as described above , prior art phased array assemblies 10 consist of a series of small rectangular elements , a and b , that are evenly spaced in a flat plane . this configuration causes the elements to emit energy beams at different angles when the phased array beam 20 is steered and focused . this can undesirably cause a widened phased array beam 20 . by contrast , the improved phased array in this patent specification reduces the undesired wideness by placing a phased array in a concaved configuration , as shown in fig2 . fig2 shows a phased array 100 of imaging elements , a and b . the elements , a and b , are situated along a concave 130 path having a radius r . the phased array 100 can have additional imaging elements along the concave path 130 ( not shown ). the phased array 100 has a length , l , and a maximum steering angle in the azimuthal direction , θ . f represents a focal point at the maximum steering angle in the azimuthal direction . the phased array 100 is shown focusing an energy beam , such as an acoustic pulse , 120 at focal point f . α and β , represent the tangential angles for elements a and b to the focal point f respectively . α 1 and β 1 , represent the flat plane angles for elements a and b to the focal point f respectively . point o represents the origin of the horizontal and vertical axis , x and y . in the case of a phased array 100 having a large number of imaging elements , wherein elements a and b represent the edge elements of the array 100 , at focal point f , element b will have the largest angle β 1 , to the focal point f , whereas element a will have the smallest angle α 1 , to the focal point f . the concaving of the array 100 will decrease the tangential angle β , for element b by β 2 , and increase the tangential angle α for element a by α 2 . one of ordinary skill in the art would appreciate that by concaving the array 100 , elements a and b will have the most significant impact on the resulting beam 120 as compared to any imaging elements in between elements a and b , and the center imaging elements will be least affected . the following is an approach to calculating the radius of curvature r of a concave phased array 100 that enables the tangential angles α and β , to be equal at the maximum azimuthal direction θ . from fig2 , the following is true : combining equations ( 5 )-( 8 ), the radius of curvature r can be expressed as : in the case of a 10 mhz , 64 element phased array , wherein the length of the array is 5 mm , if the array &# 39 ; s maximum angle in the azimuthal direction is 45 °, and the focal depth is 5 mm , then the radius of curvature r is preferably approximately 7 mm . equation ( 9 ) expresses the radius of curvature of a concave array , r , as a function of a desired focal depth if the other parameters in the array design , such as image range , have been provided . for an image range from of 1 to of 2 , an average radius of curvature r a may be determined by : the concave array 100 may have a uniform pitch , wherein the space from element center to element , a and b , is uniform ; however , it can be non - uniform as well . an element &# 39 ; s width can be varied to maximize the beam quality , as one of ordinary skill in the art would appreciate . for example , the element width can conform to a gaussian , bessel , or sinusoidal function using an element index number calculated from the array 100 center to an edge element , e . g ., a or b . for an ultrasound phased array 100 , the array 100 can be fabricated by a variety of available active acoustic material , such as piezo - ceramics , piezo - films ( thin or thick ), 2 - 2 or 1 - 3 piezoceramic composites , 2 - 2 or 1 - 3 piezocrystal materials , or cmut . further , other imaging devices may be used , instead of , or in addition to imaging transducers , such as light based apparatuses for obtaining images through optical coherence tomography ( oct ). image acquisition using oct is described in huang et al ., “ optical coherence tomography ,” science , 254 , nov . 22 , 1991 , pp 1178 - 1181 , which is hereby incorporated by reference in its entirety . a type of oct imaging device , called an optical coherence domain reflectometer ( ocdr ) is disclosed in swanson u . s . pat . no . 5 , 321 , 501 , which is incorporated herein by reference . the ocdr is capable of electronically performing two - and three - dimensional image scans over an extended longitudinal or depth range with sharp focus and high resolution and sensitivity over the range . such an array 100 is useful for intracardiac applications , and may be used for other applications , such as any kind of b - scanner medical applications , ophthalmic ultrasound , hifu and / or ndt . turning to fig3 , the phased array 100 may be used in a catheter , as described above , and can also be placed in a distal portion 520 of a guidewire 500 . the guidewire 500 may comprise a guidewire body 302 in the form of a flexible , elongate tubular member , having an outer wall 301 . the guidewire body 302 may be formed of any material known in the art including composite materials , plastics , braided polyimide , polyethylene , peek braids , stainless steel , other superelastic materials , or metal alloys , such as a nitinol hypertube , turning to fig4 , a proximal portion 510 of the guidewire 500 , shown in fig3 , may be adapted to connect to circuitry 600 that processes imaging signals from the phased array 100 , such circuits being well known . in the foregoing specification , the invention has been described with reference to specific embodiments thereof . it will , however , be evident that various modifications and changes may be made thereto without departing from the broader spirit and scope of the invention . for example , the reader is to understand that the specific ordering and combination of process actions described herein is merely illustrative , and the invention can be performed using different or additional process actions , or a different combination or ordering of process actions . as a further example , each feature of one embodiment can be mixed and matched with other features shown in other embodiments . additionally and obviously , features may be added or subtracted as desired . accordingly , the invention is not to be restricted except in light of the attached claims and their equivalents .
the present invention generally relates to medical devices , and more particularly to an improved intravascular device . in one embodiment , an intravascular device includes a catheter having proximal and distal portions , and a phased array of imaging elements , having edge elements each having angles of emission , located in the distal portion of the catheter , wherein the phased array is concaved having a radius of curvature such that when the phased array is steered in a maximal azimuthal direction , the angles of emission of the edge elements are substantially similar .