Patent Description:
A large number of Americans each year suffer a hemorrhagic stroke. Most of these occur in the basal ganglia, and a third of those include bleeding into the ventricles. Half of these victims will die within months, and a quarter of the survivors will have a second stroke within five years. Bleeding in the brain occurs due to high blood pressure, aneurysms, and less frequently arterio-venous malformations (AVM), and increases in incidence with age. Factors including smoking, diabetes, and obesity play roles, as do amyloid deposits in the elderly.

With respect to stroke treatment, up to a large number of cases per year involve surgical intervention. The objectives of surgical intervention generally include clipping bleeding aneurysms, removing bleeding AVMs, and removing clot volume in intracranial hemorrhages (ICH).

In certain applications, an interventional radiologist will insert Goldvalve detachable balloons, Guglielmi detachable coils, or Onyx liquid embolic to occlude AVMs and saccular aneurysm. These applications are primarily preventive (e.g., preventing a second bleed). Other methods of reducing further bleeding include using embolics and FVIIa, and/or maintaining intracranial pressure below mean arterial pressure. Medical therapy typically also includes head elevation, Tylenol for temperature reduction, paralytics to prevent coughing, intubation to prevent aspiration, Mannitol and diuretics to reduce fluid volume, and seizure preventatives.

Recently, lytics have been considered as a treatment option to remove obstruction in the ventricles and to reduce intracranial pressure. See e.g., <CIT>. However, such treatment has not been widely adopted because it is generally considered too slow to provide sufficient clinical benefits. More recently, therapies have been developed that combine ultrasound with a lytic such as recombinant tissue plasminogen activator (rt-PA). In such therapies, the lytic and ultrasound can delivered through a microcatheter directly into spontaneous IVH or ICH patients, to facilitate evacuation of the hemorrhage. See e.g., <CIT>. <CIT> relates to a method and apparatus for treating hemorrhage and maintaining catheter patency in the brain and spine through a new and minimally invasive technique. <CIT> relates to a catheter for delivering ultrasonic energy and therapeutic compounds to a treatment site within a patient's vasculature, the catheter comprising a tubular body.

While such therapies have shown promise, there is a general desire to continue to improve the methods and apparatuses involved with such therapy.

Further embodiments of the inventions are defined by the dependent claims.

An embodiment of an ultrasound catheter for treatment of a blood clot resulting from an intracranial hemorrhage comprises an elongate tubular body having a distal portion, a proximal portion, and a central lumen. The catheter further comprises a plurality of ultrasound radiating elements positioned within the tubular body. A plurality of ports are located on the distal portion of the elongate tubular body, and are configured to allow a fluid to flow through the ports.

In another embodiment an ultrasound catheter assembly includes an elongate tubular body having a distal portion and a proximal portion. The elongate tubular body has material properties similar to that of standard external ventricular drainage (EVD) catheter. A lumen is formed within the elongate tubular body. The lumen includes a plurality of ports on the distal portion of the elongate tubular body configured to allow fluid to flow therethrough. An ultrasonic core is configured to be received within the lumen of the catheter. The ultrasonic core comprises a plurality of ultrasound radiating elements.

In another embodiment, an ultrasound catheter comprises an elongate tubular body having a distal portion and a proximal portion. A first drainage lumen is formed within the elongate tubular body. The drainage lumen includes a plurality of drainage ports on the distal portion of the elongate tubular body configured to allow fluid to flow therethrough. A delivery lumen is formed within the elongate tubular body. The delivery lumen includes a plurality of delivery ports on the distal portion of the elongate tubular body configured to allow fluid to flow therethrough. A plurality of ultrasound radiating elements are positioned within the elongate tubular body.

Exemplary embodiments of the method and apparatus for treatment of intracranial hemorrhages are illustrated in the accompanying drawings, which are for illustrative purposes only. The drawings comprise the following figures, in which like numerals indicate like parts.

As set forth above, methods and apparatuses have been developed that allow an intracranial hemorrhage and/or a subarachnoid hemorrhage to be treated using ultrasonic energy in conjunction with a therapeutic compound. As used herein, the term "intracranial hemorrhage" encompasses both intracerebral hemorrhage and intraventricular hemorrhage. Although some embodiments may be disclosed with reference to intracerebral hemorrhage or intraventricular hemorrhage, the embodiments can generally be used to treat both types of intracranial hemorrhages. Disclosed herein are several exemplary embodiments of ultrasonic catheters that can be used to enhance the efficacy of therapeutic compounds at a treatment site within a patient's body. Also disclosed are exemplary methods for using such catheters. For example, as discussed in greater detail below, the ultrasonic catheters disclosed herein can be used to deliver a therapeutic compound to a blood clot in the brain, allowing at least a portion of the blood clot to be dissolved and/or removed, thereby reducing damage to brain tissue. Although described with respect to intracranial use, the embodiments disclosed herein are also suitable for intraventricular use in other applications. Accordingly, the term "intracranial use" can also include intraventricular use.

As used herein, the term "therapeutic compound" refers broadly, without limitation, and in addition to its ordinary meaning, to a drug, medicament, dissolution compound, genetic material or any other substance capable of effecting physiological functions. Additionally, a mixture including substances such as these is also encompassed within this definition of "therapeutic compound". Examples of therapeutic compounds include thrombolytic compounds, anti-thrombosis compounds, and other compounds used in the treatment of vascular occlusions and/or blood clots, including compounds intended to prevent or reduce clot formation, neuroprotective agents, anti-apoptotic agents, and neurotoxin scavenging agents. Exemplary therapeutic compounds include, but are not limited to, heparin, urokinase, streptokinase, tPA, rtPA, BB-<NUM> (manufactured by British Biotech, Oxford, UK), plasmin, IIbIIa inhibitors, desmoteplase, caffeinol, deferoxamine, and factor VIIa.

As used herein, the terms "ultrasonic energy", "ultrasound" and "ultrasonic" refer broadly, without limitation, and in addition to their ordinary meaning, to mechanical energy transferred through longitudinal pressure or compression waves. Ultrasonic energy can be emitted as continuous or pulsed waves, depending on the parameters of a particular application. Additionally, ultrasonic energy can be emitted in waveforms having various shapes, such as sinusoidal waves, triangle waves, square waves, or other wave forms. Ultrasonic energy includes sound waves. In certain embodiments, the ultrasonic energy referred to herein has a frequency between about <NUM> and about <NUM>. For example, in one embodiment, the ultrasonic energy has a frequency between about <NUM> and about <NUM>. In another embodiment, the ultrasonic energy has a frequency between about <NUM> and about <NUM>. In yet another embodiment, the ultrasonic energy has a frequency of about <NUM>. In certain embodiments described herein, the average acoustic power of the ultrasonic energy is between about <NUM> watts and <NUM> watts. In one embodiment, the average acoustic power is about <NUM> watts.

As used herein, the term "ultrasound radiating element" or "ultrasound or ultrasonic element" refers broadly, without limitation, and in addition to its ordinary meaning, to any apparatus capable of producing ultrasonic energy. An ultrasonic transducer, which converts electrical energy into ultrasonic energy, is an example of an ultrasound radiating element. An exemplary ultrasonic transducer capable of generating ultrasonic energy from electrical energy is a piezoelectric ceramic oscillator. Piezoelectric ceramics typically comprise a crystalline material, such as quartz, that changes shape when an electrical current is applied to the material. This change in shape, made oscillatory by an oscillating driving signal, creates ultrasonic sound waves. In other embodiments, ultrasonic energy can be generated by an ultrasonic transducer that is remote from the ultrasound radiating element, and the ultrasonic energy can be transmitted, via, for example, a wire that is coupled to the ultrasound radiating element. In such embodiments, a "transverse wave" can be generated along the wire. As used herein is a wave propagated along the wire in which the direction of the disturbance at each point of the medium is perpendicular to the wave vector. Some embodiments, such as embodiments incorporating a wire coupled to an ultrasound radiating element for example, are capable of generating transverse waves. See e.g., <CIT>, <CIT> and <CIT>. Other embodiments without the wire can also generate transverse waves along the body of the catheter.

