MICROCAVITY-CONTAINING POLYMERIC MEDICAL DEVICES FOR ENHANCED ULTRASONIC ECHOGENICITY

Abstract

An ultrasound-detectable polymeric device that offers superior visibility of the body of the device and decreased ultrasound angle dependence through the use of microcavities and methods of manufacturing thereof is disclosed. These microcavities enable superior ultrasound visualization due to diffuse reflection of sound waves when compared to solid polymeric objects, ensuring that a strong signal is received at the source of the ultrasound transducer and providing strong image contrast throughout the entire cross-section of the implant that is also robust to variable angles of insonation.

Claims

1. An ultrasound-detectable medical device comprising a polymer with microcavities dispersed in some or all of its body capable of providing improved visibility throughout some or all of its volume and under variable angles of insonation.

2. The ultrasound-detectable device of claim 1, wherein the diameter of the microcavities is about 0.1 to about 950 microns.

3. The ultrasound-detectable device of claim 1, wherein the diameter of the microcavities is about 50 to about 350 microns.

4. The ultrasound-detectable device of claim 1, wherein the volume to volume ratio of polymer structures to cavity space is than 60%.

5. The ultrasound-detectable device of claim 1, wherein the volume to volume ratio of polymer structures to cavity space is about 12% to about 50%.

6. The ultrasound-detectable device of claim 1, wherein the microcavities are formed by at least one gas.

7. The ultrasound-detectable device of claim 6, wherein the at least one gas is selected from CO.sub.2 or N.sub.2.

8. The ultrasound-detectable device of claim 1, wherein the microcavities are created via a chemical reaction within the material such that gas is released.

9. The ultrasound-detectable device of claim 1, wherein the part of the device where improved echogenicity is desired contains a microcavity-containing polymer and the remainder is composed of a non-microcavity containing polymer or non-polymer.

10. The ultrasound-detectable device of claim 1, wherein the microcavities are encapsulated by an outer skin layer.

11. The ultrasound-detectable device of claim 1, wherein the device is designed for use as an echogenic marker for ultrasound location in the human body.

12. The ultrasound-detectable device of claim 1, wherein the material comprises one or more resorbable polymers selected from the group comprising poly(lactic-co-glycolic acid) (PLGA), polylactide (PLA), polyglycolide (PGA), polyhydroxyalkanoate (PHA), polycaprolactone (PCL) and copolymers thereof.

13. The ultrasound-detectable device of claim 1, wherein the material comprises one or more non-resorbable polymers selected from the group comprising polycarbonate, polyetheretherketone, polypropylene, silicone or polyethylene.

14. A method for preparing the ultrasound-detectable marker of claim 1 comprising the steps of: a. foaming the polymer by introducing a blowing agent; and b. injecting the foamed polymer into a mold to form said marker.

15. A method for using a device of claim 1 comprising: a. inserting the device of claim 1 in a patient; b. detecting the device using B-mode ultrasound during or after surgery; and c. detecting the device in multiple frames, representing different angles of insonation, during or after surgery.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0014] FIG. 1 displays the cross section of a medical device with internal microcavities. The cavities resemble a spherical or semi-spherical shape across a range of sizes. The device contains an outer layer free of microcavities.

[0015] FIGS. 2A and 2B respectively display the reflectance of the ultrasound beam for a medical device with and a medical device without microcavities. FIG. 2A, a medical device without microcavity, exhibits a specular reflection of the ultrasound beam, which results in little to no signal returning to the probe. FIG. 2B displays the diffuse reflection that is generated when the ultrasound beam contacts the microcavities. Unlike in FIG. 2A, a significant portion of the signal is reflected back to the probe, irrespective of the originating angle of the emitted signal.

DETAILED DESCRIPTION

[0016] In one aspect, the invention provides an ultrasound-detectable medical device comprising a polymer with microcavities dispersed in some or all of its body capable of providing improved visibility throughout some or all of its volume and under variable angles of insonation FIGS. 1 and 2B. In some instances, the microcavities extend throughout the entire volume of the medical device. In other instances, the microcavities occupy a central region of the medical device. In additional instances, the space containing microcavities is surrounded by an outer layer of material without microcavities.

