitifiiar.
  • the second helically wound elongate member 258 is muitifiiar with five parallel filaments (individually identified in FIG. 32 as 258a-e), and the first helically wound elongate member 252 is monofilar.
  • the second helically wound elongate member 258 can be monofilar and the first helically wound elongate member 252 can be muitifiiar.
  • both the first and second helically wound elongate members 252, 258 can be monofilar or muitifiiar.
  • the first windings 254, the second windings 260, or both are "openly wound" or spaced apart along a longitudinal axis of the shaft 250.
  • the second windings 260 are shown spaced apart along the longitudinal axis of the shaft 250 with gaps 181 between adjacent second windings 260, and the first windings 254 are shown not spaced apart along the longitudinal axis of the shaft 250.
  • the second windings 260 can be not spaced apart along the longitudinal axis of the shaft 250 and the first windings 254 can be spaced apart along the longitudinal axis of the shaft 250. In still other embodiments, both the first and second windings 254, 260 can be spaced apart or not spaced apart along the longitudinal axis of the shaft 250.
  • a shaft 264 can include a third helically wound elongate member 266 having a series of third windings 268 at least partially forming a third tubular structure 270.
  • the first and second tubular stmctures 256, 262 can be disposed within the third tubular structure 270, and the first, second, and third tubular structures 256, 262, 270 can be concentric.
  • the third helically wound elongate member 266 is muitifiiar with parallel filaments (individually identified in FIG. 33 as 266a-e). In other embodiments, the third helically wound elongate member 266 can be monofilar.
  • the layers may be counter-wound, e.g. a right-hand helical layer may surround a left-hand helical layer.
  • the shaft 264 can further include biocompatible jacket 272 at least partially encasing the first, second, and third tubular structures 256, 262, 270.
  • the biocompatible jacket 272 for example, can be at least partially made of a smooth polymer or other suitable material well suited for sliding contact with an inner wall of a body lumen.
  • FIGS. 34 and 35 are side profile views of helically wound elongate members 274, 278, respectively, configured in accordance with several embodiments of the present technology.
  • the helically wound elongate member 274 can have a series of wmdmgs 276 with an average helix angle K-l.
  • the helically wound elongate member 278 can have a series of windings 280 with an average helix angle K-2.
  • the first windings 254, the second windings 260, the third windings 268, or a subset thereof can have different average helix angles.
  • a first average helix angle of the first windings 254 can be different than a second average helix angle of the second windings 260 by an angle within a range from about 10 degrees to about 140 degrees (e.g., a range from about 30 degrees to about 120 degrees, or another suitable range).
  • first average helix angle of the first windings 254 can be different than a third average helix angle of the third windings 268 by an angle within a range from about 10 degrees to about 140 degrees (e.g., a range from about 30 degrees to about 120 degrees, or another suitable range) and the second average helix angle of the second windings 260 can be between (e.g., about midway between) the first and third average helix angles of the first and third windings 254, 268, respecti vely .
  • FIG. 36 is a side profile view of a helically wound elongate member 282 configured in accordance with an embodiment of the present technology.
  • the helically wound elongate member 282 can have a series of windings 284 with different average helix angles and opposite chirality on either side of a transition region 286. Although an abrupt change in average helix angle at the transition region 286 is shown in FIG. 36, the change at the transition region 286 can alternatively be gradual or incremental.
  • the first windings 254, the second windings 260, and/or the third windings 268 include one or more transition regions 286.
  • the first windings 254, the second windings 260, and the third wmdmgs 268 can have consistent helix angles along the length of the shaft 250.
  • Including one or more transition regions 286 can be useful, for example, to allow a difference between average helix angles of windings within concentric tubular structures to vary (e.g., to change at least once) along the length of the shaft 250. For example, this difference can decrease (e.g., abruptly, gradually, or incrementally) distaily along the length of the shaft 250.
  • the positions of the transition regions 286 can be selected to change the flexibility of the shaft relative to the axial and torsional stiffness of the shaft along the length of a shaft (e.g., to facilitate intravascular delivery of a neuromodulation element to a treatment location within or otherwise proximate to a renal artery of a human patient via a transradial or other suitable approach).
  • neuromodulation catheters configured in accordance with at least some embodiments of the present technology can include shafts having one or more segments with different shape memory properties.
  • the first portion 127a of the segment 127 can be made at least partially of a first shape-memory alloy
  • the second portion 127b of the segment 127 can be made at least partially of a second shape-memory alloy
  • the third portion i 27c of the segment 127 can be made at least partially of a third shape-memory alloy.
  • the first, second, and third shape-memory alloys can be different or the same.
  • the first, second, and third shape-memory alloys are nitinol ( Ti), In other embodiments, the first, second, and third shape-memor alloys can be other suitable materials.
