Hyaluronic acid and its use for treating venous insufficiency and varicose veins

Abstract

The present invention relates to an injectable aqueous viscous solution for treating varicose veins. It also relates to a catheter system with cannulas for vascular puncture with double or triple cut tip comprising, (i) an outer cannula (non-cutting element), a tube-like construction which is slightly flexible, (a) the tip zone being tapered to ease introduction, (b) the edges being optionally rounded to provide atraumatic advancement (c) optionally with a Luer-lock connector (ii) a hollow needle which is flexible and bendable (c) optionally with a transparent flashback chamber, wherein (d) the diameter of the needle is below the diameter of the catheter, wherein (iii) the needle and outer cannula are connected by a temporary lock to ensure the needle tip is fixed in adequate position outside the outer cannula outer cannula during skin puncture and introduction towards the target region.

Claims

1. A method for treating venous diseases characterized by dilated veins in a subject in need thereof comprising administering a composition comprising an injectable viscous aqueous solution, wherein the composition comprises about 0.1% to 3% cross-linked hyaluronic acid with a half-life within human connective tissue of more than 1 week, wherein said injectable viscous aqueous solution has a viscosity from 10 to 5000 mPa*s, and wherein said composition is administered perivascularly.

2. The method of claim 1, wherein the composition further comprises one or more of the following compounds: poly lactic acid and alginate.

3. The method of claim 1, wherein the composition is cross-linked with 1,4-butanediol diglycidyl ether (BDDE).

4. The method of claim 1, wherein the concentration of hyaluronic acid is about 0.25% to about 2%.

5. The method of claim 1, wherein the hyaluronic acid is between 1 million and 8 million Da.

6. The method of claim 2, additionally comprising a local anesthetic.

7. The method of claim 6, wherein the local anesthetic is selected from the group consisting of scandicain, mepivacaine, cocaine, procaine, benzocaine (ethoform), lidocaine, mepivacain, bupivacaine, ropivacain, etidocain, prilocain and tetracain.

8. The method of claim 1, wherein the venous disease is selected from the group consisting of aneurysm, varicose veins, insufficient veins, dilated veins and ectasias.

9. The method according to claim 1, wherein the treatment with the composition is for shaping of dilated, incompetent valve sections by reducing the diameter.

10. The method according to claim 1, wherein the composition comprises about 0.5% to 1% cross-linked hyaluronic acid.

Description

DETAILED DESCRIPTION OF THE INVENTION

(1) The invention relates to an aqueous injectable viscous solution, for example in the form of a fluid, gel or hydrogel. The viscous solution preferably has a half-life within human connective tissue more than 1 week. The person skilled in the art will appreciate that the half-life will depend on the whether the solution is to be used in an independent therapy or as an accompanying therapy. Hence, in some cases, the half-life is preferably greater than 1 month, more preferably, greater than 3 month, most preferably greater than 6 months or even 12 months. In other cases, the half-life is between 1 week and 3 years, preferably between 1 and 12 weeks, more preferably between 4 and 6 weeks.

(2) The term “viscous” herein denotes a solution which can be conveniently injected through the herein described catheter into tissue but still has a certain toughness such that the composition is retained in the tissue for a long time. Preferred viscosities η range from 10 to 5000 mPa*s, preferably 20 to 5000 mPa*s, more preferably 30 to 2000 mPa*s. In another aspect, the viscosity ranges between 20 and 1000 mPa*s, between 50 and 2000 mPa*s or between 50 and 1000 mPa*s. Since the viscosity is temperature dependent, injectability should be given at working temperature, e.g. between 20° C. and 40° C.

(3) The density of the solution is preferably similar to the density of the tissue to be treated. In most cases, the tissue will be body fat. Hence, it is preferred that the density is between 0.7 and 1.2 kg/l, more preferably between 0.0 and 1.1 kg/l, most preferably between 0.9 and 1.0 kg/l or about 0.94 kg/l.

