Methods and devices for inserting a needle

Abstract

An apparatus provides targeted placement of openings for infusing fluids into a body. The apparatus provides a driving force to a penetrating medical device, such as a needle, when the apparatus tip encounters material of high resistance. When the apparatus tip encounters a low resistance material, no further driving force is applied to the apparatus due to contraction of an element made of interlaced flexible elements. A multi-opening needle is provided in some embodiments wherein placement of one of the openings in a target region with a relatively lower external pressure allows pressurized fluid to exit the needle while openings remaining in higher pressure, non-target regions do not release substantial amounts of the fluid.

Claims

1. A method of infusing a fluid comprising: providing a penetrating element and a tube having a lumen and a plurality of lumen openings spaced longitudinally along a sidewall of the tube lumen; penetrating the penetrating element into a body; positioning the tube such that at least one of the lumen openings is positioned in a target region at the same time that at least one of the openings is not positioned in the target region; providing fluid to the lumen; pressurizing the fluid in the lumen to a first pressure which forces the fluid to exit the lumen through the at least one of the lumen openings that is positioned in the target region; and the first pressure is insufficient to force the fluid to substantially exit the one or more lumen openings that are not positioned in the target region; wherein the target region has a first external pressure external to the penetrating element, and a region in the body that covers the one or more lumen openings that are not positioned at the target region has a second external pressure; and the first external pressure is lower than the second external pressure.

2. The method of claim 1, wherein the penetrating element forms the tube.

3. The method of claim 1, wherein the plurality of lumen openings are positioned along on a sidewall of the penetrating element.

4. The method of claim 1, wherein the penetrating element comprises a closed sharp distal tip.

5. The method of claim 1, further comprising: sliding an inner element within the penetrating element, the inner element comprising a lumen opening; and aligning the inner element lumen opening with a first penetrating element lumen opening.

6. The method of claim 1, further comprising: sliding an inner element within the penetrating element, the inner element comprising a plurality of lumen openings; aligning a first inner element lumen opening with a first penetrating element lumen opening; and aligning a second inner element lumen opening with a second penetrating element lumen opening.

7. The method of claim 1, wherein the target region is a synovial sac.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) FIG. 1 shows a prior art method of central venous catheter placement within the subclavian vein and into the right side of the heart;

(2) FIG. 2 shows a prior art Tuohy needle and associated components;

(3) FIG. 3 shows a prior art Tuohy needle being advanced into the epidural space;

(4) FIG. 4 shows one embodiment of a clutch mechanism being used to access a synovial sac;

(5) FIG. 5a shows one embodiment of a needle with a stylet in place;

(6) FIG. 5b, shows one embodiment of a braided clutch mechanism on the stylet body located inside the needle of FIG. 5a;

(7) FIG. 5c shows one embodiment of a stylet with the braided clutch mechanism of FIG. 5b placed inside a 14 Ga dialysis needle;

(8) FIG. 5d shows one embodiment of a stylet which may include a braided clutch mechanism, the braid including sixteen 0.0020.005 flat 304 stainless steel wires;

(9) FIG. 6a shows one embodiment of a stylet with a braided clutch mechanism in a relaxed state such that the stylet is free to move inside a sheath;

(10) FIG. 6b shows a longitudinal force F being applied to the stylet of FIG. 6a, causing the clutch to engage with the sheath;

(11) FIG. 6c shows one embodiment of braided clutch mechanism which permits fluid to pass through a lumen of a stylet;

(12) FIG. 6d shows another embodiment wherein the needle and stylet may be placed over a guidewire;

(13) FIG. 7a shows one embodiment of a clutch system;

(14) FIG. 7b shows one embodiment of a clutch system where a cutting element is provide on a stylet instead of an outer tube, and the clutch element is constructed and arranged to have a poor ability to translate longitudinal force once the clutch element has exited the outer tube;

(15) FIGS. 7c.sub.i and 7c.sub.ii show one embodiment of a clutch system configured to push a capsule which is free to detach once a cavity is reached;

(16) FIG. 8a illustrates a bellows-based clutch mechanism;

(17) FIG. 8b illustrates a bellows-based clutch mechanism with corresponding engaging feature on the inner diameter of the needle;

(18) FIG. 9a shows one embodiment of a clutch mechanism with a poisson clutch mechanism;

(19) FIG. 9b shows one embodiment of a clutch mechanism including a central bore to allow the flow of fluid through a lumen of the needle;

(20) FIG. 9c shows one embodiment of a clutch mechanism having a finned structure on the outside of the clutch which facilitates engagement of the clutch while allowing fluid to pass through the needle;

(21) FIG. 10a shows one embodiment of an external clutch system;

(22) FIG. 10a-1 is an enlarged partial view of FIG. 10a.