  • the first, second, and third shape-memory alloys can have first, second, and third shape-memory transformation temperature ranges, respectively.
  • the first, second, and third shape-memory transformation temperature ranges can include A/ " temperatures,
  • the third shape-memory transformation temperature range and/or an Af temperature of the third shape-memory transformation temperature range can be lower than the first shape-memory transformation temperature range and/or an Af temperature of the first shape-memory transformation temperature range.
  • the first shape-memory transformation temperature range can include an Af temperature greater than body temperature and the third shape-memor transformation temperature range includes an Af temperature less than body temperature.
  • a shape-memory transformation temperature range and/or an Af temperature of a shape-memory transformation temperature range of the shaft 108 can increase (e.g., abruptly, gradually, or incrementally) along the second portion 127b of the segment 127 from the third portion 127c of the segment 127 toward the first portion 127a of the segment 127.
  • the first, second, and third portions 127a-c of the segment 127 are formed separately and then joined
  • the shape-memory transformation temperature ranges and/or the Af temperatures along the length of the shaft 108 can be achieved by processin g the first, second, and third portions 127a-c of the segment 127 differently while they are joined.
  • one of the first, second, and third portions 127a ⁇ c can be subjected to a heat treatment to change its shape-memory transformation temperature range and/or Af temperature while the others of the first, second, and third portions 127a-e are thermally insulated.
  • shape-memory transformation temperature ranges and/or Af temperatures of shape-memory transformation temperature ranges may increase flexibility and decrease axial and torsional stiffness of a shaft (e.g., by causing nitinol (NiTi) to tend to assume a more austenitic phase at body temperature), and that lower shape-memory transformation temperature ranges and/or Af temperatures of shape-memory transformation temperature ranges may decrease flexibility and increase axial and torsional stiffness of a shaft (e.g., by causing nitinol (NiTi) to tend to assume a more martensitie phase at body temperature).
  • the positions of portions of a shaft having different shape-memory transformation temperature ranges and/or Af temperatures of shape-memory transformation temperature ranges can be selected to change the flexibility of the shaft relative to the axial and torsional stiffness of the shaft along the length of a shaft (e.g., to facilitate intravascular delivery of a neuromodulation element to a treatment location within or otherwise proximate to a renal artery of a human patient via a transradial or other suitable approach).
  • the shaft 108 can be heat treated or otherwise formed so that the shape-memory transformation temperature ranges and/or Af temperatures along the length of the shaft 108 are at least generally the same.
  • the first, second, and third portions ! 27a-c of the segment 127 can be nitinol (NiTi) heat treated or otherwise formed to have shape-memory transformation temperature ranges from 5°C to 15°C and/or Af temperatures within this range. This can facilitate maintaining nitinol (NiTi) at or near the martensite phase while at 37°C (body temperature).
  • Renal neuromodulation is the partial or complete incapacitation or other effective disruption of nerves of the kidneys (e.g., nerves terminating in the kidneys or in structures closely associated with the kidneys).
  • renal neuromodulation can include inhibiting, reducing, and/or blocking neural communication along neural fibers (e.g., efferent and/or afferent neural fibers) of the kidneys.
  • Such incapacitation can be long-term (e.g., permanent or for periods of months, years, or decades) or short-term (e.g., for periods of minutes, hours, days, or weeks).
  • Renal neuromodulation is expected to contribute to the systemic reduction of sympathetic tone or drive and/or to benefit at least some specific organs and/or other bodily structures innervated by sympathetic nerves. Accordingly, renal neuromodulation is expected to be useful in treating clinical conditions associated with systemic sympathetic overactivity or hyperactivity, particularly conditions associated with central sympathetic overstimulation. For example, renal neuromodulation is expected to efficaciously treat hypertension, heart failure, acute myocardial infarction, metabolic syndrome, insulin resistance, diabetes, left ventricular hypertrophy, chronic and end stage renal disease, inappropriate fluid retention in heart failure, cardio-rena! syndrome, polycystic kidney disease, polycystic ovary syndrome, osteoporosis, erectile dysfunction, and sudden death, among other conditions.
  • Renal neuromodulation can be electrically-induced, thermally-induced, chemically-induced, or induced in another suitable manner or combination of manners at one or more suitable treatment locations during a treatment procedure.
  • the treatment location can be within or otherwise proximate to a renal lumen (e.g., a renal artery, a ureter, a renal pelvis, a major renal calyx, a minor renal calyx, or another suitable structure), and the treated tissue can include tissue at least proximate to a wall of the renal lumen.
  • a treatment procedure can include modulating nerves in the renal plexus, which lay intimately within or adjacent to the adventitia of the renal artery.
  • Renal neuromodulation can include a cryotherapeutic treatment modality alone or in combination with another treatment modality.
  • Cryotherapeutic treatment can include cooling tissue at a treatment location in a manner that modulates neural function.
  • sufficiently cooling at least a portion of a sympathetic renal nerve can slow or potentially block conduction of neural signals to produce a prolonged or permanent reduction in renal sympathetic activity.