(4) A gel is a solid, jelly-like material that can have properties ranging from soft and weak to hard and tough. Gels are defined as a substantially dilute cross-linked system, which exhibits no flow when in the steady-state. By weight, gels are mostly liquid, yet they behave like solids due to a three-dimensional cross-linked network within the liquid. It is the crosslinks within the fluid that give a gel its structure (hardness) and contribute to stickiness (tack).

(5) Hydrogel is a network of polymer chains that are hydrophilic, sometimes found as a colloidal gel in which water is the dispersion medium. Hydrogels are highly absorbent (they can contain over 99.9% water) natural or synthetic polymers. Hydrogels also possess a degree of flexibility very similar to natural tissue, due to their significant water content.

(6) The solution preferably comprises one or more of the following compounds: poly lactic acid, alginate, hyaluronic acid, particularly the hyaluronic acid as disclosed herein, and body fat. Poly lactic acid, for example, has been used in cosmetic treatment of wrinkles and shown to exhibit a longer residence within the human skin than cross-linked hyaluronic acid. Body fat, for the present purpose, is crushed and filtered, or the like, so that it can be injected through thin cannula (see catheter dimensions below).

(7) In a specific embodiment, the invention relates to an aqueous solution comprising between 0.1% and 3% hyaluronic acid, preferably between 0.25% and 2% hyaluronic acid, even more preferably between 0.5 and 1% hyaluronic acid preferably crosslinked with 1,4-butanediol diglycidyl ether (BDDE). The percent herein characterizes mass concentration, i.e. for example gram per liter.

(8) In order to achieve a life-time as defined above or modulate the life-time, there are different methods known. For example, the solution may be combined with 2-(diethyl amino)ethyl dextrane (also known as Sephadex DEAE A25), hypromellose (hydroxypropyl methylcellulose, HPMC). Alternatively, the compound(s) in the solution may be cross-linked. The thus derived solution are preferably biocompatible and do not evoke long-term irritations or inflammations. The skilled person will appreciate that the half-life of such solution are greater than that of the solution without said modifications because degrading enzymes, such as hyaloronidases, are thereby retained from the cleavage sites within the molecules. Comparable stable properties have so-called hyper-twisted, stabilized hyaluronic acids.

(9) In one embodiment the solution further comprises inhibiting agents. Inhibiting agents herein means agents that are capable of inhibiting the degradation of one or more compounds in the viscous solution. For example, agents which have a poly saccharide-like structure inhibit the degradation of hyaluronic acid, e.g. heparin, herbal pectines and alginic acids, all of which show gel-like properties in solution. A herbal pectine may be an apple pectin. In some cases, the ability to penetrate tissue is too weak. In this case, saponins, such as glycyrrhizic acid and glycyrrhetinic acid (aglycone), which are both contained in liquorice extract, and aescin (from horse chestnut seed extract) are more effective. This applies also for flavonoids.

(10) Further, the solution, either in addition to or instead of an inhibiting agent, may further comprise one or more endogenous substances. In one embodiment said substance is capable of forming cross-linkages with the compound in the solution. For example, a mixture of hyaluronic acid and an endogenous substance forms cross-linkages. Such endogenous substance is preferably a substance that leads to a fibrin clot. Artificial hematomas from autologous blood may be used as such substance. However, it is preferred to use autologous blood or fractions of autologous blood (platelets, coagulation factors and/or the like). In some cases, it is convenient to use blood without erythrocytes to avoid discoloration. Particularly, for the goal of long-term venous formations (treatment of valve insufficiency) this is a cost-effective solution.

(11) Venous insufficiency, varicose veins and other disease related to vein dilatation are nowadays preferably treated by non-surgical catheter-based occlusion methods like radiofrequency, laser, steam, sclerosant foam, or glue. Except glue, none of these methods is able to initially occlude the target vessel with the necessary diameter reduction. Glue seals the vessel by wall-to-wall contact, but in all other methods the required shrinkage will take several weeks to months. Blood will re-enter the target vein in spite of external compression mediated by bandages, stockings or locally applied compressing bodies. The more blood is contained in the vessel, the longer takes the resorption process, and the higher is the risk that the resorption will go along with inflammation and pain.