(23) FIG. 10b shows a graph of results from an analytical model of an expanding metallic stent;

(24) FIG. 11 shows one embodiment of a syringe incorporating a clutch mechanism;

(25) FIG. 12a shows a typical double bevel needle;

(26) FIG. 12b illustrates a pencil point needle, with a centrally located cutting point and recessed eye;

(27) FIG. 13a shows a modified 22 Ga multi-hole needle with three rectangular slots, each 1 mm long, according to one embodiment;

(28) FIG. 13b shows modified 18 Ga needles plugged at their distal tips with epoxy;

(29) FIGS. 14a-14d show selective infusion using a multi-hole needle to the site of least resistance;

(30) FIG. 15 illustrates one embodiment of pressure dependent selective infusion using a multi-hole needle in a bench top model. Pressure inside the chamber (P2) can be varied by adjusting the attached syringe;

(31) FIG. 16 shows one embodiment of a multi-hole Sprotte stylet needle with an internal tube having a single orifice, which can be retracted in a corkscrew-like, helical or spring-loaded fashion such that once a drop in resistance is felt, the physician can inject into the region of least resistance;

(32) FIG. 17 shows one embodiment of a multi-hole needle, where the positioning of an orifice in the inner element relative to the outer needle controls the pressure required to infuse the drug through the needle;

(33) FIG. 18 shows one embodiment of a tunable multi-hole needle with cantilever style elements covering the holes in the inner element through which a drug may be infused;

(34) FIG. 19 illustrates one embodiment of a multi-hole needle with a breakable membrane such as a coating or a balloon. In this case, the balloon covering the hole in the pocket of least resistance (the middle balloon) expands before the other balloons. The balloon fractures, through mechanical failure or by contacting a sharp element as it exists the orifice. Once a single hole is opened, the pressure on the other balloons is reduced. The drug is infused at a slow rate to ensure no other balloons are ruptured;

(35) FIG. 20 shows one embodiment of a dual lumen balloon anchor infusion device shown anchoring and infusing in the synovial sac; and

(36) FIG. 21 shows one embodiment of a pressure sensitive, thin-walled balloon for cavity sensing and for providing tactile feedback to the user regarding correct positioning.

DETAILED DESCRIPTION

(37) In some embodiments, resistance encountered at the tip of a device may be used to control a clutch mechanism to create an apparatus that provides a driving force to a penetrating medical device when the apparatus tip encounters material of high resistance, and when the apparatus tip encounters a low resistance material, no further driving force (or a significantly reduced driving force) is applied to the apparatus. Such an apparatus may be used to stop or slow advancement the tip of a device upon reaching a desired low resistance area, regardless of whether the operator continues to apply force to certain components.

(38) 1. Clutch Mechanism Overview

(39) FIG. 4 provides an overview of the principle of placing the needle in a target site (in this case the synovial sac) using a clutch-based mechanism. This method relies on an increase in mechanical resistance (RSYM) as the combined needle and stylet cross from a first compartment or region to a second component or region. For example, in some embodiments, the combined needle and stylet may be moved through the synovium into the synovial fluid (RSF). Various embodiments are described below.

(40) Of course devices and methods described herein may be used at other target sites or regions, such as other within other types of tissues.