In certain applications, the ultrasonic energy itself provides a therapeutic effect to the patient. Examples of such therapeutic effects include blood clot disruption; promoting temporary or permanent physiological changes in intracellular or intercellular structures; and rupturing micro-balloons or micro-bubbles for therapeutic compound delivery. Further information about such methods can be found in <CIT> and <CIT>.

<FIG> and <FIG> schematically illustrate one arrangement of an ultrasonic catheter <NUM> that can be used to treat a blood clot in the brain resulting from an intracerebral hemorrhage (ICH) and/or an intraventricular hemorrhage (IVH). <FIG> shows an enlarged detail view of a distal portion <NUM> of the catheter <NUM> and <FIG> illustrates an enlarged detail view of a proximal portion <NUM> of the catheter <NUM>. In the illustrated arrangement, the ultrasonic catheter <NUM> generally includes a multi-component, elongate flexible tubular body <NUM> having a proximal region <NUM> and a distal region <NUM>. The tubular body <NUM> includes a flexible energy delivery section <NUM> located in the distal region <NUM>. Within the distal region <NUM> are located a plurality of holes <NUM>, through which fluid may flow into or out of a central lumen <NUM> (<FIG>) that extends though the catheter <NUM>. Although the drainage holes <NUM> are shown as circular, the shape of the holes may be varied. For instance, the drainage holes may be oval, polygonal, or irregular. <FIG> illustrate modified embodiments of the catheter which include separate lumens for fluid delivery and for fluid evacuation.

The catheter <NUM> defines the hollow lumen <NUM> which allows for the free flow of liquids between the drainage holes <NUM> and the proximal port <NUM>. For instance, blood may flow from an area external to the ultrasonic catheter through the drainage holes <NUM> and into the lumen <NUM>. The blood may then flow proximally in the lumen <NUM> towards the proximal region <NUM> of the ultrasonic catheter, where it may be collected via the drainage kit. In certain embodiments, any number of therapeutic compounds may be introduced into the ultrasonic catheter through the proximal end <NUM>. The compounds, which may be dissolved or suspended within a liquid carrier, may flow through the lumen <NUM> and towards the distal end <NUM> of the ultrasonic catheter, ultimately exiting the catheter through drainage holes <NUM> and entering a treatment site.

In certain embodiments, negative pressure may be applied to the lumen <NUM> of the catheter to facilitate the flow of blood from the drainage holes <NUM> towards the proximal end <NUM>. In other embodiments, no external pressure is applied, and the conditions present at the treatment site are sufficient to cause the blood to flow proximally through the lumen <NUM>. In some embodiments, a positive pressure may be applied to the lumen <NUM> of the catheter <NUM> in order for therapeutic compounds or other liquids to pass distally through the lumen <NUM> towards the drainage holes <NUM>. In other embodiments, no external pressure is applied, and the liquid is permitted to independently flow distally and exit the drainage ports <NUM>.

The tubular body <NUM> and other components of the catheter <NUM> can be manufactured in accordance with a variety of techniques known to an ordinarily skilled artisan. Suitable materials and dimensions can be readily selected based on the natural and anatomical dimensions of the treatment site and on the desired access site. In addition, the surface of the catheter <NUM> can be coated with an antimicrobial material, such as silver or a silver based compound. In certain embodiments, the catheter may be biocompatible for use in the brain for up to <NUM> days, for up to <NUM> days, up to <NUM> days, or for up to <NUM> days. In one arrangement, the catheter can be coated with a hydrophilic material.

In some embodiments, the tubular body <NUM> can be between about <NUM> and <NUM> centimeters in length. In certain arrangements, the lumen <NUM> has a minimum inner diameter of about <NUM> millimeters and the catheter body has a maximum outer diameter of about <NUM>.

In one particular embodiment, the tubular body <NUM> has material properties similar to that of standard external ventricular drainage (EVD) catheters. For example, the tubular body can be formed of radiopaque polyurethane or silicone, which can be provided with antimicrobial features. In such embodiments, the catheter <NUM> by itself may not have sufficient flexibility, hoop strength, kink resistance, rigidity and structural support to push the energy delivery section <NUM> through an opening in the skull and then, in turn, the patient's brain tissue to a treatment site (e.g., one of the ventricles). Accordingly, the catheter <NUM> can be used in combination with a stylet <NUM> (<FIG>), which can be positioned within the tubular body <NUM>. In one embodiment, the device is configured to be compatible with Neuronaviagation systems by easily accommodating the Neuronavigation system stylet. The stylet <NUM> can provide additional kink resistance, rigidity and structural support to the catheter <NUM> such that it can be advanced through the patients' brain tissue to the target site. In certain embodiments, the stylet <NUM> can be configured to be used in combination with a standard image guided EVD placement system. As described below, after placement, the stylet <NUM> can then be removed to allow drainage through the tubular body <NUM>. In a modified arrangement, the tubular body <NUM> can be reinforced by braiding, mesh or other constructions to provide increased kink resistance and ability to be pushed with or without a stylet.

In one embodiment, the tubular body energy delivery section <NUM> can comprise a material that is thinner than the material comprising the tubular body proximal region <NUM>. In another exemplary embodiment, the tubular body energy delivery section <NUM> comprises a material that has a greater acoustic transparency than the material comprising the tubular body proximal region <NUM>. In certain embodiments, the energy delivery section <NUM> comprises the same material or a material of the same thickness as the proximal region <NUM>.

<FIG> shows an enlarged detail view of the proximal portion <NUM> of the ultrasonic catheter <NUM>. The proximal portion <NUM> includes a connector <NUM>. In the embodiment shown, the connector <NUM> comprises a series of annular rings <NUM> aligned in parallel. The connector <NUM> permits the catheter <NUM> to be joined to a drainage kit. For example, in one arrangement, the connector <NUM> is configured to connect to a standard EVD drainage kit that can include an attachment fitting that slides over the connector <NUM> or can include a buckle or joint that is fastened around connector <NUM>. Specific length and configuration of the connector <NUM> can vary according to the needs of the particular application, and to facilitate connection with various drainage kits. Additionally, the number of annular rings <NUM> may vary in certain embodiments.

In the illustrated arrangement of <FIG> and <FIG>, the catheter <NUM> can be use in combination with an inner core <NUM> (<FIG>) which can be inserted into the lumen <NUM> after the stylet <NUM> has been removed to deliver ultrasound energy to the target site. The core <NUM> can include proximal hub <NUM> fitted on one end of the inner core <NUM> proximal region. One or more ultrasound radiating members <NUM> are positioned within a distal region of the core and are coupled by wires <NUM> to the proximal hub <NUM>. In some embodiments, the inner core <NUM> can be inserted into the lumen <NUM> and/or along a side of the catheter <NUM>. In yet another arrangement, the core <NUM> can be inserted into the lumen <NUM> with the distal end including the ultrasound radiating members extending outside one of the holes positioned on the distal region of the catheter <NUM>.

In other embodiments, the catheter <NUM> can include separate lumens for drainage and for drug delivery. <FIG> show cross-sectional views of two embodimdnets of a catheter with multiple lumens. With reference to <FIG>, a fluid-delivery lumen <NUM> is located within the wall of the catheter <NUM>, between the outer surface and the inner lumen <NUM>, which may be used for fluid evacuation. In other embodiments, a plurality of fluid-delivery lumens <NUM> may be arranged within the catheter <NUM>. Although shown as substantially circular in cross-section, any number of shapes may be employed to provide for optimal fluid flow through the fluid-delivery lumen <NUM>. With reference to <FIG>, a separate fluid-delivery lumen <NUM> is located within a separate tube running longitudinally within the inner lumen <NUM>. In certain embodiments, a plurality of fluid-delivery lumens <NUM> may be arranged within inner lumen <NUM>. The size of fluid-delivery lumen <NUM> may be small enough so as to not interfere with the function of inner lumen <NUM> in evacuating fluid from the treatment site.