[0017] In another aspect, the invention provides an ultrasound-detectable device wherein the diameter (microcavity size) ranges between 0.1 to 950 microns, and commonly between 50 to 350 microns. In some instances, the microcavity diameter exceeds 1,000 microns. In other instances, the microcavity diameter ranges from 10 to 500 microns. In additional instances, the microcavities exhibit diameters from 10 to 1,500 microns.

[0018] In a further aspect, the invention provides an ultrasound-detectable device wherein the ideal volume to volume ratio of cavity space to polymer structures should be less than 60%, and is commonly between 12% and 50%. In some instances, the microcavities comprise between 30 to 50% of the volume. In other instances, the volume ratio of microcavities exceeds 60%.

[0019] The ultrasound-detectable device contains microcavities. In one aspect of the device, the microcavities are composed of gas. In one aspect of the invention, the device is created via injection molding. In another embodiment, the device is manufactured by extrusion. In some aspects of the invention, microcavities are created by introducing gas into the polymer material prior to manufacturing, commonly through injection. In other aspects of the invention, microcavities are introduced during the manufacturing process, which can be performed by injecting gas into a mold either before, while, or after the polymer enters the mold.

[0020] The microcavities may be composed of a variety of biocompatible gases. In some instances, super-critical CO2 is used, and in other instances, N2 is used.

[0021] In another embodiment, the microcavities are created via a chemical reaction such that gas is released into the polymer. This may be accomplished with a foaming agent or other chemical processes. The gas may be activated by pressure or temperature changes in the manufacturing process.

[0022] For a variety of reasons, including mechanical, material degradation, visibility, and manufacturing considerations, it is desirable to have the microcavities consume a region within the overall volume, rather than the entire device. In one embodiment, the region containing the microcavities is central to the device. In this embodiment, the region containing the microcavities is surrounded by a layer of polymeric or non-polymeric material that does not contain microcavities. In other embodiments of the device, this external layer, or skin, contains microcavities, though of a reduced density. In further embodiments, the region containing the microcavities resides on the top surface of the device (superficial towards the position of the ultrasound probe), while in other embodiments, the microcavity region resides on the bottom surface of the device.

[0023] In one aspect of the invention, there is an outer layer of the device which is meant to maintain the structural integrity of the inner microcavity-containing region. This outer layer does not contain microcavities and thus provides a barrier protecting the inner region, especially from fluid flow, which could accelerate degradation and also negatively impact the ultrasonic visibility. In another aspect of the invention, the outer layer described has a smooth surface to minimize irritation and other adverse events to surrounding tissue or vessels once the device is implanted.

[0024] Another aspect of the device relates to the visibility of the device under ultrasonic imaging. In this aspect, the device is used as an echogenic marker for ultrasound location in the human body. Some anatomic structures that can be marked using this device include: veins, arteries, soft tissue, urinary tracts, nerves, and ducts. The device enables location of any of these structures after implantation. In particular, the device gives the clinician knowledge of the spatial relationship between the ultrasound probe and anatomic structure, independent of the angle of insonation. The device enables locating the anatomic location repeatedly across many examinations after placement of the device. The size of the device ranges from 1 to 60 mm in length, 1 to 60 mm in width, and 1 to 40 mm in height. Some embodiments of the device represent curved, cradle-like structures. Other embodiments of the device are spheres, rectangles, cubes, plates, pellets, and discs. Some instances of when this device could be used are for: microvascular anastomoses, solid organ transplants, vascular bypass, and vascular access.

[0025] In one embodiment of the device, it is comprised of one or more resorbable polymers selected from the group of: poly(lactic-co-glycolic acid) (PLGA), polylactide (PLA), polyglycolide (PGA), polyhydroxyalkanoate (PHA), polycaprolactone (PCL), polyethylene glycol (PEG) and copolymers thereof.

