referring to fig1 , and 8 , one embodiment of the invention comprises a plate 51 , 851 , with an integrated channel system , with a base stem 110 and a left arm 120 , a right arm 130 and a central arm 140 . the walls of the base stem 810 , 820 are essentially perpendicular to the plate 51 and parallel or near parallel to each other , and to the flow , which is a prerequisite for the establishment of standing waves across the channel along its entire depth and length , see below . at the back of the plate 51 , means for delivering ultrasound energy to the plate is arranged in the form of a piezoelectric element 150 , 853 . the device will function as follows : a fluid with suspended particles entering the base stem 110 at the inlet 160 will flow towards the branching point 175 because of an arranged pressure gradient , which gradient could be created by e . g . a suction pump , a pressure pump , a syringe or by gravity . by controlling the frequency of the ultrasound and use of certain frequencies suitable to the dimensions of the base stem 110 , particularly the width 185 of said stem 110 , a stationary wave pattern is formed in the fluid inside said stem 110 . especially there will form a stationary wave pattern orthogonal to the direction of the flow between a left 810 and a right 820 side wall of the base stem 110 . pressure nodes will form in greater numbers in the middle part of the channel than at the walls , where pressure antinodes will form . during said flow , particles in the fluid will tend to accumulate in nodes of said stationary wave - pattern , or in certain layers in relation to the nodes depending on the particles &# 39 ; density / densities / acoustic impedance relative to the surrounding fluid . particles with a higher density than said surrounding fluid will tend to accumulate in the nodes , whereas particles with a density lower than the surrounding fluid will tend to accumulate in the antinodes . the layers of fluid discussed in the following are the layers parallel to the sidewalls 810 , 820 of the base stem 110 . depending on the density / acoustic impedance , size and weight of the particles , certain patterns of accumulations of particles will be formed . this is an advantage when separating out particles of a certain weight and / or size from a medium containing a spectrum of particles of different density / acoustic impedance . generally , particles having a density higher than the density of the surrounding fluid , accumulates in the nodes , and particles having a density lower than the fluid without particles , accumulate in the antinodes . by providing a branching fork with two side branches or arms and one central branch or arm 140 as shown in fig1 or 8 , it is possible to separate out said particles . the post - branch point arms or channels are preferably arranged with spacing adapted to the wavelength , i . e ., a centre to centre distance of approximately ⅜ of a wavelength . depending on the resonance conditions , confer fig7 different results of the above will be obtained . for a single node condition , the result of the above is that the layers of fluid near the walls of the base stem 110 will contain a decreasing concentration of high density particles as the fluid flows along said stem 110 towards the branching point 175 . at said branching point 175 , fluid that mainly originates from the central parts of the fluid - stream in the stem 110 will , due to laminar flow , continue its movement straight ahead and enter the central arm 140 . fluid originating from the fluid - stream appearing near the walls of the stem 110 , will deflect into the left arm 120 ( from the left wall ) and into the right arm ( from the right wall ). fractions of fluid containing a low concentration of high - density particles can then be collected at the left outlet 170 and the right outlet 180 . the fraction of fluid containing a high concentration of high - density particles can be collected at the top outlet 190 . in fig9 is shown how a number of high density particles ( higher density than surrounding fluid ) accumulates in a central division or channel with a central outlet 91 , whereas fluid with a low or zero concentration of said particles flows out at the lateral divisions and outlets 92 . as a comparison , fig1 shows one way of using a two - node standing wave pattern to move the particles so that they can be collected at two lateral divisions provided with outlets 102 . fluid with a low or zero concentration of said particles flows out at the central division and outlet 101 . a similar effect could also be achieved using five divisions or channels , where the most lateral channels and the central channel collect fluid with low or zero concentration of high density particles , and the other two channels collect fluid with high concentration of said particles , i . e . n = 3 below . by controlling the frequency of the ultrasound that creates the standing wave field it is possible to generate a standing wave between the side walls of the base stem 110 with a standing wave length of 0 . 5 , 1 . 5 , 2 . 5 etc . wavelengths , i . e ., n times 0 . 5 wavelengths , n = 1 , 3 , 5 , 7 . . . cf . fig7 . a device according to the invention making use of the invention &# 39 ; s ability to separate particles into the nodes and antinodes could therefore have a number of channels after the branching point corresponding to the number of nodes plus the number of antinodes in the standing wave field . for example , frequencies having 0 . 5 , 1 , 5 and 2 . 