These separate lumens connect drainage and drug delivery holes positioned generally at the distal end of the catheter with drug delivery and drainage ports positioned at the proximal end of the catheter. In one embodiment, the device can include separate lumens for the drug and drain delivery such that the holes and ports for drug delivery and drainage are separated from each other. In some embodiments, the treatment zone (defined as the distance between the distal most and proximal most ultrasound transducer) can be about <NUM> to <NUM>. In other embodiments, the treatment zone may extend as far as <NUM>. The drug and drain ports can include luer type fittings. The ultrasound transducers can be positioned near or between the drain and drug delivery holes.

<FIG> are schematic illustrations of an ultrasonic catheter according to another embodiment. The catheter <NUM> contains components similar to that shown in <FIG> and <FIG>. However, in this embodiment, includes wires <NUM> embedded within the wall of the tube. As will be explained below, the wires can activate and control ultrasonic radiating elements located within the distal region <NUM> of the catheter <NUM>. Additionally, the catheter <NUM> may include thermocouples for monitoring temperature of the treatment zone, the catheter, or surrounding areas. In some embodiments, each ultrasound radiating element is associated with a temperature sensor that monitors the temperature of the ultrasound radiating element. In other embodiments, the ultrasound radiating element itself is also a temperature sensor and can provide temperature feedback. In certain embodiments, one or more pressure sensors are also positioned to monitor pressure of the treatment site or of the liquid within the lumen of the catheter.

In the embodiment shown, the wires <NUM> are bundled and embedded within the wall of the tubular body <NUM>. In other embodiments, the wires may not be bundled, but may, for example, each be spaced apart from one another. Additionally, in certain embodiments the wires may not be embedded within the wall of the tubular body <NUM>, but may rather run within the lumen <NUM>. The wires <NUM> may include protective and/or insulative coating.

The wires may be advantageously configured such that they can withstand tension applied to the catheter. For example, the wires may be able to withstand at least <NUM> pounds of tension. In other embodiments, the wires may be able to withstand at least <NUM> pounds, at least <NUM> pounds, or at least <NUM> pounds of tension. <NUM> pound equals <NUM>.

The wires may also be configured such that they increase the stiffness of the tubular body <NUM> as little as possible. The flexibility of the tubular body <NUM> facilitates the introduction of the catheter <NUM> into the cranial cavity. It may therefore be advantageous to select wires that only minimally contribute to the stiffness of the catheter. The wires chosen may be between <NUM> and <NUM> gauge. In other embodiments, the wires may be between <NUM> and <NUM> gauge, between <NUM> and <NUM> gauge, or between <NUM> and <NUM> gauge. The number of wires within the catheter is determined by the number of elements and thermocouples in a particular device.

In certain embodiments, the drainage holes <NUM> include radii on the outside of the holes, as can be seen in <FIG>. Applying a larger external radius to each drainage hole may improve the flow of blood into the drainage holes <NUM> and through the lumen of the catheter and may reduce damage to brain tissue during insertion and withdrawal. Although the drainage holes <NUM> are depicted as arranged in regular rows, the pattern may vary considerably. The length of the region in which the holes are located may be between <NUM> and <NUM>. In certain embodiments, the length may be between <NUM> and <NUM>, or the length may be about <NUM>.

In the embodiment shown, the annular rings <NUM> located within in the proximal region <NUM> of the catheter <NUM> may be connected to the wires <NUM>. In certain embodiments, a wire may be soldered to each annular ring <NUM>. An electrical contact may then be exposed on the outer diameter of the annular ring <NUM> to provide for an electrical connection to an individual wire. By virtue of this design, each wire, and therefore each thermocouple or element, may be addressed independently. In alternative embodiments, two or more wires may be soldered to an annular ring, thereby creating a single electrical connection. In other embodiments, the wires may meet electrical contacts at other points within the catheter <NUM>. Alternatively, the wires may pass through the wall of the tubular body <NUM> and connect directly to external apparatuses.

<FIG> is a schematic illustration of an ultrasonic catheter partially inserted into the brain. The catheter <NUM> may be positioned against the external surface of the skull, with the distal portion inserted through bore <NUM>. The bore <NUM> creates an access path through the skull <NUM>, dura <NUM>, and into the brain tissue <NUM>. Once in the brain tissue <NUM>, excess blood resulting from hemorrhaging may be accepted into the drainage holes <NUM> located on the distal region of the catheter. Due to the angle of entry into the brain, the tubular body <NUM> of the catheter <NUM> is advantageously kink resistant, in particular around a bend. Kink resistance is advantageous at the distal region <NUM> of the catheter <NUM>. As the catheter <NUM> is withdrawn from the brain tissue <NUM> and begins to straighten, excess stiffness of the catheter can result in the distal tip migrating into the brain tissue <NUM>. The presence of the drainage holes <NUM> contributes to the flexibility at the distal region <NUM> of the catheter <NUM>.

In one embodiment, the device can be placed using a tunneling technique which involves pulling the device under the scalp away from the point of entry in the brain to reduce the probability of catheter-initiated infections. In one embodiment, the catheter is made (at least partially) of a soft and pliant silicone material (and/or similar material) which will move with the brain matter during therapy without causing injury.

Dimensions of an ultrasonic catheter may vary according to different embodiments. For example, the Wall Factor is defined as the ratio of the outer diameter of the tube to the wall thickness. The inventors have discovered that a Wall Factor of <NUM> is useful in preventing kinking of the catheter. In particular, a Wall Factor of <NUM> may prevent kinking of the catheter around a <NUM> diameter bend, with the bend measured through the centerline of the catheter. The area of the tubular body <NUM> in which kink resistance is most advantageous is between <NUM> and <NUM> from the distal end of the device.

Various methods may be employed to impart kink resistance to the catheter <NUM>. For instance, the tubular body <NUM> may be reinforced with coil to prevent kinking of the catheter around bends. In other embodiments, the tubular body has a wall thickness that is chosen (in light of the material) sufficient to prevent kinking as the catheter is placed through a bend.

<FIG> illustrates one arrangement of the ultrasonic radiating elements <NUM>. <FIG> is an enlarged detailed view of a cross-section along line J-J in <FIG>. As shown, in one arrangement, the ultrasonic radiating elements <NUM> can be disposed in the distal region <NUM> of the ultrasonic catheter <NUM>. In other embodiments, thermocouples, pressure sensors, or other elements may also be disposed within the distal region <NUM>. The distal region <NUM> may be composed of silicone or other suitable material, designed with drainage holes <NUM> as discussed above. Ultrasonic radiating elements <NUM> may be embedded within the wall of the distal region <NUM>, surrounded by the silicone or other material. In addition to the ultrasonic radiating elements <NUM>, the catheter may include wiring embedded within the wall of the flexible tubular body, as discussed in more detail above with reference to <FIG>. The ultrasonic radiating elements <NUM> can include connective wiring, discussed in greater detail below. In various embodiments, there may be as few as one and as many as <NUM> ultrasonic radiating elements <NUM> can be embedded with the distal region <NUM> of the device. The elements <NUM> can be equally spaced in the treatment zone. In other embodiments, the elements <NUM> can be grouped such that the spacing is not uniform between them. In an exemplary embodiment, the catheter <NUM> includes two ultrasonic radiating elements <NUM>. In this two-element configuration, the elements can be spaced apart approximately <NUM> axially, and approximately <NUM> degrees circumferentially. In another embodiment, the catheter <NUM> includes three ultrasonic radiating elements <NUM>. In this three-element configuration, the elements <NUM> can be spaced approximately <NUM> apart axially, and approximately <NUM> degrees apart circumferentially. As will be apparent to the skilled artisan, various other combinations of ultrasonic radiating elements are possible.