(12) With thermo occlusion methods usually tumescent anaesthesia is applied. Tumescence means to dissolve the local tissue compound. The method has been established for liposuction, and is performed by distributing large amounts of saline with local anaesthetic and optional supplements like bicarbonate, epinephrin or corticoids added, by injection manually or with pumps in the fatty tissue. The purpose is to separate fat cells from their compound and from connective tissue to support the following suction process (Klein, J. (2000). Tumescent Technique: Tumescent Anesthesia & Microcanullar Liposuction. St. Louis, Mo.: Mosby, Inc, 2000).

(13) Applying tumescent anaesthesia on endovenous methods means to inject larger amounts of solution (USA: 400-600 ml for 40 cm vein segment) into the connective tissue adjacent to the target vein. This helps to decrease the vein lumen during treatment, contributing to a more homogenous energy deployment, but will vanish within hours. Solutions of HAES or other larger molecules have not been sufficient, vanishing within a few days. If vein compression by fluid or gel is aimed at, it should be strictly around the target vessel, but not diffuse in a large space infiltrating all kinds of surrounding tissues. In fact, due to the large amounts of fluids, tumescent anaesthesia itself is often painful for the patient.

(14) The present desirable compression is achieved by an agent (solution) which is injectable like a fluid, but it does not propagate into the connective tissue. This means, there is a trade-off between easy injectability (low exertion) and the tendency to propagate into connective tissue, thereby decreasing the life-time of the solution. It is preferred that the solution can be injected with a force less than 50 N. In a specific embodiment said force is 7.5 to 15 N (normal exertion), in another embodiment 15 to 50 N (high exertion). It turns out to be well visible in ultrasound imaging with a distinct signal. The half-life at the inventive concentration of hyaluronic acid is 2-8 weeks for each treatment. After 8 weeks no remainders are palpable or visible.

(15) The inventor has astonishingly found that a special aqueous solution of hyaloronan may be used very efficiently in order to treat venous diseases. Hence, in the following the invention is detailed for hyaluronic acid. However, the disclosure applies generally to any solution as disclosed herein.

(16) The inventors have found that different to tumescent anaesthesia, the hyaluronan solution does not diffusely infiltrate the connective tissue. The hyaluronan solution was, in patients, exactly placeable around the target vein, and sufficient vein compression could be established with very small amounts of about 1-2 ml per centimeter (40-80 ml for a 40 cm vein segment). The same is true for the viscous solution disclosed herein.

(17) In laser treatments (wavelength: 810 nm, energy: 100 J/cm) of insufficient saphenous veins (diameter 6.2-10.8 mm; 8 cases), regression times from pre-treatment to a target diameter of 25% could be reduced from 33-98 days with tumescent anaesthesia to immediate when using a solution according to the invention.

(18) In another ongoing pilot study, two vein aneurysms of 18 and 25 mm were normalized in diameter to 6 and 7.5 mm using 3 ml of a solution or composition according to the invention, and remained with this reduced diameter during the follow-up of 90 days.

(19) Preferably for use in occlusive vein treatments the solution of hyaluronan has a half life at the site of injection of between 2 and 8 weeks. Hence, another way of characterizing the hyaluronic acid in the aqueous solution is by way of its half life (see also above).

(20) The invention can also be used for a shaping of dilated, incompetent valve sections by reducing the diameter. The effect can be immediately monitored in a color-coded doppler ultrasound imaging. If a diseased vein valve is restored in the sense that backward blood flow is stopped and an onward flow established, the formerly affected vein may relax and shrink due to reduced blood load. Therefore, normal vein function may be re-established by shaping diseased valve zones. The principle has been proven in a surgical method called extraluminal valvuloplasty by implanting a perivenous cuff (B. Geier, I. Voigt, L. Barbera, B. Marpe, M. Stacker, S. El Gammal, A. Mumme: Extraluminal Valvuloplasty in Insufficiency of V. saphena magna; Phlebologie 2004, Vol. 33:5; 145-185).