(41) 1.1 Braid Mechanism

(42) FIGS. 5a-5d illustrate one embodiment of a needle arrangement incorporating a clutch mechanism. The clutch mechanism on the stylet body includes an expandable and contractible member which is made of a plurality of flexible elements, such as long, thin wires. In some embodiments, the flexible elements may be interlaced. For example, in some embodiments, a series of flat wires are interlaced to form a braid. The flat wires may be the type typically used to form the body of catheters and wire-based stents such as the Wallstent. This braided shaft forms part of the inner core insert or stylet. When axially loading is applied to the inner core, the braided shaft component undergoes a change in its architecture wherein it expands from a first diameter to a larger, second diameter. The braided shaft can be configured such that the larger, second diameter exceeds the inner diameter of the tube or needle component (outer element). This expansion causes the braided shaft to engage with the outer element until the axial load is reduced on the inner core. Unlike a conventional coil, the braid expands radially in an efficient and repeatable manner when axially loaded. In some embodiments, this arrangement relies predominately on elastic behavior rather than a buckling mode, which may induce plastic deformation. This approach of using elastic behavior reduces the variability within the system, allowing for a smooth transition between engagement and disengagement of the clutch. The braid expands uniformly, simultaneously inducing multiple points of contact with the inside of the needle. The sensitivity of the mechanism can be adjusted by varying one or more of 1) the pics per inch (PPI) of the braid and hence the braid angle, 2) the cross sectional profile of the wires and 3) the gap between the outer diameter of the relaxed braid and the inner diameter of the needle 4) the composition of the braid, and 5) the composition of the material with which the braid engages.

(43) The braid PPI may by any suitable PPI between 10-70 PPI inclusive in some embodiments, or any suitable PPI between 30-50 PPI inclusive in some embodiments. Cross-sectional profiles may be circular, elliptical, square, rectangular, or any other suitable shape. In some embodiments, the gap between the outer diameter of the relaxed braid and the inner diameter of the needle is sufficient to ensure that there is limited frictional contact between the braid and the needle when the braid is in its relaxed state. In some embodiments of smaller diameter applications, the gap may be 1 mm or less.

(44) The braid is typically made of one or more metals, such as stainless steel, nitinol, cobalt chromium, or polymers, or a combination thereof, or any other suitable metal or material. The material and surface topography of the needle may include a metallic or polymeric coating.

(45) In some embodiments, the long, thin flexible wires or other elements may not be interlaced, but instead be grouped together. For example, several, dozens, or hundreds of long, thin, flexible wires may be bundled together to form a clutch mechanism. The wires may bow outwardly when a force is applied to an end of the group of wires.

(46) Further advantages of this new approach are shown in FIGS. 6c and 6d. Because the braid mechanism is placed on a tubular stylet with a lumen in some embodiments, fluid can pass freely through the device via the lumen. This arrangement can permit the device to incorporate a flash back element for the user, where blood or other internally pressurized fluid can be viewed through a transparent portion toward the proximal end of the needle or syringe (often at the needle hub), providing additional assurance that the correct cavity has been located or reached. Also, the braid based stylet and needle can be placed over a guidewire. This makes the technology usable for a broad range of internal over-the-wire catheter-based applications.

(47) Further embodiments of needle system with a clutch mechanism are shown in FIG. 7. In the schematic shown in FIG. 7b, the stylet plays an active role in penetrating through the tissue, while the outer tube is a hollow cannula. The clutch element is designed to buckle easily once it exits the needle, meaning clutch element no longer transmits a longitudinal force to the needle tip. For improved effectiveness, the clutch element is located as close as possible to the distal end of the assembly.

(48) As shown in FIGS. 7C.sub.i and 7C.sub.ii, the assembly is designed to deliver a capsule to the cavity in an efficient and user-friendly manner. The capsule is placed at the proximal end of the stylet and slots into a groove but is not attached. When a region of less resistance is reached, the capsule is released in a semi-automated fashion. In certain applications, this could have the advantage of drug delivery with zero or limited blood loss. For purposes herein, the term capsule is intended to include pills, tablet, caplets or any other drug delivery device.

(49) 1.2 Bellows-Based Clutch

(50) In an alternative embodiment, the clutch mechanism is activated using a bellows arrangement which expands radially under axial compression (see FIG. 8a). The mechanical properties of the bellows and the dimensions of bellows can be tailored to adjust the sensitivity of the clutch mechanism. In FIG. 8b, the bellows mechanism is illustrated with corresponding engagement features on the inner diameter of the needle. The engagement features may provide a positive engagement with the expanded bellows.

(51) 1.3 Polymer/Foam Based Clutch

(52) FIG. 9a shows a clutch arrangement with a poisson effect clutch element as described in U.S. Patent Application Publication No. 2011/0125107, which is hereby incorporated by reference. This mechanism is based on the inclusion of a polymer (e.g. a molded foam), which expands radially as it is compressed axially to engage with the needle. FIGS. 9b-9c illustrate various improvements to the arrangement illustrated in FIG. 9a. In FIG. 9b, the clutch element includes a central bore to permit flow of fluid through the needle lumen. The inclusion of this feature facilitates communication between the distal and proximal ends of the needle, which allows for the use of a visual indicator of correct needle placement (e.g., flash back), and/or administration of a drug or other therapeutic agent without the requirement of stylet removal.