<FIG> illustrates another arrangement of the distal region of an ultrasonic catheter <NUM>. <FIG> is an enlarged detail view of a cross-section along line H-H in <FIG>. In the configuration shown, two elements are spaced approximately <NUM> degrees apart circumferentially, and are equidistant from the distal tip of the catheter <NUM>. The catheter can include only two ultrasonic radiating elements <NUM> in the distal region <NUM>, or alternatively it may include four, six, eight, or more, with each pair arranged in the configuration shown. In embodiments containing more than one pair, the pairs may be aligned axially. Alternatively, each pair may be rotated slightly with respect to another pair of elements. In certain embodiments, each pair of radiating elements <NUM> are spaced apart axially approximately <NUM>.

Still referring to <FIG>, an epoxy housing <NUM> is shown, surrounded by an external layer of silicone <NUM>. In the embodiment shown, the ultrasonic radiating elements <NUM> are potted in the epoxy housing <NUM>. The epoxy may be flush with the outer diameter of silicone <NUM>. The epoxy housing <NUM> may have an axial length less than the length of the distal region <NUM>. In embodiments including multiple pairs of ultrasonic radiating elements <NUM>, each pair of elements may be confined to a separate epoxy housing <NUM>. In one embodiment, the epoxy housing <NUM> may have an axial length of between <NUM> and <NUM> inches. In other embodiments, the epoxy housing <NUM> may have an axial length of between <NUM> and <NUM> inches, between <NUM> and <NUM> inches, or approximately <NUM> inches.

<FIG> show two embodiments of epoxy housings <NUM> in which an ultrasonic radiating element <NUM> may be housed. Although the housing depicted is made from epoxy, any suitable material may be used. For instance, the housing may be made from rubber, polyurethane, or any polymer of suitable flexibility and stiffness. In embodiments employing epoxy, the housing may be formed by filling a polyimide sleeve with epoxy followed by curing.

In some embodiments, epoxy housings <NUM> may be embedded in the silicone layer with the assistance of chemical adhesives. In other embodiments, the housings <NUM> may additionally contain structural designs to improve the stability of the housing within the silicone. For instance, the housing <NUM> shown in <FIG> contains a notch <NUM> which, when fitted with a complementary structure of a silicone layer, may improve the stability of the housing <NUM> within the silicone layer. Such structural designs may be used in conjunction with or independently of chemical adhesives. <FIG> shows another embodiment of an epoxy housing <NUM>. In this embodiment, the raised ridge <NUM> is designed such that the top surface may lie flush with a silicone layer that surrounds the epoxy housing <NUM>. The presence of ridge <NUM>, when positioned with a complementary silicone layer structure, may help to maintain the position of the housing, and therefore of the ultrasonic radiating element, with respect to the ultrasonic catheter.

<FIG> show an ultrasonic catheter with a modified connector <NUM> that can be used in combination with the arrangements and embodiments described above. The catheter <NUM> includes flexible tubular body. Distal to the connector <NUM> is the proximal port <NUM>, which is in communication with the lumen of the tubular body <NUM>. In the embodiment shown, the proximal port <NUM> is coaxial with the lumen of the tubular body <NUM>. In use, blood from the treatment site may enter the lumen through the drainage holes <NUM> located on the distal region <NUM> of the catheter <NUM>. Blood may then flow through the lumen and exit through proximal port <NUM> into a drainage kit. In some embodiments, a negative pressure is applied to the lumen of the catheter <NUM> to facilitate movement of the blood or other liquids at the treatment site proximally along the lumen and out the proximal port <NUM>. In other embodiments, no external pressure is applied, and the blood or other liquid is permitted to flow from the treatment site to the proximal port <NUM>, unaided by external pressure. In certain instances, the treatment site will possess relatively high pressure due to intracranial hemorrhaging. In such instances, the natural pressure of the treatment site may cause blood or other liquids to flow from the treatment site proximally along the lumen, and out the proximal port <NUM>. Blood or other liquids may be drained at defined time intervals or continuously throughout the treatment. By continuously draining fluid the clot, under compression, may move towards the ultrasonic transducers for optimum ultrasound enhancement. Additionally, therapeutic agents may pass in the opposite direction. Such agents may enter the proximal port <NUM>, pass distally through the lumen, and exit the catheter <NUM> through the drainage holes <NUM>. In some embodiments, a positive pressure is applied to facilitate movement of the therapeutic agent or other liquid distally through the lumen and out the drainage holes <NUM>. In other embodiments, no external pressure is applied, and the liquid is permitted to flow independently through the lumen. Therapeutic agents may be delivered in the form of a bolus within defined time intervals or continuously throughout the treatment. In order to allow for an exit path through the proximal port <NUM>, the connector <NUM> is oriented at an angle with respect to the tubular body <NUM>. In some embodiments, the connector lies at an angle between <NUM> and <NUM> degrees. In other embodiments, the connector <NUM> lies at an angle between <NUM> and <NUM> degrees, between <NUM> and <NUM> degrees, between <NUM> and <NUM> degrees, or approximately <NUM> degrees.

As described above with respect to other embodiments, the connector <NUM> may be configured to provide electrical connections to the ultrasound radiating elements. In the embodiments shown, however, the connector <NUM> may lie at an angle with respect to the tubular body <NUM>. In certain embodiments, a wire may be soldered to a contact point on the inner portion of connector <NUM>. An electrical contact may then be exposed on the outer surface of the connector <NUM> to provide for an electrical connection to an individual wire. By virtue of this design, each wire, and therefore each thermocouple or element, may be addressed independently. In alternative embodiments, two or more wires may be soldered to a single contact, thereby creating a single electrical connection. In other embodiments, the wires may meet electrical contacts at other points within the catheter <NUM>. Alternatively, the wires may pass through the wall of the tubular body <NUM> and connect directly to external apparatuses.

The catheter <NUM> may be advanced until distal region <NUM> reaches the desired treatment site. For instance, the catheter <NUM> may be advanced through the cranial cavity until it is proximate to a blood clot. Therapeutic agents may then be delivered to the treatment site by the path described above. For instance, thrombolytic agents may be delivered to the treatment site, in order to dissolve the blood clot. In certain embodiments, ultrasonic energy may then be applied to the treatment site, as discussed above. Ultrasonic energy, alone or in combination with thrombolytic agents, may advantageously expedite dissolution of the blood clot. The ultrasonic energy may be applied continuously, periodically, sporadically, or otherwise. As the blood clot dissolves, excess blood may be drained from the treatment site through drainage holes <NUM>. Excess blood entering the drainage holes <NUM> may pass through the lumen to the proximal port <NUM> and into a drainage kit or other disposal mechanism.

A modified embodiment of an ultrasonic catheter with a proximal port is shown in <FIG>. In the embodiment shown, the proximal port <NUM> is located on the flexible tubular body <NUM> and is in communication with the lumen of the tubular body <NUM>. In this configuration, the proximal port <NUM> is perpendicular to the axis of the tubular body <NUM>, as opposed to the configuration depicted in <FIG>, in which the proximal port <NUM> is coaxial with the tubular body <NUM>. Positioning the proximal port <NUM> on the wall of the tubular body <NUM> removes the need for the connector to lie at an angle with respect to the tubular body <NUM>.