(21) The advantages of the solution or composition for the treatment outlined above are multiple: The solution is not immunogenic, biocompatible, of non-animal origin, binds water very well and body resorption is very good.

(22) Hyaluronan (also called hyaluronic acid or hyaluronate) is an anionic, nonsulfated glycosaminoglycan distributed widely throughout connective, epithelial, and neural tissues. It is unique among glycosaminoglycans in that it is nonsulfated, forms in the plasma membrane instead of the Golgi, and can be very large, with its molecular weight often reaching the millions.

(23) Hyaluronan is a polymer of disaccharides, themselves composed of D-glucuronic acid and DN-acetylglucosamine, linked via alternating β-1,4 and β-1,3 glycosidic bonds; see FIG. 1. Hyaluronan can be 25,000 disaccharide repeats in length. Polymers of hyaluronan can range in size from 5,000 to 20,000,000 Da in vivo. The average molecular weight in human synovial fluid is 3-4 million Da, and hyaluronan purified from human umbilical cord is 3,140,000 Da.

(24) It is preferred that the hyaluronic acid has between 1 million and 8 million Da, more preferably between 2 and 6 Mio. Da, more preferably between 3 and 5 Mio Da. About 4 million Da is most preferred (+/−20%).

(25) The hyaluronan is obtained by bacterial fermentation, passing sterile filtration and optional heat treatment. Additionally, potential endotoxins may be extracted. Thermal sterilization may reduce the length of molecular chains.

(26) Hyaluronan is energetically stable, in part because of the stereochemistry of its component disaccharides. Bulky groups on each sugar molecule are in sterically favored positions, whereas the smaller hydrogens assume the less-favorable axial positions.

(27) One preferred solution is obtained by crosslinking Hyaluronic Acid (HA) with 1,4-Butanediol Diglycidyl Ether (BDDE). Such a solution passes all the biocompatibility tests. BDDE is a sensitizer and has also found to be a mutagen in Drosophila (Foureman et al, Environ Mol Mutagen 1994; 23(1):51-63). To address the carcinogenicity potential of the residual BDDE (2 ppm) present in the device, one can cite an animal study conducted on BDDE by CIBA-GEIGY. The animal study investigators felt the study was not conclusive to say BDDE is a systemic carcinogen. Therefore, BDDE is considered to be today's least toxic cross-linking agent.

(28) In certain embodiments the solution may additionally comprise a local anesthetic. These may be scandicain, mepivacaine, cocain, procain, benzocain (Ethoform), lidocain, mepivacain, bupivacain, ropivacain, etidocain, prilocain and tetracain but also others. Corticoids may be used to prevent perivascular inflammations. Further substances may be added to delay or accelerate the resorption of HA or the compounds in the composition.

(29) The signal intensity of the substance can be varied from equal to water to more intense than human tissue, by adding small amounts of gas (Carbondioxid, Oxygen, air, or mixtures thereof), e.g. 1-10 vol.-%, and prepare an injectable mixture. In contrary to water-like fluids, gas bubbles will be stable for minutes to hours in hyaluronan due to its gel-like viscosity.

(30) Normally, the desired ultrasound signal will be equal to water, as this allows the best view on the vein and the endoluminal tools, but in some indications (e.g. aneurysm) it may be preferred to use an ultrasound pattern much different from water to easier differentiate aneurysm and compressing substance.

(31) The preferred pH of the solution is 7.2+/−0.1.

(32) The solution may additionally comprise CO.sub.2, O.sub.2, air or mixtures thereof, in amounts of 1-10%.

(33) The invention also relates to the inventive solution for use as a medicament.

(34) Preferably the solution is used for treating dilatative or ectatic venous diseases. Hence, the invention also relates to a method of treating a patient which has venous disease. The venous disease is preferably characterized by dilated veins.