  • cryotherapeutic tissue damage can include, for example, direct cell injury (e.g., necrosis), vascular or luminal injury (e.g., starving cells from nutrients by damaging supplying blood vessels), and/or sublethal hypothermia with subsequent apoptosis.
  • Exposure to cryotherapeutic cooling can cause acute cell death (e.g., immediately after exposure) and/or delayed cell death (e.g., during tissue thawing and subsequent hyperperfusion).
  • Neuromodulation using a cryotherapeutic treatment in accordance with embodiments of the present technology can include cooling a structure proximate an inner surface of a body lumen wall such that tissue is effectively cooled to a depth where sympathetic renal nerves reside.
  • a cooling assembly of a cryotherapeutic device can be cooled to the extent that it causes therapeuticaliy-effective, cryogenic renal neuromodulation.
  • a cryotherapeutic treatment modality can include cooling that is not configured to cause neuromodulation.
  • the cooling can be at or above cryogenic temperatures and can be used to control neuromodulation via another treatment modality (e.g., to protect tissue from neuromodulating energy).
  • Renal neuromodulation can include an electrode-based or transducer-based treatment modality alone or in combination with another treatment modality.
  • Electrode-based or transducer-based treatment can include delivering electricity and/or another form of energy to tissue at a treatment location to stimulate and/or heat the tissue in a manner that modulates neural function. For example, sufficiently stimulating and/or heating at least a portion of a sympathetic renal nerve can slow or potentially block conduction of neural signals to produce a prolonged or permanent reduction in renal sympathetic activity.
  • a variety of suitable types of energy can be used to stimulate and/or heat tissue at a treatment location.
  • neuromodulation in accordance with embodiments of the present technology can include delivering RF energy, pulsed energy, microwave energy, optical energy, focused ultrasound energy (e.g., high-intensity focused ultrasound energy), or another suitable type of energy alone or in combination.
  • An electrode or transducer used to deliver this energy can be used alone or with other electrodes or transducers in a multi-electrode or multi-transducer array.
  • the energy can be applied from within the body (e.g., within the vasculature or other body lumens in a catheter-based approach) and/or from outside the body (e.g., via an applicator positioned outside the body).
  • energy can be used to reduce damage to non-targeted tissue when targeted tissue adjacent to the non-targeted tissue is subjected to neuromodulating cooling.
  • Focused ultrasound is an example of a transducer-based treatment modality that can be delivered from outside the body. Focused ultrasound treatment can be performed in close association with imaging (e.g., magnetic resonance, computed tomography, fluoroscopy, ultrasound (e.g., intravascular or intraluminal), optical coherence tomography, or another suitable imaging modality). For example, imaging can be used to identify an anatomical position of a treatment location (e.g., as a set of coordinates relative to a reference point).
  • imaging can be used to identify an anatomical position of a treatment location (e.g., as a set of coordinates relative to a reference point).
  • the coordinates can then entered into a focused ultrasound device configured to change the power, angle, phase, or other suitable parameters to generate an ultrasound focal zone at the location corresponding to the coordinates.
  • the focal zone can be small enough to localize therapeutical ly-effective heating at the treatment location while partially or fully avoiding potentially harmful disruption of nearby structures.
  • the ultrasound device can be configured to pass ultrasound energy through a lens, and/or the ultrasound energy can be generated by a curved transducer or by multiple transducers in a phased array (curved or straight).
  • Heating effects of electrode-based or transducer-based treatment can include ablation and/or non-ablative alteration or damage (e.g., via sustained heating and/or resistive heating).
  • a treatment procedure can include raising the temperature of target neural fibers to a target temperature above a first threshold to achieve non-ablative alteration, or above a second, higher threshold to achieve ablation.
  • the target temperature can be higher than about body temperature (e.g., about 37°C) but less than about 45°C for non-ablative alteration, and the target temperature can be higher than about 45°C for ablation.
  • Heating tissue to a temperature between about body temperature and about 45°C can induce non-ablative alteration, for example, via moderate heating of target neural fibers or of vascular or luminal structures that perfuse the target neural fibers. In cases where vascular structures are affected, the target neural fibers can be denied perfusion resulting in necrosis of the neural tissue. Heating tissue to a target temperature higher than about 45°C (e.g., higher than about 60°C) can induce ablation, for example, via substantial heating of target neural fibers or of vascular or luminal structures that perfuse the target fibers.
  • tissue it can be desirable to heat tissue to temperatures that are sufficient to ablate the target neural fibers or the vascular or luminal structures, but that are less than about 90°C (e.g., less than about 85°C, less than about 80°C, or less than about 75°C).
  • Renal neuromodulation can include a chemical-based treatment modality alone or in combination with another treatment modality.
  • Neuromodulation using chemical-based treatment can include delivering one or more chemicals (e.g., drugs or other agents) to tissue at a treatment location in a manner that modulates neural function.