As discussed above, therapeutic agents may flow through proximal port <NUM>, distally through the lumen, and may exit the catheter <NUM> through the drainage holes <NUM> in distal region <NUM>. Additionally, blood or other liquid may flow in the opposite direction, entering the catheter through drainage holes <NUM>, flowing proximally through the lumen, and exiting the catheter <NUM> through proximal port <NUM> and into a drainage kit or other disposal means. Ultrasonic energy may also be applied periodically, continuously, sporadically, or otherwise throughout the process as desired. In certain embodiments, external pressure, negative or positive, may be applied in order to facilitate movement of liquids from the proximal port <NUM> through the lumen and out drainage holes <NUM>, or in the opposite direction. In other embodiments, liquids are permitted to flow through the lumen, unaided by external pressure.

<FIG> illustrate another arrangement for arranging the wires of an ultrasonic catheter. This arrangement can be used with the embodiments and arrangements described above. In this arrangement, a spiral groove extrusion <NUM> provides structural support to the tubular body <NUM>. In certain embodiments, the groove extrusion <NUM> may be replaced by a similar structure formed by molding or any other method. The spiral groove design can provide improved kink resistance compared to a solid structure. The spiral groove extrusion <NUM> may be formed of a variety of different materials. For example, in one arrangement, metallic ribbons can be used because of their strength-to-weight ratios, fibrous materials (both synthetic and natural). In certain embodiments, stainless steel or tungsten alloys may be used to form the spiral groove extrusion <NUM>. In certain embodiments, more malleable metals and alloys, e.g. gold, platinum, palladium, rhodium, etc. may be used. A platinum alloy with a small percentage of tungsten may be preferred due to its radiopacity. A sleeve <NUM> is arranged to slide over the spiral groove extrusion <NUM>. The material for sleeve <NUM> may be formed of almost any biocompatible material, such as polyvinyl acetate or any biocompatible plastic or metal alloy. Distal extrusion <NUM> can house ultrasonic elements as well as drainage holes <NUM>. The distal extrusion <NUM> can be formed of materials such as those described above with respect to spiral groove extrusion <NUM>. Wires <NUM> are affixed to the distal extrusion <NUM> and connected to thermocouple or ultrasound radiating elements. A distal tip <NUM> is fitted to the end of distal extrusion <NUM>.

<FIG> shows a cross-sectional view of the tubular body <NUM> taken along line N-N of <FIG>. <FIG> inch = <NUM>. Outer diameter <NUM> may be approximately <NUM> inches. In other embodiments, the outer diameter <NUM> may be approximately <NUM> inches. The inner diameter <NUM> may be approximately <NUM> inches. In other embodiments, the inner diameter may be approximately <NUM> inches. As will be apparent, the dimensions of the inner and outer diameters will be selected according to the application intended based on, e.g., the diameter of the access path through the skull, the treatment site, the volume of therapeutic agent delivered, and anticipated volume of blood to be drained.

In the embodiment shown, the distal extrusion <NUM> may contain a window <NUM> in which an ultrasound radiating element may be affixed. In other embodiments, multiple ultrasonic radiating elements, each with a corresponding window <NUM>, may be employed. As discussed above, the number, orientation, and relation of the ultrasonic radiating elements <NUM> may vary widely.

<FIG> shows a cross-sectional view of distal extrusion <NUM> taken along line M-M of <FIG>. The drainage holes <NUM> are, in the embodiment shown, longitudinal gaps in the external surface of the distal extrusion <NUM>. As can be seen in <FIG>, the distal extrusion <NUM> contains four drainage holes <NUM>, each positioned approximately <NUM> degrees apart circumferentially. In other embodiments, two or three longitudinal drainage holes may be employed. In exemplary embodiments, five or more longitudinal drainage holes may be used.

<FIG> show another embodiment of an ultrasonic catheter. As with <FIG>, a spiral groove extrusion <NUM> provides the structural support to the flexible tubular body <NUM>. Sleeve <NUM> is dimensioned to fit over the spiral extrusion <NUM>. In the embodiment shown, the distal extrusion <NUM> has been excluded. Instead, the spiral extrusion <NUM> includes at its distal end drainage holes <NUM>. Additionally, sleeve <NUM> also contains holes <NUM> designed to align with the drainage holes <NUM> of the spiral groove extrusion <NUM>. In some embodiments, the spiral extrusion <NUM> and sleeve <NUM> may be joined before drainage holes <NUM> are drilled through both layers. Wires <NUM> are connected to ultrasound radiating elements <NUM>. In the embodiment shown, the ultrasound radiating elements <NUM> and wires <NUM> are arranged to lie between the spiral extrusion <NUM> and the sleeve <NUM>. As discussed above, the wires may be arranged in various other configurations. In certain embodiments, the wires may be arranged to lie within the spiral groove.

<FIG> shows a cross-sectional view of the proximal region of the ultrasonic catheter taken along line P-P of <FIG>. The outer diameter <NUM> of the flexible tubular body <NUM> may be approximately <NUM> inches. In certain embodiments, the outer diameter <NUM> may be approximately <NUM> inches. The inner diameter <NUM> of the flexible tubular body <NUM> may be approximately <NUM> inches. In certain embodiments, the inner diameter <NUM> may be approximately <NUM> inches. As described above, the dimensions of the inner and outer diameters may vary based on the intended application. <NUM> inch = <NUM>.

As can be seen in <FIG>, in certain embodiments the spiral groove may become straight at the distal region <NUM> of the catheter. In this arrangement, the straightened region permits drainage holes <NUM> to be drilled in an arrangement of rows. Additionally, ultrasonic radiating elements <NUM> and wires <NUM> may be arranged to lie within the straight portion of the groove.

<FIG> show an ultrasonic catheter assembly according to one embodiment, in which a coaxial ultrasonic core is introduced into a separate external drain.

<FIG> illustrate one embodiment of a drain <NUM>. The distal portion <NUM> of the drain <NUM> includes drainage holes <NUM>. In a preferred embodiment, the drainage holes <NUM> may span approximately <NUM> along the distal portion <NUM>. In other embodiments, the drainage holes <NUM> may span shorter or longer distances, as desired. The drain <NUM> comprises an elongate tubular body <NUM>, and may include distance markers <NUM>. Distance markers <NUM> may be, for instance, colored stripes that surround the drain. In other embodiments, the distance markers <NUM> may be notches, grooves, radiopaque material, or any other material or structure that allows the regions to be visualized. The distance markers <NUM> may be spaced apart at regular intervals, for instance, every <NUM>, <NUM>, or other distance. In other embodiments they may be spaced in gradually increasing intervals, gradually decreasing intervals, irregularly, or in any other manner. In some embodiments, the distance between each marker will be written onto external surface of the drain. The presence of distance markers <NUM> may advantageously facilitate careful placement of the drain at a treatment site. In modified embodiments, a suture wing may be positioned at about <NUM> inches along the length of the catheter. Allowing a physician to visually observe the distance that the drain is advanced may improve control and placement precision.

The drain <NUM> includes a central lumen <NUM> which allows for the free flow of liquids from the drainage holes <NUM> towards the proximal portion <NUM> of the drain. As will be discussed in more detail below, in certain embodiments, any number of therapeutic compounds may be passed through the lumen <NUM> and out the drainage holes <NUM>, where they then enter a treatment site. The diameter of the lumen may be approximately <NUM>, with an approximate outer diameter of <NUM>. In other embodiments, these diameters may be larger or smaller, as desired. As will be apparent to one of skill in the art, the inner and outer diameters of the drain <NUM> will be chosen based on desired treatment site, fluid flow rate through the lumen, the material used to construct the drain, and the size of the ultrasonic core or any other element intended to pass therethrough. In one arrangement, the drain may operate at a flow rate of approximately <NUM> per hour, at a pressure of <NUM> mmHg. <NUM> mmHg equals <NUM> kPa.