(35) Preferably, the venous disease is select from the group of venous insufficiency, dilated veins, varicose veins, ectasias or aneurysm.

(36) The amount of solution, e.g. hyaluronan solution, for one patient may have a volume of between 3 ml (e.g. small aneurysms) and 200 ml (e.g. long ectatic veins).

(37) The invention also relates to a kit comprising a solution according to the features outlined above and one of the following: a hollow needle, a catheter and/or a tube. Preferably, the catheter is a catheter system as described below.

(38) A catheter system herein is a medical device that can be inserted in the body to treat diseases, particular vein diseases. The catheter system according to the invention comprises a needle for vascular puncture with double or triple cut tip which suit the purpose of easy skin puncture and an outer cannula. The outer cannula may be most appropriately called a catheter, though catheters are usually made of rubber. In order to provide the present catheter system the material of known catheters would be in most cases too weak. Hence, the herein disclosed catheter system and the catheter (outer cannula) differs from the known ones in that they are characterized as disclosed herein. Catheters or tubes near to the required kind are known from biopsy, where they serve as outer part (non-cutting element). Needles for tumescent anesthesia in liposuction are either sharp cannulas, or tube-like tools with multiple side-holes for rapid tissue infiltration.

(39) The catheter system according to the invention differs largely from all existing coaxial catheter or needle systems, as there so far has been no construction for the invention's purpose, i.e. to safely deploy viscous solutions around vascular structures.

(40) Straight coaxial systems for intravascular use are widely spread and used for infusions, transfusions or to take blood samples. They consist of a hollow needle with a sharp tip penetrating tissue layers, and a second, outer tube of plastic material which remains within the vessel after the inner needle has been removed. Such plastic tubes are far too soft and vulnerable to kinkings as to use them as a steerable blunt cannula for the deployment of gels or fluids outside of vessels.

(41) Coaxial tube systems used for biopsy usually contain an inner element which is solid to replace tissue material and leaving it for the outer tube to aspirate a sample. The purpose is to cut and collect tissue samples. There are few coaxial biopsy needle systems consisting of two sharp hollow structures. There is no biopsy system containing one blunt and one sharp, unfenenstrated tubes.

(42) There are coaxial systems for lumbar anesthesia, but they are not straight to fit to the given anatomy. Furthermore, they are stiff to pass the resistant connective perilumbar tissue.

(43) Cannulas for liposuction are made of metal with minimal flexibility, but are just a single tube instrument, normally with a closed end, a rounded tip and a side window near the tip for the collection of fat cells.

(44) Finally, there are some constructions called “safety cannula” which consist of a cannula with a sharp tip for puncturing, and a device to cover this sharp tip when the cannula is withdrawn to avoid injuries. Other constructions allow the introduction and pull-back of hollow needles into a catheter, an endoscope or other tools. However, this does not refer to highly flexible coaxial injection tubes.

(45) In contrast to the above the catheter disclosed herein comprises two coaxial straight tubes (cannulas), open at both sides, the first tube with a sharp tip, i.e. a needle, and the second tube with a blunt tip, i.e. outer part, herein also denoted outer cannula (non-cutting element). Both tubes are flexible and/or elastic. The tubes are composed at a distance allowing easy relocation but preferably no manually perceptible play when steering the tip by moving the handle. The system of both tubes is designed for advancing it to positions outside diseased vessels, to deploy viscous compositions around the vascular structures for shaping them or reducing their diameter for a time period from weeks to months (see above).

(46) The needle is positioned within the cannula having a blunt tip. Accordingly, the needle has a smaller outer diameter than the inner diameter of the outer cannula. The needle may be supplemented by a transparent aspiration chamber to monitor incidental intravascular positions or hematoma after vascular injuries.

(47) It is preferred that a connector element allows withdrawal of the needle into an injection position for the safe extravascular deployment of viscous compositions, and/or movement of the needle into a puncturing position in order to penetrate skin and connective tissue layers until the target position has been reached. Preferably, the cannulas can be fixed in predetermined positions relative to each other in one or both of said positions.