  • the chemical for example, can be selected to affect the treatment location generally or to selectively affect some structures at the treatment location over other structures.
  • the chemical for example, can be guanethidine, ethanol, phenol, a neurotoxin, or another suitable agent selected to alter, damage, or disrupt nerves.
  • a variety of suitable techniques can be used to deliver chemicals to tissue at a treatment location.
  • chemicals can be delivered via one or more needles originating outside the body or within the vasculature or other body lumens.
  • a catheter can be used to intravascularly position a therapeutic element including a plurality of needles (e.g., micro-needles) that can be retracted or otherwise blocked prior to deployment.
  • a chemical can be introduced into tissue at a treatment location via simple diffusion through a body lumen wall, electrophoresis, or another suitable mechanism. Similar techniques can be used to introduce chemicals that are not configured to cause neuromodulation, but rather to facilitate neuromodulation via another treatment modality.
  • the system 100 may be a stent delivery system.
  • the catheter 102 can be a stent delivery catheter and the neuromodulation element can 1 12 be a stent delivery element.
  • the stent delivery element can include a dilatation balloon (not shown) with a balloon expandable stent disposed thereon.
  • the stent delivery catheter also can include the handle 1 10 operably connected to the shaft 108 via the proximal end portion 108a.
  • the shaft 108 can be configured to locate the stent delivery element intravascularly at a treatment location within or otherwise proximate to a body lumen (e.g., coronary artery).
  • the handle 1 10 can be configured to aid in the deliver ⁇ ' and deployment of the stent to the treatment location.
  • the stent delivery system may, in at least some cases, be without the console 104 or the cable 106.
  • the stent of stent delivery element may be any balloon expandable stent as known to one of ordinary skill in the art.
  • the stent is formed from a single wire forming a continuous sinusoid.
  • the stent may include a coating disposed on the surface of the stent.
  • the coating may include a polymer and/or a therapeutic agent.
  • the coating includes a BiolinxTM polymer blended with a limus drug.
  • the stent is a drug filled stent having a lumen filled with a therapeutic agent.
  • Other configurations are also possible, such as configurations in which the stent deliver ⁇ ' element does not include a stent disposed on a dilatation balloon.
  • a neuromoduiation catheter comprising:
  • an elongate shaft including—
  • first cut shapes being configured to at least partially resist deformation in response to compression on the shaft along a longitudinal axis of the shaft, tension on the shaft along the longitudinal axis, and torsion on the shaft in a first circumferential direction perpendicular to the longitudinal axis
  • second cut shapes being configured to at least partially resist deformation in response to compression on the shaft along the longitudinal axis, torsion on the shaft in the first circumferential direction, and torsion on the shaft in a second circumferential direction opposite to the first circumferential direction
  • a neuromoduiation element operably connected to the shaft via a distal end portion of the shaft
  • the first cut shapes are less resistant to deformation in response to torsion on the shaft in the second circumferential direction than are the second cut shapes
  • the shaft includes a hypotube having a wall thickness
  • the first and second cut shapes extend at least partially through the wall thickness of the hypotube.
  • the first cut shapes are sinusoidal and have amplitudes with a first orientation relative to the longitudinal axis
  • the second cut shapes are sinusoidal and have amplitudes with a second orientation relative to the longitudinal axis, the second orientation being different than the first orientation.
  • the helical path extends along a portion of the longitudinal axis corresponding to a segment of the shaft
  • a distance along the longitudinal axis between the neuromodulation element and the segment is selected to cause the segment to be at least proximate to a relatively sharply angled or otherwise relatively tortuous region of a transradial approach when the neuromodulation element is operably positioned at a treatment location within or otherwise proximate to a renal artery of a human patient, 8.
  • the shaft includes an uncut region
  • the first and second cut shapes are positioned along portions of the helical path on either side of the uncut region
  • the shaft includes a hypotube having a wall thickness
  • the first and second cut shapes extend at least partially through the wall thickness of the hypotube at a first segment of the shaft, the first segment being within about 3 centimeters of the neuromodulation element and having a length from about 30 centimeters to about 80 centimeters;
  • the shaft includes a second segment proximal to the first segment, the second segment having a length greater than about 40 centimeters;
  • hypotube is less resistant to deflection in response to lateral force at the first segment than at the second segment.
  • the first segment has a length from about 40 centimeters to about 70 centimeters; and the second segment has a length greater than about 50 centimeters.
  • the individual first cut shapes include a first peak and a second peak with a first interface therebetween;
  • the individual second cut shapes include a third peak and a fourth peak with a second interface therebetween;
  • an angle between the first interface and the longitudinal axis is greater than an angle between the second interface and the longitudinal axis
  • lengths of the second interfaces increase along at least a portion of the length of the first segment toward the second segment.