(53) A preferred embodiment of this mechanism is illustrated in FIG. 9c, where fin features on the outer diameter of the clutch increase the channel size for fluid flow when the clutch is engaged. To increase the friction between the stylet and the needle in the engaged state, micropatterned bumps (e.g., rubber) or other textures may be included on the outside of the fins.

(54) 1.4 External Mechanism

(55) In FIG. 10a, one element of a clutch mechanism is illustrated where the clutch is external to from the needle. This approach has several advantages: The user is able to view the clutch engaging and disengaging, and also view in some embodiments flash back indication from fluid in the target cavity; The user is familiar with the components used, that is, the device appears similar to a typical syringe; Modular devices can be used and interchanged easily for adaptability to any current needle product; and Can be used with much smaller needle gauges

(56) Further, an indicator may be included so that the user does not push too far. For example, Point A cannot be advanced as far as Point B, otherwise the needle and stylet will advance together (it should be noted that the distance between A and B can be longer or shorter than illustrated in FIG. 7.

(57) The increased working length may induce more variability within the system in some embodiments. The stylet being introduced is very stiff in some embodiments to prevent the stylet distal of the clutch from bending or buckling.

(58) FIG. 10b is a graph showing the results of an analytical model based on Equation 12 from Jedwab and Clerc, A Study of the Geometrical and Mechanical Properties of a Self-Expanding Metallic StentTheory and Experiment, Journal of Applied Biomaterials, Vol. 4, 77-85 (1993), showing the load F acting on a stent. Also see the associated Erratum in Vol. 5, 273 (1994). Equation 12 is provided as:

(59) $F=2n\left[\frac{{\mathrm{GI}}_p}{K_3}\left(\frac{2\sin }{K_3}-K_1\right)-\frac{\mathrm{EI}\mathrm{Tan}}{K_3}\left(\frac{2\cos }{K_3}-K_2\right)\right]$

(60) where K.sub.1, K.sub.2 and K.sub.3 are constants given by

(61) $K_1=\frac{\mathrm{Sin}2{}_0}{D_0}$$K_2=\frac{2{\mathrm{Cos}}^2{}_0}{D_0}$$K_3=\frac{D_0}{\mathrm{Cos}{}_0},$

(62) I and I.sub.p are the moment of inertia and polar moment of inertiat of the wire, respectively, E is Young's moudulas of elasticity, and G is the rigidity modulus.

(63) The graph in FIG. 10b shows estimates of how the diameter of a radially unconfined braided member changes in response to an axial force. Curves for different initial pitch angles are provided. The analytical model does not incorporate friction or account for contact with a needle.

(64) 1.5 Clutch Syringe

(65) FIG. 11 illustrates another embodiment, where the clutch is incorporated into a loss of resistance syringe. In this embodiment, a clutch needle or a regular needle is used to locate the target area of reduced resistance. As a means of ensuring that a therapeutic will be delivered only to the target zone, the sensitivity of the clutch is designed such that when the needle tip is located in the high resistance zone, R1, the clutch engages upon attempted depression of the plunger. The plunger mounted clutch engages with the inner diameter of the syringe barrel, causing increased resistance. This increased resistance makes it impossible or extremely difficult to depress the plunger when the needle tip is in R1, providing a safety mechanism for the user. Conversely, when the syringe is located in R2, the resistance at the needle tip is insufficient to cause the clutch to engage with the ID of the syringe barrel, allowing infusion to occur. The clutch mechanism could be located along the length of the barrel, preferably toward the distal end, or it may be incorporated into the plunger tip itself in some embodiments.

(66) For one or more of the embodiments described above, a device that is advanced to a target region may be used to withdraw and/or infuse fluids, such as liquids.

(67) 2. Needles that Target and Infuse Selectively

(68) Introduction

(69) While advancements in visualization techniques, such as MRI and ultrasound have facilitated the interventionalist in needle directing, the mechanics of needle insertion and delivery in routine procedures have not changed. There is a need for low cost, user-friendly methods of targeted infusion.