(48) The puncturing position may be characterized in that the tip of the needle is 2 to 8 mm ahead of the outer cannula. The injection position may be characterized in that the tip of the needle is positioned within the outer cannula. For example, the needle may be withdrawn by some mm such that the needle is located and fixed 4 to 6 mm before the opening of the outer cannula.

(49) Herein, sharp means that the cannula is able to penetrate skin and connective tissue, for example the force applied is less than 5, preferably less than 3 or even less than 1.5 N. Blunt means that the cannula cannot penetrate skin or connective tissue, for example when the force applied is less than 3, preferably less than 4 or even less than 5N. The person skilled in the art will appreciate that the above values depend on the outer diameter of the cannula and, thus, relate to cannulas with an outer diameter of about 0.8 to 1.2 mm. More specific, for cannulas with an outer diameter of 0.8 mm and 1.2 mm, the values for a sharp cannula may be less than about 1.5 N and less than about 2.0 N, respectively. The values for a blunt cannula may be less than about 3 N and less than about 4 N, respectively.

(50) The needle and/or outer cannula are flexible and elastic in a way such that the catheter can both penetrate the skin at an angle of 10 to 90 degrees, preferably 20 to 45 degrees, relative to the skin surface and can be steered parallel to the vessel, which is parallel to the skin surface in most of the cases. In certain embodiments, this may mean that the coaxial tubes bent for 5 to 90 degrees, preferably 5 to 50 degrees, more preferably 5 to 30 degrees or more than 10 degrees when a bending force less than 1N is applied. In other embodiments, the cannula will bend for 10 to 40 mm, preferably 10 to 30 mm or 15 to 25 mm (measured at the tip), when the tip is stressed with a force of 0.2 N. The definition may apply to the needle and/or the outer cannula and/or to the catheter system, i.e. when both cannulas are assembled.

(51) “Elastic” means that the tube returns to the original, straight shape, when stressing the tip of a 100 mm long cannula with a force of 0.2 N (20 g). These properties are rarely reached by some small injection needles, but not by any existing coaxial needle system.

(52) For easy and pain-free introduction and positioning the catheter system is preferably as small as possible and does not exceed a maximum outer diameter (OD) of 3.0 mm, preferably 2.0 mm, more preferably 1.5 mm. However, for easy deployment of viscous fluids or gels, it is preferred that the inner diameter (ID) is at least 0.3, preferably 0.5 mm.

(53) The catheter system, in a specific embodiment, has the following dimensions. The total length of the catheter is 60 to 250 mm, preferably 80 to 180 mm, more preferably 100 to 140 mm. The needle has an outer diameter (OD) of 0.6 to 0.9 mm, preferably 0.7 to 0.8 mm. Its inner diameter (ID) is 0.45 to 0.8 mm, preferably 0.6 to 0.7 mm. The needle's wall diameter (WD) is 0.05 to 0.15 mm, preferably 0.75 to 0.125 mm, more preferably 0.8 to 1.0 mm. The outer cannula's outer diameter (OD) is 0.7 to 1.2 mm, preferably 0.9 mm. The outer cannula's inner diameter (ID) is 0.6 to 0.9 mm, preferably 0.8 mm. The outer cannula's wall diameter (WD) is 0.05 to 0.15 mm, preferably 0.075 to 0.125 mm, even more preferably 0.08 to 0.1 mm.

(54) In another specific embodiment, the catheter according to the invention comprises a tube-like construction, which preferably has an outer diameter of 0.9 to 1.2 mm, and an inner diameter of 0.8 to 1.1 mm. It is (slightly) flexible.

(55) The person skilled in the art will appreciate that at least some of the above dimensions depend on the material of the cannulas. This is particularly true for the wall diameter. In any case, the inner diameter of the outer cannula is smaller than the outer diameter of the needle such that the cannulas can be plugged into each other (see above). The wall diameter means the thickness of the tube's wall.