<FIG> show one embodiment of an ultrasonic core <NUM>. The ultrasonic core <NUM> comprises an elongate shaft <NUM> and hub <NUM>. Ultrasonic elements <NUM> are positioned coaxially with the elongate shaft <NUM>. In certain embodiments, the ultrasonic core includes between one and four ultrasonic elements <NUM>. In other embodiments, five or more ultrasonic elements <NUM> may be included. The elongate shaft <NUM> is dimensioned so as to be removably received within drain <NUM>. Accordingly, in certain embodiments, the outer diameter of the elongate shaft is approximately <NUM>, and the length of the elongate shaft is approximately <NUM>.

The hub <NUM> is attached to elongate shaft <NUM> through a tapered collar <NUM>. A proximal fluid port <NUM> is in fluid communication with the hub. Fluids, such as therapeutic drugs, may be injected down the core through proximal fluid port <NUM> towards the treatment zone. Introducing fluids in this manner may permit the use of a smaller bolus of therapeutic drug as compared to introducing fluids through the drain as discussed above. Alternatively, fluids may be injected into the lumen <NUM> of drain <NUM> through use of a Tuohy-Borst adapter attached thereto. Injecting fluids through the lumen <NUM> of the drain <NUM> may require lower injection pressure, although a larger bolus of therapeutic drug may be necessary. In either configuration, the therapeutic drug ultimately flows out of drainage holes <NUM> located in the distal region <NUM> of drain <NUM>.

<FIG> illustrate the catheter assembly <NUM> in which ultrasonic core <NUM> is inserted within lumen <NUM> of drain <NUM>. In certain embodiments, the drain <NUM> may be advanced to the treatment site, followed by insertion of the ultrasonic core <NUM> within the drain. For instance, the drain may be tunneled under the scalp, through a bore in the skull, and into the brain. Then the ultrasonic core <NUM> may be inserted into the drain <NUM>, and advanced until the elongate shaft <NUM> reaches the distal region <NUM> of drain <NUM>.

Upon insertion, ultrasonic elements <NUM> may be positioned near the drainage holes <NUM>, allowing for the application of ultrasonic energy to the treatment site. As can be seen in <FIG>, the distal end of the elongate shaft <NUM> of ultrasonic core <NUM> may include one or more ultrasonic elements <NUM>. When advanced into the distal region <NUM> of drain <NUM>, the ultrasonic radiating element <NUM> would be located within the region containing drainage holes <NUM>. As discussed in more detail above, application of ultrasonic energy to a treatment site may aid in dissolution of a blood clot. Introduction of therapeutic drugs through the catheter assembly <NUM> and out drainage holes <NUM> may further aid in this process. As the clot is dissolved, excess blood or other fluid may be received within the drainage holes <NUM> and evacuated from the treatment site.

With reference now to <FIG>, in alternative embodiments two separate lumens may be included, one for fluid evacuation and one for fluid delivery. <FIG> shows a catheter In certain embodiments, continuous fluid flow may be possible. For example, application of positive pressure at the drug delivery port and simultaneous application of vacuum at the drainage port may provide for continuous removal of toxic blood components. Alternatively, influx and efflux could be accomplished separately and intermittently to allow drugs to have a working dwell time. In certain embodiments, the catheter design could spatially separate drainage holes from drug delivery holes and inlet ports, with the ultrasound transducers in between. The ultrasound radiating radially may prevent influx from going directly to efflux.

<FIG> illustrate one embodiment of an ultrasonic element and core wire. The ultrasonic core wire <NUM> comprises locking apertures <NUM> and pad <NUM>. When integrated within a completed ultrasonic core or ultrasonic catheter, the ultrasonic core wire <NUM> may be embedded in silicone. The two locking apertures <NUM> allow for silicone to flow through the opening, thereby providing for a mechanical lock that secures the element into the silicone. The locking apertures need not be circular, but may be any shape that permits silicone to flow therethrough to create a mechanical lock. Additionally, in certain embodiments there may be one locking aperture <NUM>. In other embodiments, there may be two, three, four, or more locking apertures <NUM>, as desired. Ultrasonic transducers <NUM> are affixed to either side of pad <NUM>. RF wires <NUM> are then mounted to be in communication with ultrasonic transducers <NUM>. A polyimide shell <NUM> may be formed around the assembly of the pad <NUM>, ultrasonic transducers <NUM>, and RF wires <NUM>, as shown in <FIG>. The polyimide shell may be oval-shape to aid in correct orientation of the ultrasonic element, and to minimize the use of epoxy in manufacturing.

<FIG> illustrates an ultrasonic element suspended in a fluid-filled chamber. The fluid-filled chamber <NUM> is bounded circumferentially by a polyimide shell <NUM>, with plugs <NUM> defining the ends of the fluid-filled chamber. Ultrasonic core wire <NUM> and RF wires <NUM> penetrate one of the plugs <NUM> to enter the fluid-filled chamber <NUM>. A fluid-tight seal is provided at the point of penetration to ensure that the chamber retains its fluid. Within the fluid-filled chamber <NUM> are the ultrasonic transducers <NUM> affixed to the ultrasonic core wire <NUM> and in communication with RF wires <NUM>. This design may provide for several advantages over other configurations. For instance, potting ultrasonic elements in epoxy may lead to absorption of water by the epoxy, potentially causing delamination of an ultrasonic element from the potting material. Delamination of an element reduces the ability of the ultrasonic energy to be transferred from the ultrasonic element to the surrounding tissue. Suspending an ultrasonic element within a fluid-filled chamber may advantageously avoid this problem. The ultrasonic energy emitted by the ultrasonic elements transfers easily in fluid, and there is no risk of delamination. In addition, suspending ultrasonic elements within a fluid-filled chamber may advantageously reduce the number of components needed for an ultrasonic core, as well as potentially reducing assembly time.

<FIG> schematically illustrates one embodiment of a feedback control system <NUM> that can be used with the catheter <NUM>. The feedback control system <NUM> allows the temperature at each temperature sensor <NUM> to be monitored and allows the output power of the energy source <NUM> to be adjusted accordingly. In some embodiments, each ultrasound radiating element <NUM> is associated with a temperature sensor <NUM> that monitors the temperature of the ultrasound radiating element <NUM> and allows the feedback control system <NUM> to control the power delivered to each ultrasound radiating element <NUM>. In some embodiments, the ultrasound radiating element <NUM> itself is also a temperature sensor <NUM> and can provide temperature feedback to the feedback control system <NUM>. In addition, the feedback control system <NUM> allows the pressure at each pressure sensor <NUM> to be monitored and allows the output power of the energy source <NUM> to be adjusted accordingly. A physician can, if desired, override the closed or open loop system.

In an exemplary embodiment, the feedback control system <NUM> includes an energy source <NUM>, power circuits <NUM> and a power calculation device <NUM> that is coupled to the ultrasound radiating elements <NUM> and a pump <NUM>. A temperature measurement device <NUM> is coupled to the temperature sensors <NUM> in the tubular body <NUM>. A pressure measurement device <NUM> is coupled to the pressure sensors <NUM>. A processing unit <NUM> is coupled to the power calculation device <NUM>, the power circuits <NUM> and a user interface and display <NUM>.

In an exemplary method of operation, the temperature at each temperature sensor <NUM> is determined by the temperature measurement device <NUM>. The processing unit <NUM> receives each determined temperature from the temperature measurement device <NUM>. The determined temperature can then be displayed to the user at the user interface and display <NUM>.

In an exemplary embodiment, the processing unit <NUM> includes logic for generating a temperature control signal. The temperature control signal is proportional to the difference between the measured temperature and a desired temperature. The desired temperature can be determined by the user (as set at the user interface and display <NUM>) or can be preset within the processing unit <NUM>.

In such embodiments, the temperature control signal is received by the power circuits <NUM>. The power circuits <NUM> are configured to adjust the power level, voltage, phase and/or current of the electrical energy supplied to the ultrasound radiating elements <NUM> from the energy source <NUM>. For example, when the temperature control signal is above a particular level, the power supplied to a particular group of ultrasound radiating elements <NUM> is reduced in response to that temperature control signal. Similarly, when the temperature control signal is below a particular level, the power supplied to a particular group of ultrasound radiating elements <NUM> is increased in response to that temperature control signal. After each power adjustment, the processing unit <NUM> monitors the temperature sensors <NUM> and produces another temperature control signal which is received by the power circuits <NUM>.