(70) Particular difficulties are encountered when targeted injection is critical to clinical outcome. For example, intra-articular injection with the requirement of drug delivery exclusively to the synovial sac only can pose specific challenges. Conventionally, the physician is unable to routinely detect sufficient tactile feedback when the needle passes through the synovium (a <0.1 mm thick membrane). Applicant has recognized a need for devices which can successfully deliver drugs exclusively to synovial sac, through improved targeting by taking advantage of distinct changes in the local mechanical environment inside the synovial sac compared to the surrounding tissue and/or by providing augmented tactile feedback to the physician. It would be extremely useful for routine outpatient procedures, for the physician to be able to inject with confidence of accurate placement without the requirement for ambiguous, costly and time consuming image guidance.

(71) The methods and devices described herein also may be used for medical procedures including, but not limited to, Vascular Access (including arterial cannulation, central venous catheterization and AV Fistula Access), lymphatic access, Peritoneal Access, Tracheostomy, Placement of chest tubes, Intra-articular Injection, Intervertebral Injection, Epidural and Spinal Anesthesia, Suprachoroidal injection, Ocular Injection, laparoscopy, percutaneous access to the brain, enhanced local delivery of therapeutics to localized tumors. Methods and devices also may be used purely for sensing application, and/or to deliver agents of interest in solution or suspension and/or sample tissues, cells, or fluids. Further applications include access, withdrawal and infusion to and from the bladder, pleural effusion, tympanic membrane, trachea, cricothyroid membrane, embryonic sac, uterus, ventricular drainage, catheter mounted endovascular procedures including crossing a thrombus or emboli, calcification or recannulization.

(72) 2.1 Infusion/Aspiration

(73) In the case of targeted infusion to the synovial sac, one approach takes advantage of the pressure differential that exists as the synovium is crossed. Miniaturized pressure transducers are too expensive for use in routine procedures. A 1 mm pressure sensor can sell for approximately $3500 and requires a power line and amplifier which can cost approximately $7000. Applicant has recognized a need for cost-effective devices and methods for selective injection into a target site, such as the synovial sac.

(74) Each of needle design, hole positioning, number of infusing holes and infusion pressure can influence the likelihood of successful delivery. Below, several embodiments which achieve targeted delivery are described, using the example of synovial sac as the target site.

(75) 2.1.1 Multi-Hole Needles

(76) Traditionally, standard double bevel needles (see FIG. 12a) have been used for intra-articular aspiration and drug delivery. Applicant has recognized that a design which more closely resembles a Sprotte needle, traditionally used for catheter delivery in intrathecal injections for spinal anesthesia, can achieve more efficient delivery of drug to compartments or potential spaces, such as the synovial sac. In particular, a pencil point needle with multiple openings can be effective. An illustration of a pencil point needle, with a centrally located cutting point and recessed eye is illustrated in FIG. 12b.

(77) 2.1.1.1 Multi-hole Needle Pencil Point Needle

(78) One method of improving the likelihood of successful infusion is to use a multi-hole needle approach. Cartilage in the knee joint is usually 1-3 mm thick. The underlying bone can be used as a reference point, such that holes start at 1 mm proximal to the distal tip of the needle. When a fluid filled multi-hole needle is inserted until contact is made with the bone, one or more of the holes is located inside the synovial sac. A collapsed, non-effusive synovial sac tends to have a lower pressure than the surrounding interstitial tissue. When care is taken to infuse at a slow rate, the drug is largely delivered through the holes that offer the least resistance to flow residing in the synovial sac. FIGS. 13A and 13B illustrate embodiments of various configurations of multi-hole needles.

(79) Other examples of target regions or sites which may exhibit a lower resistance than surrounding regions include open spaces or cavities, or regions of loose tissue surrounded by denser tissue.

(80) In FIGS. 14A, 14B, 14C and 14D, a multi-hole needle is deployed into a centrifuge tube contacting two distinct layers of silicone, separated by a very thin gap, representing a target cavity within tissue. Irrespective of the exact location of the holes relative to the gap, the injected red dye is delivered exclusively to the narrow cavity between the two blocks of silicone. In this case the surrounding silicone offers sufficient mechanical resistance to allow fluid to be effused only from the hole exposed to the cavity.

(81) Similarly, when a multi-hole needle, full of liquid and/or gas, is placed across a membrane that has a pressure differential, upon injection, the liquid is seen to largely infuse into the area of lower pressure (see FIG. 15).