(56) It is further preferred that the radial distance between the cannulas is less than 20% of the ID of the second tube, preferably less than 15% and more preferably less than 10% to conduct any movement of the rear end to the tip without perceptible play.

(57) The cannulas of the catheter system may be made of metal, plastic, carbon fibre and other medically accepted materials provided that these materials have the features as disclosed herein. A preferred material is metal, such as stainless steel.

(58) In one embodiment, the tube consists of metal. In another embodiment, it consists of plastic material. The tip zone may be tapered to ease introduction. The edges may be rounded to provide atraumatic advancement. In one embodiment, it comprises a Luer-lock connector.

(59) The hollow needle may be flexible and bendable. It may comprise a transparent flashback chamber for early indication of blood from eventual vessel puncture. The diameter of the needle is below the diameter of the outer cannula with a distance that allows easy needle removal (0.05 to 0.10 mm). The inner diameter determines the force required for injection, therefore it should not be smaller than 0.25 mm. An easy injection is performed using cannulas with an inner diameter of 0.4-0.8 mm. The needle may comprise a Luer lock connector, or another connector for the hyaluronan syringe. Needle and outer cannula are connected by a temporary lock to ensure the needle tip is fixed in adequate position outside the catheter during skin puncture and introduction towards the target region. The connection may be achieved by thread, hooks, humps, plugs, magnets, and adhesive materials or otherwise.

(60) The catheter system kit comprises cannulas for vascular puncture with double or triple cut tip, the catheter comprises (i) an outer part (non-cutting element), a tube-like construction which is slightly flexible, of a metal or plastic material, preferably of 0.9 to 1.2 mm in outer diameter, and 0.8-1.1 mm inner diameter, (a) the tip zone being optionally tapered to ease introduction, (b) the edges being optionally rounded to provide atraumatic advancement (c) optionally with a Luer-lock connector. (ii) a hollow needle which is flexible and bendable (a) optionally with a transparent flashback chamber, wherein (b) the diameter of the needle is below the diameter of the catheter, wherein (iii) the needle and catheter are connected by a temporary lock to ensure the needle tip is fixed in adequate position outside the catheter during skin puncture and introduction towards the target region.

(61) The system is first used in connected mode with the cannula tip in front to penetrate resistant structures (skin, fascia) until perivascular target position is reached. Extravascular position and proof of no vascular lesion is shown by aspiration: No blood should show on the flashback chamber, otherwise the position has to be changed. After positioning, the cannula is removed. Hyaluronan or another solution (see above) is injected, and the catheter moved for adequate allocation of the hyluronan. Catheter movements can be performed without risk of incidentally puncturing the target vein or other relevant vessels, or damaging nerves because of the blunt tip.

(62) The invention also relates to a preloaded syringe, wherein the solution according to the invention has been loaded. The kit may also comprise such a syringe.

EXAMPLES

Example 1

(63) 15 ml of an aqueous solution comprising 0.5% hyaluronic acid were mixed with 2 ml of 2% solution of Scandicain and injected as shown in the figures. After 2 weeks, the compression by hyaluronan was still effective (FIGS. 14-15), while the contralateral side similarly treated by using saline was totally uncompressed.

Example 2

Regression of Vein Diameters after Sclerotherapy

(64) Sclerotherapy of veins was conducted. Subsequently, an aqueous solution comprising 1% hyaluronic acid (not cross-linked) according to the invention (with IntraShape 1%) was administered to the tissue surrounding the treated vein. The diameter of the treated vein was determined after three time points and its reduction in percent was calculated. The results were compared to the results obtained without administering a solution or composition according to the invention (without IntraShape).

(65) 20 patients, target vein with diameter of 6 to 22 mm and length of segment to be treated 23 to 45 cm.

(66) TABLE-US-00001 14 d 30 d 3 mon. without IntraShape 22.2% 34.7% 48.1% with IntraShape 1% 52.0% 62.0% 74.4%

Example 3

(67) Two patient groups were treated as described in example 2 and further examined with respect to the occurrence of hematoma after perivenous tumescence.