  • the axial density of the first and second cut shapes decreases gradually along the entire length of the first segment toward the second segment
  • the lengths of the second interfaces increase gradually along die entire length of the first segment toward the second segment.
  • the individual first cut shapes include a first peak and a second peak with a first interface therebetween;
  • the individual second cut shapes include a third peak and a fourth peak with a second interface therebetween;
  • an angle between the first interface and the longitudinal axis is greater than an angle between the second interface and the longitudinal axis.
  • the shaft includes a guide wire exit opening in place of the first peak, the second peak, the third peak, the fourth peak, or a combination thereof,
  • the first interface is perpendicular to the longitudinal axis
  • the second interface is parallel to the longitudinal axis.
  • a neuromodulation catheter comprising:
  • a neuromodulation element operably connected to the shaft via a distal end portion of the shaft
  • first and second cut shapes are interspersed along a helical path extending about the longitudinal axis.
  • a neuromodulation catheter comprising:
  • an elongate shaft including two or more cut shapes configured to at least partially resist deformation in response to compression on the shaft along a longitudinal axis of the shaft, tension on the shaft along the longitudinal axis, torsion on the shaft in a first circumferential direction perpendicular to the longitudinal axis, and torsion on the shaft in a second circumferential direction opposite to the first circumferential direction, the cut shapes being distributed along a helical path extending about the longitudinal axis;
  • a neuromodulation element operably connected to the shaft via a distal end portion of the shaft.
  • the shaft includes tabs acent to the cut shapes, the individual tabs including a flared portion and a restricted "tion.
  • the flared portion includes a rounded head
  • the restricted portion includes a rounded neck.
  • the flared portion comprises a wedge-shaped head
  • the restricted portion comprises a rounded neck
  • a neuromoduiation catheter comprising:
  • an elongate shaft including two or more sinusoidal cut shapes
  • a neuromoduiation element operably connected to the shaft via a distal end portion of the shaft
  • the cut shapes have an orientation that is perpendicular to the helical path.
  • the individual cut shapes include a first peak and a second peak with an interface therebetween;
  • the interface is perpendicular to the helical path.
  • a neuromoduiation catheter comprising:
  • an elongate shaft including—
  • a first helically wound elongate member having a series of first windings with a first average helix angle, the first windings at least partially forming a first tubular structure; and a second helically wound elongate member having a series of second windings with a second average helix angle, the second windings at least partially forming a second tubular structure; and a neuromodulation element operablv connected to the shaft via a distal end portion of the shaft,
  • the first tubular structure is disposed within the second tubular structure, the first and second tubular structures are concentric, and
  • the first average helix angle is different than the second average helix angle by an angle within a range from about 10 degrees to about 140 degrees.
  • the neuromodulation catheter of example 30 wherein a difference between the first and second average helix angl es changes at least once along a length of the shaft.
  • the first tubular structure includes a transition region
  • the second tubular structure includes a transition region
  • the second windings on either side of the transition region have different a verage helix angles.
  • the first and second tubular structures extend along a portion of a longitudinal axis of the shaft, the portion of the longitudinal axis corresponding to a segment of the shaft;
  • a distance along the longitudinal axis between the neuromodulation element and the segment is selected to cause the segment to be at least proximate to a relatively sharply angled or otherwise relatively tortuous region of a transradial approach when the neuromodulation element is operably positioned at a treatment location within or otherwise proximate to a renal artery of a human patient.
  • the neuromodulation catheter of example 39 wherem the relatively sharply angled or otherwise relatively tortuous region is within or otherwise proximate to a subclavian artery.
  • a neuromodulation catheter comprising:
  • an elongate shaft including—
  • a first segment made at least partially of a first shape-memory alloy having a first shape-memory transformation temperature range
  • a second segment made at least partially of a second shape-memory alloy having a second shape-memory transformation temperature range lower than the first shape-memory transformation temperature range, the second segment being proximal to the first segment along a longitudinal axis of the shaft; and a neuromodulation element operably connected to the shaft via a distal end portion of the shaft.
  • the elongate shaft includes a third segment made at least partially of a third shape-memory alloy, the third segment being between the first and second segments along the longitudinal axis;
  • the first, second, and third shape-memory alloys are the same;
  • a shape-memory transformation temperature range of the third shape-memory alloy gradually increases along the third segment from the second segment toward the first segment.
  • the first shape-memory transformation temperature range includes an Af temperature greater than body temperature
  • the second shape-memory transformation temperature range includes an Af temperature less than body temperature.