In an exemplary method of operation, the pressure at each pressure sensor <NUM> is determined by the pressure measurement device <NUM>. The processing unit <NUM> receives each determined pressure from the pressure measurement device <NUM>. The determined pressure can then be displayed to the user at the user interface and display <NUM>.

In an exemplary embodiment, the processing unit <NUM> includes logic for generating a pressure control signal. The pressure control signal is proportional to the difference between the measured pressure and a desired pressure. The desired pressure can be determined by the user (as set at the user interface and display <NUM>) or can be preset within the processing unit <NUM>.

As noted above, it is generally desirable to provide low negative pressure to the lumen in order to reduce the risk of sucking solid material, such as brain matter, into the lumen. Furthermore, because reduction of intracranial pressure is often desirable in treating ICH, it is often desirable to deliver fluids with little pressure differential between the delivery pressure and the intracranial pressure around the catheter. Accordingly, the processing unit <NUM> can be configured to monitor the pressure and modify or cease the delivery of fluid and/or increase evacuation of fluid to the treatment site if intracranial pressure increases beyond a specified limit.

In other embodiments, the pressure control signal is received by the power circuits <NUM>. The power circuits <NUM> are configured to adjust the power level, voltage, phase and/or current of the electrical energy supplied to the pump <NUM> from the energy source <NUM>. For example, when the pressure control signal is above a particular level, the power supplied to a particular pump <NUM> is reduced in response to that pressure control signal. Similarly, when the pressure control signal is below a particular level, the power supplied to a particular pump <NUM> is increased in response to that pressure control signal. After each power adjustment, the processing unit <NUM> monitors the pressure sensors <NUM> and produces another pressure control signal which is received by the power circuits <NUM>.

In an exemplary embodiment, the processing unit <NUM> optionally includes safety control logic. The safety control logic detects when the temperature at a temperature sensor <NUM> and/or the pressure at a pressure sensor <NUM> exceeds a safety threshold. In this case, the processing unit <NUM> can be configured to provide a temperature control signal and/or pressure control signal which causes the power circuits <NUM> to stop the delivery of energy from the energy source <NUM> to that particular group of ultrasound radiating elements <NUM> and/or that particular pump <NUM>.

Consequently, each group of ultrasound radiating elements <NUM> can be identically adjusted in certain embodiments. For example, in a modified embodiment, the power, voltage, phase, and/or current supplied to each group of ultrasound radiating elements <NUM> is adjusted in response to the temperature sensor <NUM> which indicates the highest temperature. Making voltage, phase and/or current adjustments in response to the temperature sensed by the temperature sensor <NUM> indicating the highest temperature can reduce overheating of the treatment site.

The processing unit <NUM> can also be configured to receive a power signal from the power calculation device <NUM>. The power signal can be used to determine the power being received by each group of ultrasound radiating elements <NUM> and/or pump <NUM>. The determined power can then be displayed to the user on the user interface and display <NUM>.

As described above, the feedback control system <NUM> can be configured to maintain tissue adjacent to the energy delivery section <NUM> below a desired temperature. For example, in certain applications, tissue at the treatment site is to have a temperature increase of less than or equal to approximately <NUM> degrees C. As described above, the ultrasound radiating elements <NUM> can be electrically connected such that each group of ultrasound radiating elements <NUM> generates an independent output. In certain embodiments, the output from the power circuit maintains a selected energy for each group of ultrasound radiating elements <NUM> for a selected length of time.

The processing unit <NUM> can comprise a digital or analog controller, such as a computer with software. In embodiments wherein the processing unit <NUM> is a computer, the computer can include a central processing unit ("CPU") coupled through a system bus. In such embodiments, the user interface and display <NUM> can include a mouse, a keyboard, a disk drive, a display monitor, a nonvolatile memory system, and/or other computer components. In an exemplary embodiment, program memory and/or data memory is also coupled to the bus.

In another embodiment, in lieu of the series of power adjustments described above, a profile of the power to be delivered to each group of ultrasound radiating elements <NUM> can be incorporated into the processing unit <NUM>, such that a preset amount of ultrasonic energy to be delivered is pre-profiled. In such embodiments, the power delivered to each group of ultrasound radiating elements <NUM> is provided according to the preset profiles.

In an exemplary embodiment, the ultrasound radiating elements are operated in a pulsed mode. For example, in one embodiment, the time average power supplied to the ultrasound radiating elements is between about <NUM> watts and about <NUM> watts. In another embodiment, the time average power supplied to the ultrasound radiating elements is between about <NUM> watts and about <NUM> watts. In yet another embodiment, the time average power supplied to the ultrasound radiating elements is approximately <NUM> watts or approximately <NUM> watts. In an exemplary embodiment, the duty cycle is between about <NUM>% and about <NUM>%. In another embodiment, the duty cycle is between about <NUM>% and about <NUM>%. In yet another embodiment, the duty cycles is approximately <NUM>% or approximately <NUM>%. In an exemplary embodiment, the pulse averaged power is between about <NUM> watts and about <NUM> watts. In another embodiment, the pulse averaged power is between approximately <NUM> watts and approximately <NUM> watts. In yet another embodiment, the pulse averaged power is approximately <NUM> watts or approximately <NUM> watts. The amplitude during each pulse can be constant or varied.

In an exemplary embodiment, the pulse repetition rate is between about <NUM> and about <NUM>. In another embodiment, the pulse repetition rate is between about <NUM> and about <NUM>. In yet another embodiment, the pulse repetition rate is approximately <NUM>. In an exemplary embodiment, the pulse duration is between about <NUM> millisecond and about <NUM> milliseconds. In another embodiment, the pulse duration is between about <NUM> millisecond and about <NUM> milliseconds. In yet another embodiment, the pulse duration is approximately <NUM> milliseconds or approximately <NUM> milliseconds.

For example, in one particular embodiment, the ultrasound radiating elements are operated at an average power of approximately <NUM> watts, a duty cycle of approximately <NUM>%, a pulse repetition rate of approximately <NUM>, a pulse average electrical power of approximately <NUM> watts and a pulse duration of approximately <NUM> milliseconds.

In an exemplary embodiment, the ultrasound radiating element used with the electrical parameters described herein has an acoustic efficiency greater than approximately <NUM>%. In another embodiment, the ultrasound radiating element used with the electrical parameters described herein has an acoustic efficiency greater than approximately <NUM>%. As described herein, the ultrasound radiating elements can be formed in a variety of shapes, such as, cylindrical (solid or hollow), flat, bar, triangular, and the like. In an exemplary embodiment, the length of the ultrasound radiating element is between about <NUM> and about <NUM>, and the thickness or diameter of the ultrasound radiating element is between about <NUM> and about <NUM>.

With reference now to <FIG>, in one embodiment of a treatment protocol, patients can be taken to an operating room and placed under general anesthesia for ultrasound and drainage catheter insertion. Patients can be registered using electromagnetic (EM) stealth, based on CT parameters for stereotactic placement of catheters using the Medtronic EM Stealth navigation system. However, as described above, in modified embodiments, other navigation techniques and tools could be used. Using such navigation systems, an entry point for the burr hole and target point in the hemorrhage for the catheter tips can be chosen. In some embodiments, the burr-hole can be located for an occipital approach if the patient has an intraventricular hemorrhage. In some embodiments, the burr-hole can be located for a more frontal approach if the patient has an intracerebral hemorrhage located in the frontal portion of the brain. It should be appreciated that the location of the burr-hole or drill hole can be selected to reduce the path length between the blood clot and the hole in the patient's skull. In addition, it may be desirable in some cases to approach the blood clot from an angle that avoids certain portions of the brain.