(68) 20 patients per group, great saphenous vein (GSV), diameter 8.2 to 22.1 mm.

(69) TABLE-US-00002 Visible Occur- Visible hema- Number of rence of hema- toma patients with symptoms Number of toma (%) symptoms (%) patients n % n % without 20 14 70.0 5 25.0 IntraShape with IntraShape 20 1 5.0 0 0.0 1%

Example 4

(70) Cannulas with a preferred flexibility were determined as follows. The first (sharp) cannula, the second (blunt) cannula and the catheter (both cannulas assembled), respectively, were pressed against scales. Upon bending the movement of the tip relative to its tangent and the weight was recorded (see FIG. 15). The respective force was calculated. Results are shown below and visualized in FIG. 16.

(71) Flexibility of first cannula (OD 0.8 mm; WD 0.125 mm; length 100 mm):

(72) TABLE-US-00003 tip bent weight force mm g N 1 6.2 0.06 2 11.8 0.12 3 18.2 0.18 4 24.8 0.24 5 33.2 0.33

(73) Flexibility of second cannula (OD: 0.95 mm, WD 0.125 mm; length: 100 mm):

(74) TABLE-US-00004 tip bent weight force mm g N 1 7.1 0.07 2 13.1 0.13 3 19.5 0.19 4 26.7 0.26 5 35.8 0.35

(75) Flexibility of both cannulas:

(76) TABLE-US-00005 cannula sharp blunt both tip bent weight weight weight mm g g g 1 6.2 7.1 12.8 2 11.8 13.1 23.9 3 18.2 19.5 37 4 24.8 26.7 51.3 5 33.2 35.8 68.4

FIGURE CAPTIONS

(77) FIG. 1:

(78) FIG. 1 shows hyaluronan.

(79) FIG. 2:

(80) FIG. 2 shows an aneurysmatic vein.

(81) FIG. 3:

(82) After skin penetration the catheter system is coaxially advanced.

(83) FIG. 4:

(84) The catheter system contains a hollow needle with a double or triple cut tip (4) and a transparent plastic flashback chamber (6). It may have a Luer-lock connector. Top: puncturing position; bottom: injection position (safety position). As outlined above the diameters may vary.

(85) FIG. 5:

(86) After puncturing the tool is advanced without harming the vessel.

(87) FIG. 6:

(88) Retraction and removal of needle.

(89) FIG. 7:

(90) Extravascular position is shown by lack of blood in the flashback chamber, or syringe aspiration.

(91) FIG. 8:

(92) The aqueous solution comprising between 0.1% and 3% hyaluronic acid is injected beside the vessel.

(93) FIG. 9:

(94) FIG. 9 shows typical ultrasound cross-section images.

(95) FIG. 10:

(96) FIG. 11 shows the vein being ready for endovascular treatment.

(97) FIG. 11:

(98) FIG. 11 shows the vein before and after treatment with the solution according to the invention. Ultrasound, cross-sectional view.

(99) FIG. 12

(100) FIG. 12 shows details of the catheter system. A) shows a scheme, B) a prototype (i) system connected, (ii) inner tube with cut tip, fixed outside, (iii) outer tube with smooth tip, and (ii again) of outer tube (puncturing position) and (iii again) inner tube retracted.

(101) FIG. 13

(102) This ultrasound image shows the groin region (sapheno-femoral junction) with perivenous hyaluronan compressing the target vein during laser obliteration. The veins original diameter was 8.8 mm, and now is compressed to 2.5 mm.

(103) FIG. 14

(104) This ultrasound image shows the same region with hyaluronan still effective after 2 weeks. The target vein is closed. Its diameter is compressed to about 2.7 mm (mean).

(105) FIG. 15

(106) Experimental setup for determining preferred flexibility.

(107) FIG. 16

(108) Result of flexibility determination.