Abstract

Selon l'invention, un cathéter de neuromodulation comprend une tige allongée et d'un élément de neuromodulation. La tige comprend au moins deux premières formes découpées et au moins deux secondes formes découpées le long d'un chemin hélicoïdal s'étendant autour d'un axe longitudinal de la tige. Les premières formes découpées sont conçues pour résister au moins partiellement à une déformation due à une compression et à une tension longitudinales exercées sur la tige ainsi qu'à une torsion sur la tige dans une première direction circonférentielle. Les secondes formes découpées sont conçues pour résister au moins partiellement à une déformation due à une compression longitudinale exercée sur la tige ainsi qu'à une torsion sur la tige à la fois dans les première et seconde directions circonférentielles opposées.
PCT/US2015/013029 2014-01-27 2015-01-27 Cathéters à flexibilité accrue et dispositifs, systèmes et procédés associés WO2015113027A2 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP15703210.3A EP3099263A2 (fr) 2014-01-27 2015-01-27 Cathéters à flexibilité accrue et dispositifs, systèmes et procédés associés

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US201461932213P 2014-01-27 2014-01-27
US61/932,213 2014-01-27

Publications (2)

Publication Number Publication Date
WO2015113027A2 true WO2015113027A2 (fr) 2015-07-30
WO2015113027A3 WO2015113027A3 (fr) 2015-10-29

Family

ID=52462479

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2015/013029 WO2015113027A2 (fr) 2014-01-27 2015-01-27 Cathéters à flexibilité accrue et dispositifs, systèmes et procédés associés