[0026] In another embodiment of the device, it is comprised of one or more non-resorbable polymers selected from the group of: polycarbonate, polyetheretherketone, polypropylene, silicone, polyethylene, polyester, polybutylene terephthalate (PBT), polyvinyl chloride, polyethylsulfone, polyacryclate, polyetheretherketone, poly-p-xylylene (parylene), polytetrafluoroethylene, cyclo olefin, acrylonitrile butadiene styrene, polyeurethane, acrylonitrile styrene acrylate, acetals, polyetherimide, ethylene, chlorotrifluoroethylene, ethylene tetrafluoroethylene, polyvinyl fluoride, polyvinylidene difluoride, and polyhydroxybutyrate. In a further embodiment, the device is comprised of both resorbable and non-resorbable materials, which may be in the form of multiple sections with unique materials, a single blend of materials, or multiple sections of blended materials.

[0027] In one aspect of the invention, the device is manufactured via a foaming process. Microcavities are introduced into the polymer by introducing a blowing agent. The blowing agent created the cellular structure of the microcavities. In one embodiment of the invention, the blowing agent is a physical blowing agent. In another embodiment, the blowing agent is a chemical blowing agent. An alternative way of generating the foam is using a solvent such as acetone. In addition to introducing the foaming agent, this invention describes injecting the polymer into a mold. An alternative way of producing the device is via extrusion.

[0028] This invention describes a method for using the device where the device is first inserted into a patient, it is then detected using B-mode ultrasound during or after surgery, and the device is detected in multiple frames, representing different angles of insonation. The ultrasound user can leave the patient and return to find the device at a later time point. This is important because it is often desired to track anatomical or physiological features over a time horizon of multiple days or weeks, and sometimes months or years. This means that user needs to walk away from the patient, return to the patient, and easily locate the device. Another critical feature of the invention is the ability to detect the device using ultrasound from any angle of insonation. This is important because a non-expert is able to locate the marked site and use the visual information to achieve a desired angle or set of angles. The invention enables strong visibility in angles ranging from 25 degrees to 155 degrees from the skin surface. The microcavity feature of the invention provides the ability to visualize the device across such a broad range of insonation angles. Due to the geometry and microcavity feature of the device, the user is able to understand the angle of insonation. Therefore, the user can repeatedly match the same orientation upon each examination, generate the same image of the device, and thus compare anatomic or physiologic conditions reliably over time. Alternatively, the user can approach the device from a new orientation in each additional examination, though will have the geometric information from the device to make proper calculations to adjust for the new angle of insonation.

[0029] The device should not be compromised at 40 degrees Celsius when in a dark and moist environment, such as human or animal tissue. Compromise includes but is not limited to geometric changes, mechanical deformation, degradation, or microcavity change. The device must maintain its original integrity for at least 72 hours in such conditions. The device must yield contrast when visualized using B-mode ultrasound between 1 cm and 5 cm deep from the surface of the skin.

Examples

Example 1

[0030] An ultrasound-detectable medical device made by extrusion. Specifically, a Nano 16 mm extruder was used with a GFA3-10-30 screw element at 270 mm. The extruder has four zones, each with individual temperature control, which ultimately lead to a die to achieve the desired geometry of the device. The zones were first preheated to 110, 140, 130 and 100 C. respectively. The pressure within the die ranged from 10-70 psi. The feeding rate of the polymer was 2.5 cc/min, and the screw speed fell between 75-100 rpm. The torque on the screw ranged from 1500-3000 Gm. The supercritical CO.sub.2 was injected at 200 psi with a flow rate of 20 cfh. When the extruded polymer left the die, it was cooled via an air jacket. In cases when it was desired to achieve variance along the extrusion axis, the device was laser cut once it cooled to room temperature using the air jacket.

Example 2

[0031] An ultrasound-detectable medical device made by injection molding. The polymer was introduced into the mold via injection through the port. While the material was being injected into the mold, CO.sub.2 gas was simultaneously injected to provide microbubbles. In another example, the CO.sub.2 was introduced into the material prior to injection into the mold. Once the material filled the mold, the mold was released via its pins, the part was removed, and the process was repeated.