5 wavelengths across the base stem 110 could have 3 , 5 and 7 channels correspondingly . preferred embodiments of the invention therefore include means for controlling the frequency of the ultrasound generating means . in fig8 is shown how a control unit 863 ( shown in a different scale ) can be connected to the piezoelectric element 853 . said control unit 863 is capable of delivering electrical energy to said element 853 . said electrical energy is controllable with regard to waveform , frequency and power , where said waveform is controllable to be one of , but not limited to sinus wave , triangular wave or square wave . other embodiments of the invention include bifurcation and “ trifurcation ” of different shape , integrated on the same piece of material , and with the overall purpose to divide the laminar flow of fluid . in fig6 is shown a detail of another embodiment where the branching point comprises the branching of the base stem 110 directly into three parallel arms 610 , 620 , 630 divided by thin dividing walls . by the use of the techniques described below it is possible to arrange these thin walls with a thickness of down to 1 μm and even lower . thin walls will give better performance due to better preservation of the laminar flow profile across the full channel width . [ 0049 ] fig1 shows an embodiment with a left branching angle α1 between a left arm 143 and a central arm 144 and a right branching angle α2 between said central arm 144 and a right arm 145 . by varying the angles α1 and α2 it is possible to optimise certain factors such as e . g . the degree of particle concentration . however , certain angles can be difficult to manufacture with certain manufacturing processes . angles between 0 and 90 degrees show good ability to separate flow . in fig3 which shows the device from beneath , are shown the connections 31 - 34 to the inlet 160 and to the outlets 170 , 180 , 190 from fig1 . the piezoelectric element is not shown for the sake of clarity . in fig4 the device is shown from the side . the device preferably comprises two layers , one layer 51 including the channel system , made e . g . of silicon , and one sealing layer 52 made of e . g . glass which makes it possible to visually inspect the process . the sealing glass layer could preferably be bonded with known techniques to the base layer 51 . the piezoelectric element 53 is arranged in acoustic contact with the base layer 51 . in fig5 , 12 , and 13 arrangements are shown where certain effects can be achieved through a consecutive or serial use of repeated structures . for example , high and low density particles can be separated using the arrangement in fig5 . ( high and low density indicate merely the density relatively to the surrounding fluid ). here , fluid is entered at a main inlet 60 . if a one - node resonance condition is present , fluid with high concentration of high - density particles will accumulate at outlet 61 . fluid with low concentration of high - density particles together with high concentration of low - density particles will accumulate at outlet 62 , and fluid with intermediate concentration of high - density particles will accumulate at outlet 63 . a piezoelectric element 65 is arranged in acoustic contact with the common supporting structure , giving rise to standing wave fields in channels with appropriate dimensions , i . e . the channel parts 66 and 68 . to compensate for fluid loss , inlets 69 are provided for adding pure fluid without particles . the inlets could also be used for cleaning of the system . parallel arrangements of single or serial structures according to fig5 , 12 , and 13 can easily be achieved . channel systems according to embodiments of the invention could e . g . repeatedly and inter - connectedly be arranged , filling the area of the plate , which plate can comprise e . g ., a silicon wafer or other area sheets or discs of other materials such as e . g . plastics . parallel arrangements will add capacity , i . e . more fluid volume can be processed per time interval . [ 0054 ] fig1 shows schematically a one - node three - step serial washer . contaminated fluid with particles of interest to save ( e . g . red blood cells ) enters at inlet 111 . contaminated fluid with low or zero concentration of particles leaves at outlets 112 . particles continue to flow , passing inlet 113 which adds clean fluid to the particles and some still remaining contaminants will become more diluted . separation will be repeated in a second step where contaminated fluid with low or zero concentration of particles leaves at outlets 114 . particles continue to flow , passing inlet 115 , which adds clean fluid to the particles and if still some remaining contaminants , these will become even more diluted . separation will then be repeated in a third step , and particles suspended in now very clean fluid will leave at outlet 117 . [ 0055 ] fig1 shows schematically a one - node three - step serial concentrator . contaminated fluid with particles of interest to save ( e . g . red blood cells ) enters at inlet 121 . particles are concentrated at outlets 122 , 124 and 128 . contaminated fluid is removed at outlets 126 . [ 0056 ] fig1 shows schematically a one - node four - step integrated washer and concentrator . contaminated fluid with particles of interest to save ( e . g . red blood cells ) enters at inlet 131 . contaminated fluid with low or zero concentration of said particles leaves at outlets 132 . clean fluid is added at inlet 134 . in a second step , ( less ) contaminated fluid with low or zero concentration of particles leaves at outlets 133 . clean fluid is added at inlet 136 . in steps 3 and 4 particles are concentrated and removed through outlets 137 and 138 . excess fluid is removed through outlets 139 . returning now to fig1 the channel system , including the base stem 110 and the branching point , is preferably integrated on a single piece of homogenous material 51 in fig4 . this entails the advantage of ease to repeat a number of channel systems thereby easily increasing the capacity of a separation apparatus making use of the invention . preferred embodiments include embodiments with channel systems integrated with a single substrate or deposited on a substrate by a continuous series of compatible processes . the device according to the present invention can be manufactured for example in silicon . the requirement to make the walls of the base stem ( 810 , 820 ) essentially perpendicular to the plate and parallel or near parallel to each other is easily fulfilled by using silicon of a & lt ; 110 & gt ; crystal structure and well known etching techniques . the desired channel wall structure described may also be realised by deep reactive ion etching , drie . it is also possible to form the layers in plastic materials , for instance by using a silicon matrix . many plastics have good chemical properties . the silicon layer structure can be produced by means of well - known technologies . channels and cavities can be produced by means of anisotropic etching or plasma etching techniques . the silicon layer may be protected against etching by an oxide layer that is by forming a sio 2 layer . patterns may be arranged in the sio 2 layer by means of lithographic technologies . also , etching may be selectively stopped by doping the silicon and using p . n . etch stop or other etch stop techniques . since all these process steps are well known in the art they are not described in detail here . the above described technology is also suitable for producing a matrix or mould for moulding or casting devices of the invention in e . g . plastic . the piezoelectric element providing the mechanical oscillations is preferably of the so - called multi - layer type , but a bimorph piezoceramic element may also be used as well as any other kind of ultrasound generating element with suitable dimensions . an appreciated application of an embodiment of the invention is in the field of cleaning a patient &# 39 ; s blood during surgical operations . the object in this field is to sort out the red blood cells from the contaminated plasma . contamination could include air bubbles , fat particles , coagulation products and other not desirable biological material . the red cells will thereafter be brought back to the patient &# 39 ; s circulation . one disadvantage with prior art in the form of centrifuges is that the red blood cells can become deformed , a disadvantage that is not present with a device according to the present invention . depending on the application , the shape and dimensions of the channel , the length of the stem 110 and the arms 120 , 130 , 140 , and the frequency of the ultrasound may vary . in an application for separating out red blood cells from diluted blood recovered from a patient during a surgical operation , the channel is preferably rectangular in cross - section and the stem part of the channel has a width of 700 μm for a one - node standing wave ultrasound field . greater widths will be appropriate for standing wave ultrasound fields with more nodes . the mechanical tolerance of the width of the channel is important . the difference should preferably be less than a few percent of half the wavelength of the frequency used in the material / the fluid concerned . [ 0066 ] fig1 shows a separation unit comprising eight channel units 1501 - 1508 , which units are supplied with fluid from a distribution cavity 1510 having one inlet 1512 and eight outlets 1521 - 1528 . each channel unit 1501 - 1508 is provided with three outlets , one central outlet 1541 and two lateral outlets . said lateral outlets are connected in pairs , except for the two most lateral outlets of the separation unit 1500 , forming nine intermediate outlets 1531 - 1539 . said intermediate outlet are connected to a fast collecting cavity ( not shown ) alternatively to a first collecting manifold ( not shown ). the central outlets 1541 - 1548 are connected to a second collecting cavity alternatively to a second collecting manifold ( neither shown ). [ 0067 ] fig1 shows the separation unit 1500 of fig1 in a perspective view . the plate 1602 in which the separation unit 1500 is formed is arranged on top of an ultrasound source 1620 , preferably a piezoelectric element 1620 and a support structure 1612 . an inlet tube 1610 is connected to the distribution cavity inlet 1542 to provide an inlet for the fluid connectable to outside tubing . a first outlet tube 1631 is providing a connection from the nine intermediate outlets 1531 - 1539 via a first collecting manifold to a free end 1641 of said first outlet tube 1631 . a second outlet tube 1632 is providing a connection from the eight central outlets 1541 - 1548 via a second collecting manifold to a free end 1642 of said second outlet tube 1632 . [ 0069 ] fig1 shows a serial arrangement in a plate 1701 of two channel units , devised to increase particle separation from a fluid . a first channel unit 1710 is formed in the plate 1702 having a central branch 1712 , which branch is connected to a base