Country Status (2)

Country Link
EP (1) EP3099263A2 (fr)
WO (1) WO2015113027A2 (fr)

Cited By (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10188829B2 (en) 2012-10-22 2019-01-29 Medtronic Ardian Luxembourg S.A.R.L. Catheters with enhanced flexibility and associated devices, systems, and methods
US10368775B2 (en) 2014-10-01 2019-08-06 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for evaluating neuromodulation therapy via hemodynamic responses
WO2019222441A1 (fr) 2018-05-16 2019-11-21 Voyager Therapeutics, Inc. Sérotypes de vaa pour l'administration de charge utile spécifique au cerveau
EP3632923A1 (fr) 2015-01-16 2020-04-08 Voyager Therapeutics, Inc. Polynucléotides de ciblage du système nerveux central
US10667736B2 (en) 2014-12-17 2020-06-02 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for assessing sympathetic nervous system tone for neuromodulation therapy
US10786306B2 (en) 2018-01-24 2020-09-29 Medtronic Ardian Luxembourg S.A.R.L. Denervation therapy
US10959669B2 (en) 2018-01-24 2021-03-30 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for assessing the efficacy of neuromodulation therapy
US11116564B2 (en) 2017-07-05 2021-09-14 Medtronic Ardian Luxembourg S.A.R.L. Methods for treating anxiety disorders in patients via renal neuromodulation
US11160982B2 (en) 2017-07-05 2021-11-02 Medtronic Ardian Luxembourg S.A.R.L. Methods for treating post-traumatic stress disorder in patients via renal neuromodulation
US11253189B2 (en) 2018-01-24 2022-02-22 Medtronic Ardian Luxembourg S.A.R.L. Systems, devices, and methods for evaluating neuromodulation therapy via detection of magnetic fields
US11304749B2 (en) 2017-11-17 2022-04-19 Medtronic Ardian Luxembourg S.A.R.L. Systems, devices, and associated methods for neuromodulation with enhanced nerve targeting
US11350992B2 (en) 2016-04-28 2022-06-07 Medtronic Ardian Luxembourg S.A.R.L. Neuromodulation and associated systems and methods for the treatment of cancer
US11413084B2 (en) 2018-07-03 2022-08-16 Medtronic Ardian Luxembourg S.A.R.L. Methods for treating eating disorders in patients via renal neuromodulation
US11633120B2 (en) 2018-09-04 2023-04-25 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for assessing efficacy of renal neuromodulation therapy
US11717343B2 (en) 2018-01-24 2023-08-08 Medtronic Ireland Manufacturing Unlimited Company Systems, devices, and associated methods for neuromodulation in heterogeneous tissue environments
US11857249B2 (en) 2014-04-25 2024-01-02 Medtronic Ireland Manufacturing Unlimited Company Devices, systems, and methods for monitoring and/or controlling deployment of a neuromodulation element within a body lumen and related technology

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060206140A1 (en) * 2005-02-24 2006-09-14 Samuel Shaolian Adjustable embolic aneurysm coil
US20120184952A1 (en) * 2011-01-19 2012-07-19 Jenson Mark L Low-profile off-wall electrode device for renal nerve ablation
WO2014066432A2 (fr) * 2012-10-22 2014-05-01 Medtronic Ardian Luxembourg Sarl Cathéters à flexibilité accrue et dispositifs associés, systèmes et procédés