(82) In another embodiment of the multi-hole needle, each hole is individually exposed to an orifice in an inner tube through which the drug is to be injected (the inner tube is plugged at the distal end). The physician exposes one hole at a time, starting in a distal to proximal fashion, until the physician feels a drop in resistance and is able to infuse (see FIG. 16). The same setup can be used to introduce a catheter through each hole until it enters without resistance indicating it is in a fluid-filled cavity. Similarly, in a simplified approach, the inner element consists of a standard hollow tube. As the hollow tube is retracted from distal to proximal, it sequentially exposes the first hole, then the first and second hole, etc. until a drop in resistance is felt and the physician can infuse the drug.

(83) In a further embodiment of this approach, an adjustable internal wedge is used to angle an internal catheter to be directed out a lateral hole; if resistance is encountered when attempting to extrude the catheter, the wedge is retracted to align with the next lateral hole. An attempt is again made to extrude the catheter, and this process is repeated in a distal to proximal fashion, until the catheter is inserted into the cavity of low resistance.

(84) The leading edge of the needle and device embodiments described above may be a pencil point or may be a double bevel needle point, or may be any suitable needle point or leading edge. In some embodiments, the leading edge is closed, that is, the distal tip of the needle or other penetrating element does not have an opening to a lumen.

(85) In some embodiments, the lumen may extend only partially along the device, or may be entirely outside of the device. In such an embodiment, the lumen openings may be lumen extensions which extend from a common lumen and extend to a sidewall of the device. For example, a lumen may be positioned distal to the penetrating portion of the device and include three lumen extensions which reach the sidewall of the penetrating portion at different longitudinal positions along the penetrating device. In this manner, the lumen has three openings which receive the same fluid pressure when pressure is applied to the lumen fluid.

(86) 2.1.1.2 Multi-Hole Needles with Adjustable Sensitivity

(87) Needles which have a tunable sensitivity offer useful advantages in targeted drug delivery. For example, in FIG. 17, a multi-hole needle is illustrated which has an inner element with corresponding holes that can be rotated to adjust the pressure required to infuse using the needle. The physician starts with no overlap and applies a constant infusion pressure. The inner element is then gradually rotated until the drug begins to infuse. This helps maximize the capacity of the needle to inject into a low pressure cavity.

(88) In another embodiment, the holes are offset in a spiral fashion. In the case where the holes are in a spiral configuration, a catheter is introduced through each hole until it enters without resistance indicating it is in a fluid-filled cavity.

(89) Another embodiment of this concept is illustrated in FIG. 18. In this case, the holes in the inner element are covered by cantilever-like elements. When the inner element is rotated relative to the outer element, which has a corresponding longitudinal slot, more of the cantilever elements are exposed. Once a sufficient amount of the cantilever beam is exposed to overcome the resistance of the surrounding tissue, the holes in the inner element open. If the needle is placed through a pocket of low resistance, the corresponding cantilever is the first to open, allowing exclusive injection into that space.

(90) 2.1.1.3 Multi-Hole Needles with Breakable Element

(91) Another method of promoting selective injection through a multi-hole needle is illustrated in FIG. 19. Here, each hole is covered with a highly distensible non-porous membrane of pliable material. When infusing pressure is applied internally, the membranes begin to expand. The membrane in the pocket of least resistance expands the fastest. This membrane expands to a point of failure, or may be intentionally ruptured as it contacts a sharp edge at a threshold point.

(92) 2.1.2 Changes to Viscosity of Therapeutic Agent

(93) The capacity and speed at which a liquid is able to flow into an area of reduced resistance is influenced by its viscosity. Whereas as a low viscosity liquid may tend to move freely from the needle into the surrounding tissue once infusion pressure is applied, a higher viscosity liquid will move at a slower rate and tend not to disperse into the surrounding tissue. For this reason, by varying the viscosity of the solution, more efficient delivery of the therapeutic agent to a potential space may be achieved.