In the illustrated embodiment, a Stealth guidance system (or other guidance system or technique) can used to place a <NUM> French peel-away introducer through the burr hole into the desired location in the hemorrhage, to accommodate placement of the ultrasonic catheter <NUM>. In modified arrangements, a different size and/or type of introducer could be used and/or the ultrasonic catheter can be inserted without an introducer.

As shown in <FIG>, the catheter <NUM> can be with the peel away introducer and the position confirmed by neuro-navigation or other navigation technique. In one embodiment, the two catheters can then be tunneled out through a separate stab wound in the skin and secured to the patient. A portable CT scan can be done at the completion of the procedure to confirm acceptable catheter placement. In one embodiment, the distal tip of the ultrasonic catheter <NUM> is generally positioned long the longitudinal center (measured along the axis of the catheter) of the hemorrhage. As described above, in other embodiments, an ultrasonic core can be place through a lumen in the catheter (see e.g., <FIG>). In other embodiments, the ultrasonic catheter can be placed along side the catheter.

In one embodiment of use, patients with ICH or IVH can be treated after the CT scans to confirm no active bleeding and expansion of the hematoma. In one embodiment, such scans can be obtained approximately <NUM> hours after catheter placement but before treatment had begun with ultrasound and thrombolytic. In some embodiments, the treatment may include injecting a thrombolytic drug into the hemorrhage through the catheter. The catheter is then flushed and clamped for about <NUM> hour with the drainage close and then opened to closed drainage at <NUM> below the lesion thus allowing the full dose of the thrombolytic drug to be delivered into the clot. In one embodiment of use, patients with intraventricular hemorrhages, <NUM> of rt-PA can be injected and <NUM> rt-PA can be injected in patients with intraparenchymal hemorrhages.

In one embodiment of use, following about <NUM> hour of drug treatment, the closed drainage can be opened below the lesion. The injections can be repeated about every <NUM> hours (e.g., at about <NUM> hours and about <NUM> hours from the time of the initial injection) for a total of <NUM> doses over a period of about <NUM> hours. Computer Tomography (CT) imaging can be performed at appropriate time during the treatment to determined rate of lysis and to monitor the progress of clot lysis. The drainage may also be evaluated by performing a CT. The ultrasound remains operating all the time during the treatment, and may be turned off only during the CT imaging for the least possible length of time. Thus, in some embodiments, the ultrasound may be turned on at the time of the initial injection and delivered continuously at the catheter tip for up to about <NUM> hours.

Ultrasound energy can be delivered for a duration sufficient to enable adequate drug distribution in and/or around the blood clot. This can be accomplished by either intermittent or continuous delivery of ultrasound energy. For example, ultrasound energy can be delivered for a set time period to adequately distribute the drug to the blood clot, and then turned off to allow the drug to act on the blood clot. Alternatively, ultrasound energy can be delivered substantially continuously after the drug has been delivered to the blood clot to continuously redistribute the drug into the blood clot as the blood clot is successfully lysed. In addition, ultrasound energy can be delivered intermittently to reduce heating. Also, as described in <CIT>, the power parameters controlling the delivery of ultrasound energy can be randomized or varied according to complex non-linear algorithms in order to enhance the efficacy of the ultrasound treatment.

Drug delivery can be controlled by monitoring, for example, lysis byproducts such as D-dimer in the effluent evacuated from the blood clot. A high and/or increasing concentration of D-dimer in the effluent can indicate that lysis of the blood clot is proceeding adequately, and therefore drug delivery can be maintained, reduced or stopped. A low or decreasing concentration of D-dimer in the effluent can indicate that lysis of the blood clot is inadequate or slowing or that the clot is nearly dissolved, and therefore drug delivery can be increased if the clot is not nearly dissolved, and reduced or stopped if lysis is almost complete. Alternatively, lytic concentration can be monitored to determine whether more drug should be delivered and whether lysis is complete. In some embodiments, as lysis of the blood clot proceeds, lytic is freed from the lysed clot, thereby increasing the concentration of lytic in the effluent. Therefore, increased lytic concentration can correlate to lysis completion. One way of determining the concentration of lytic and/or D-dimer in the effluent is to measure the color of the effluent that is evacuated from the blood clot. The redder the effluent, the greater the concentration of lytic and/or D-dimer in the effluent.

In some embodiments, neuroprotective drugs or agents that assist in the functional recovery and/or the reduction of cell and tissue damage in the brain can also be delivered to the brain and blood clot with the methods and apparatus described above. These neuroprotective drugs or agents can be delivered before, with, or after the delivery of the thrombolytic drugs. Delivery of these drugs using the methods and apparatus described above is particularly useful where the drug delivery through the blood brain barrier is enhanced with ultrasound treatment, or where ultrasound enhances cell penetration by the drug, or where the drug is sonodynamic.

Another embodiment of an ultrasonic catheter is shown in <FIG>. Similar to the embodiments described above with respect to <FIG>, the catheter includes wires <NUM> embedded within the wall of the tubular body <NUM>. The wires <NUM> are connected to and may control ultrasonic radiating elements <NUM> located within the distal region <NUM> of the catheter <NUM>. The wires extend from the proximal end of the tubular body <NUM>. In certain embodiments, the wires extend more than fifteen centimeters (six inches) from the proximal end, so as to facilitate electrical connection with external devices. Drainage holes <NUM> are positioned in the distal region <NUM> of the catheter <NUM>, near the ultrasonic radiating elements <NUM>. In other embodiments, thermocouples, pressure sensors, or other elements may also be disposed within the distal region <NUM>. The distal region <NUM> may be composed of silicone or other suitable material, designed with drainage holes <NUM> as discussed above. Ultrasonic radiating elements <NUM> may be embedded within the wall of the distal region <NUM>, surrounded by the silicone or other material. In various embodiments, there may be as few as one and as many as <NUM> ultrasonic radiating elements <NUM> can be embedded with the distal region <NUM> of the device. The elements <NUM> can be equally spaced in the treatment zone. In other embodiments, the elements <NUM> can be grouped such that the spacing is not uniform between them. In an exemplary embodiment illustrated in <FIG>, the catheter <NUM> includes four ultrasonic radiating elements <NUM>. In this four-element configuration, the elements can be spaced apart as pairs, with each pair located at a similar longitudinal position, but separated by <NUM> degrees circumferentially. The pairs of offset from one another both by <NUM> degrees circumferentially and by a longitudinal distance along the length of the catheter <NUM>. As will be apparent to the skilled artisan, various other combinations of ultrasonic radiating elements are possible.

While the foregoing detailed description has set forth several exemplary embodiments of the apparatus of the present invention, it should be understood that the above description is illustrative only and is not limiting of the disclosed invention. It will be appreciated that the specific dimensions and configurations disclosed can differ from those described above, and that the methods described can be used within any biological conduit within the body.

Claim 1:
An ultrasound catheter (<NUM>) comprising:
an elongate tubular body (<NUM>) having a distal portion (<NUM>) and a proximal portion (<NUM>), the elongate tubular body (<NUM>) having material properties similar to that of standard external ventricular drainage (EVD) catheter;
a drainage lumen (<NUM>) formed within the elongate tubular body (<NUM>), wherein the drainage lumen (<NUM>) includes a plurality of drainage ports (<NUM>) on the distal portion (<NUM>) of the elongate tubular body (<NUM>) configured to allow fluid to flow therethrough;
a delivery lumen (<NUM>) formed within the elongate tubular body (<NUM>), wherein the delivery lumen includes a plurality of delivery ports (<NUM>) on the distal portion (<NUM>) of the elongate tubular body (<NUM>) configured to allow fluid to flow therethrough; and
a plurality of ultrasound radiating elements (<NUM>) positioned within the elongate tubular body (<NUM>).