channel 1721 of a second channel unit 1720 . each channel unit is provided with ultrasound energy from piezoelectric elements arranged under the plate 1701 at positions approximately under a portion of the base channel of each channel unit as indicated by rectangles 1716 , 1726 . [ 0070 ] fig1 show a channel unit 1800 used to separate a fluid containing two types of particles , indicated as black and white , respectively . when fluid flows in the direction of the arrow 1804 , ultrasound - standing waves are separating the particles in the channel unit into three fluid layers 1801 - 1803 . the position of the ultrasound source is indicated by the rectangle 1810 . the described process separating two types of particles is illustrating a solution to the need within the field of medical technology to separate blood components from each other , i . e . red and white blood cells and platelets ( erythrocytes , leukocytes and thrombocytes ), also called the formed elements of the blood . known art in the field comprises mainly or solely solutions based on centrifugation . a disadvantage is that it is very difficult to obtain a complete separation of the formed elements , instead a so - called “ buffy coat ” is obtained . this buffy coat comprises a high concentration of thrombocytes , leukocytes and a low concentration of erythrocytes . in this context one should bear in mind that the sensitive thrombocytes have been centrifugated and subjected to high g - forces , which probably have induced an impaired function within said erythrocytes . an embodiment of the present invention can be used to separate thrombocytes and leukocytes from erythrocytes , because they possess different densities as can be seen in table 1 . blood consists of plasma and formed elements . as can be seen in table 1 , different components have different density . the variation in density is very small for the table entries . when ordinary blood is separated , a channel unit will separate all formed elements in the same way , because their density is higher than the medium they are suspended in , i . e . the plasma . as an alternative embodiment , the medium is modified , i . e . the plasma is modified so that its density is altered , giving the possibility to separate the different blood cells . this is achieved by adding an amount of denser liquid to the plasma and thereby dilute the plasma to a lower concentration , but with a higher density . take 100 ml blood with a haematocrit of 40 %. this entails that 60 % (= 60 ml ) of the blood is plasma . the plasma has a density of 1 . 0269 . by adding 30 ml of 50 % glucose solution we get according to the formula : when this mixture is entered in an embodiment , a separation is achieved where thrombocytes and erythrocytes are directed into separate branches , because now the thrombocytes are lighter than the medium . this is of course just an example . it is also possible to separate out leukocytes because they have a specific weight , different from the one of erythrocytes and thrombocytes . it should also be possible to separate out bacteria and virus with this method . the method can be used on all solutions except those solutions where it is impossible or otherwise inappropriate to manipulate the density of the solution . it is also possible to separate out bacteria and stem cells from cultures of the same , having them suspended in a suitable solution . [ 0088 ] fig1 and fig2 shows a channel unit with three inlets a , b , a and three outlets c , d , c . a first fluid is fed to the channel unit at both a - inlets and a second fluid is fed to the b inlet . at this microscale , the fluids will not blend . [ 0089 ] fig2 shows how particles from the fluid entered at the a - inlets are forced by the ultrasound standing wave field to migrate over to the fluid entered at the b - inlet . this type of “ separation ” is especially useful when the objective is to keep formed elements of the blood and discard the plasma , as in e . g . plasmapheresis , and in blood wash applications where blood cells in contaminated plasma ( a ) are moved to a clean solution ( b ) and finally blood cells in a clean medium is produced ( d ). the waste plasma ( c ) is discarded . this method will enable a highly efficient blood wash with very low amounts of washing substance needed . [ 0090 ] fig2 and 22 show a radial arrangement of the channel units , said arrangement being particularly advantageous when base material of the plate are circular discs or the like . it will be appreciated by persons skilled in the art that the structure of the device according to the present invention has several advantages including ease of manufacture and solving of the problem of separating particles liable to disintegration in filtering and centrifugation processes .
the present invention provides a device and a method for separating particles from fluids using ultrasound , laminar flow , and stationary wave effects comprisinga micro - technology channel system with an integrated branching point or branching fork , and a single ultrasound source . one of the characteristics of the invention is that the single ultrasound source , which generates the standing waves , excites the complete structure including the channel system . no special reflectors or the like are needed . extremely thin dividers can separate the flow , thereby enhancing the effectiveness of the device . the device could be manufactured in silicon and the ultrasound energy could preferably be delivered by a piezoelectric element .