(94) 2.1.3 Dual Lumen Needle with Balloon Indicator and Separate Delivery Channel

(95) In FIG. 20, one embodiment of selective delivery to a cavity of less resistance is illustrated. According to this embodiment, a dual lumen assembly is provided. One lumen is connected to a pressure sensitive balloon. The other lumen is connected to a separate syringe that infuses through a separate orifice at the same longitudinal position once the balloon has been correctly placed. The balloon is free to inflate when the principal channel is pressurized at atmospheric pressure. The needle is inserted into the tissue with the balloon deflated. The balloon is then pressurized such that the needle is still free to pass through the tissue without additional resistancethis channel is held at this pressure (e.g., syringe is locked) and the needle is advanced further. The balloon expands once the cavity of lower pressure is entered. The expanded balloon provides a tactile feedback to the user by providing resistance when the user pulls lightly on the needle. The supporting stylet is then removed from the secondary infusion channel and the desired medium is infused, secondary to aspiration if necessary. As will be apparent to one of skill in the art, the fluid used to inflate the balloon (or other membrane) may be a gas or a liquid.

(96) One embodiment of a balloon element of this device is shown in FIG. 21. In other embodiments, instead of providing a secondary channel, the balloon is configured to be porous once expanded or to have a central lumen through which the injection can be made, without the need for a secondary channel.

(97) Any suitable type of membrane, such as a balloon or other material, may be used in some embodiments. A single membrane covering multiple openings may be used in some embodiments, or separate membranes for each opening may be used. A membrane may cover an opening by being positioned on the outside of the opening, the inside of the opening, or intermediate the outside and inside of the opening.

(98) 2.2 Needle Uses

(99) In each of the above embodiments, drugs may be delivered through the needles in liquid form, or as a suspension of micro-particles or nano-particles containing a drug. A suspension of micro-particles or nano-particles may delivered for use with imagine application instead of, or in addition to, the delivery of a drug. For example, imaging and/or contrast agents may be delivered by devices and methods disclosed herein. Additionally, the above needle designs can be used to deliver cells, organoids, or tissues. Various embodiments also may be used for biopsy or sensing purposes. Embodiments disclosed herein may be used to infuse vitamins, biomaterials, proteins, cells (e.g., stem cells or progenitor cells), peptides, RNAi, inorganic materials, polymers, hydrogel materials, hyaluronic acid, and/or lubricating materials. Further applications include the placement of fillers or aesthetic altering agents for dermatology and or cosmetic applications.

(100) In some embodiments, embodiments described herein may be used to withdraw fluids, such as liquids, from a body. For example, a vacuum may be applied to a multi-opening needle, and one or more openings that are subjected to a higher pressure than other openings may selectively pass liquid to a lumen, while the openings subjected to a lower external pressure pass limited or no liquids.

(101) Various devices and methods described herein do not necessarily need to be used for infusing or withdrawal of fluids. In some embodiments, the devices and methods may be used for detection or certain tissues, tissue regions and/or tissue spaces.

(102) Various types of openings may be used with embodiments herein, including slits, holes, and/or tapered opening (e.g. pyramid shaped, cone shaped, or telescoping). Opening may be patterned or meshed in some embodiments, and also may be nano-scale, micro-scale or macro-scale.

(103) In some embodiments, a lumen opening may be formed with a region of porous material. For example, the needle or other tube may include two or more regions with an increased porosity which permits fluid to escape or enter a lumen. In some embodiments, the entire tube may have a porous wall, and various regions may have different porosities. The tube may be porous on a micron scale or a nano scale in some embodiments.

(104) Target sites for one or more of the above-described embodiments may include, but are not limited to, blood vessels, degenerated discs (e.g., during kyphoplasty procedures), joints, fat, lungs (including collapsed lungs). Embodiments may be used as part of a tracheotomy procedure, placement of gastric tubes, and withdrawing fluid from cysts or the peritoneal cavity. Methods and devices disclosed herein also may be used to target a medical implant, or to access a region of the brain or a tumor (e.g., at the necrotic nerve).

(105) Further applications include industrial applications with larger penetrating elements and tubes. For example, a multi-opening pipe may be used to inject cement or withdraw oil. For injecting cement, when one or more of the openings reaches a region of lower pressure, cement may be injected. For withdrawing oil, when one or more of the opening reaches an area of higher pressure, oil may be drawn into the tube. Of course, embodiments disclosed herein may be used for other non-medical applications as well. Embodiments disclosed herein may be used for short term application and/or long term application. For example, embodiments may be used for cannulation or implantation.

(106) Having thus described several aspects of at least one embodiment of this invention, it is to be appreciated various alterations, modifications, and improvements will readily occur to those skilled in the art. Such alterations, modifications, and improvements are intended to be part of this disclosure, and are intended to be within the spirit and scope of the invention. Accordingly, the foregoing description and drawings are by way of example only.