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
None

Cited By (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11147948B2 (en) 2012-10-22 2021-10-19 Medtronic Ardian Luxembourg S.A.R.L. Catheters with enhanced flexibility and associated devices, systems, and methods
US10188829B2 (en) 2012-10-22 2019-01-29 Medtronic Ardian Luxembourg S.A.R.L. Catheters with enhanced flexibility and associated devices, systems, and methods
US11857249B2 (en) 2014-04-25 2024-01-02 Medtronic Ireland Manufacturing Unlimited Company Devices, systems, and methods for monitoring and/or controlling deployment of a neuromodulation element within a body lumen and related technology
US10368775B2 (en) 2014-10-01 2019-08-06 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for evaluating neuromodulation therapy via hemodynamic responses
US11311205B2 (en) 2014-10-01 2022-04-26 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for evaluating neuromodulation therapy via hemodynamic responses
US10667736B2 (en) 2014-12-17 2020-06-02 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for assessing sympathetic nervous system tone for neuromodulation therapy
EP3632923A1 (fr) 2015-01-16 2020-04-08 Voyager Therapeutics, Inc. Polynucléotides de ciblage du système nerveux central
US11350992B2 (en) 2016-04-28 2022-06-07 Medtronic Ardian Luxembourg S.A.R.L. Neuromodulation and associated systems and methods for the treatment of cancer
US11116564B2 (en) 2017-07-05 2021-09-14 Medtronic Ardian Luxembourg S.A.R.L. Methods for treating anxiety disorders in patients via renal neuromodulation
US11160982B2 (en) 2017-07-05 2021-11-02 Medtronic Ardian Luxembourg S.A.R.L. Methods for treating post-traumatic stress disorder in patients via renal neuromodulation
US11284934B2 (en) 2017-07-05 2022-03-29 Medtronic Ardian Luxembourg S.A.R.L. Methods for treating sleep disorders in patients via renal neuromodulation
US11304749B2 (en) 2017-11-17 2022-04-19 Medtronic Ardian Luxembourg S.A.R.L. Systems, devices, and associated methods for neuromodulation with enhanced nerve targeting
US11253189B2 (en) 2018-01-24 2022-02-22 Medtronic Ardian Luxembourg S.A.R.L. Systems, devices, and methods for evaluating neuromodulation therapy via detection of magnetic fields
US10959669B2 (en) 2018-01-24 2021-03-30 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for assessing the efficacy of neuromodulation therapy
US10786306B2 (en) 2018-01-24 2020-09-29 Medtronic Ardian Luxembourg S.A.R.L. Denervation therapy
US11419681B2 (en) 2018-01-24 2022-08-23 Medtronic Ardian Luxembourg S.A.R.L. Denervation therapy
US11717343B2 (en) 2018-01-24 2023-08-08 Medtronic Ireland Manufacturing Unlimited Company Systems, devices, and associated methods for neuromodulation in heterogeneous tissue environments
WO2019222441A1 (fr) 2018-05-16 2019-11-21 Voyager Therapeutics, Inc. Sérotypes de vaa pour l'administration de charge utile spécifique au cerveau
US11413084B2 (en) 2018-07-03 2022-08-16 Medtronic Ardian Luxembourg S.A.R.L. Methods for treating eating disorders in patients via renal neuromodulation
US11633120B2 (en) 2018-09-04 2023-04-25 Medtronic Ardian Luxembourg S.A.R.L. Systems and methods for assessing efficacy of renal neuromodulation therapy

Also Published As

Publication number Publication date
EP3099263A2 (fr) 2016-12-07
WO2015113027A3 (fr) 2015-10-29

Similar Documents

Publication Publication Date Title
US11376398B2 (en) Catheters with enhanced flexibility and associated devices, systems, and methods
EP2908755B1 (fr) Cathéters à flexibilité accrue et dispositifs associés, systèmes et procédés
EP3099263A2 (fr) Cathéters à flexibilité accrue et dispositifs, systèmes et procédés associés
US11154353B2 (en) Neuromodulation catheters having jacketed neuromodulation elements and related devices, systems, and methods
KR101912960B1 (ko) 다중전극 어레이를 구비한 신장 신경조절용 카테터 장치 및 관련된 시스템 및 방법
EP3116430B1 (fr) Cathéters à éléments d'expansion radiale indépendants, dispositifs, systèmes et procédés associés
US20140066915A1 (en) Renal rf ablation system with a movable virtual electrode and related methods of use
EP2996754B1 (fr) Sondes de neuromodulation comportant une tige, pour une souplesse et une commande améliorées, et dispositifs et systèmes associés
US20160101216A1 (en) Myocyte-derived flow assist device: extravasal sheaths of rhythmically contracting myocytes aiding flow of biological fluids

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 15703210

Country of ref document: EP

Kind code of ref document: A2

REEP Request for entry into the european phase

Ref document number: 2015703210

Country of ref document: EP

WWE Wipo information: entry into national phase

Ref document number: 2015703210

Country of ref document: EP

NENP Non-entry into the national phase

Ref country code: DE