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Table of Contents
Year : 2020  |  Volume : 28  |  Issue : 3  |  Page : 138-142

A brief review for common doppler ultrasound flow phantoms

1 Department of Sciences Medical, Higher Institute Sciences Medical, Elkhomes, Libya
2 Department of Medical Imaging, Faculty of Applied Medical Sciences, The Hashemite University, Zarqa, Jordan
3 Department of Sciences Medical, Faculty of Health Sciences, Elmergib University, Elkhomes, Libya
4 Department of Physics, Faculty of Science, University of Jeddah, Jeddah, Saudi Arabia
5 Department of Medical Imaging, An-Najah National University, Nablus, Palestine

Date of Submission08-Oct-2019
Date of Decision31-Oct-2019
Date of Acceptance10-Mar-2020
Date of Web Publication02-Jun-2020

Correspondence Address:
Dr. Ammar A Oglat
Department of Medical Imaging, Faculty of Applied Medical Sciences, The Hashemite University, Zarqa
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Source of Support: None, Conflict of Interest: None

DOI: 10.4103/JMU.JMU_96_19

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In this review, the flow phantoms and the wall-less flow phantoms with recognized acoustic features (attenuation and speed of sound), interior properties, and dimensions of tissue were prepared, calibrated, and characterized by Doppler ultrasound (US) scanning which demands tissue-mimicking materials (TMMs). TMM phantoms are commercially available and readymade for medical US applications. Furthermore, the commercial TMM phantoms are proper for US purpose or estimation of diagnostic imaging techniques according to the chemical materials used for its preparation.

Keywords: Doppler ultrasound scanning, flow phantoms, ultrasonography, wall-less flow phantoms

How to cite this article:
Shalbi SM, Oglat AA, Albarbar B, Elkut F, Qaeed M A, Arra AA. A brief review for common doppler ultrasound flow phantoms. J Med Ultrasound 2020;28:138-42

How to cite this URL:
Shalbi SM, Oglat AA, Albarbar B, Elkut F, Qaeed M A, Arra AA. A brief review for common doppler ultrasound flow phantoms. J Med Ultrasound [serial online] 2020 [cited 2022 Jan 27];28:138-42. Available from: http://www.jmuonline.org/text.asp?2020/28/3/138/285749

  Introduction Top

Flow phantoms

Phantoms are usually utilized to check (calibrate) and characterize ultrasound (US) scanning systems and to confirm their performance weather it matches with quality standards [Figure 1] and [Figure 2]. Moreover, the phantoms are applied to evaluate the development of modern probes, new medical imaging modalities, and medical diagnostic and image processing techniques.[1],[2],[3],[4],[5],[6]
Figure 1: Pictures of (a) a Sylgard carotid vessel mounted in the acrylic phantom box with the metal core prematurely melted out for demonstration purposes, and (b) the completed phantom sealed with a Lexan lid and frame[1]

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Figure 2: Schematic diagram of the flow phantom illustrating acquisition of Doppler measurements[28]

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Several techniques have been advanced to pattern vascular acoustically (vessel) structures and with main concern on prime (large) arteries, such as the coronary and carotid artery [Figure 3]. Flow phantoms are classified into three general classes: walled flow phantom, which has a closer similarity to the vessel arteries; basic (simple tubular structure) flow phantom (with no classes); and wall-less flow phantom, which does not have tubing separating the tissue-mimicking material (TMM) and blood-mimicking fluid (BMF). Moreover, several studies revealed the made of phantoms from the real human vessels which harvested from cadavers (bodies). However, the main disadvantages of flow phantoms include the flow patterns, limited longevity, expensive (high cost), and inconstant geometries.[7],[8]
Figure 3: Photograph of a phantom container with reticulated foam surrounding the connectors. Moreover, color Doppler ultrasound image showing the flow recirculation occurring in the bulb region of a phantom carotid artery[32]

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Flow phantom is a model of TMM with a vessel-mimicking material (VMM) surrounding it during pumping of BMF.[9],[10],[11],[12],[13],[14] The acoustical features of the different ingredients of the flow phantom correspond to the acoustical features of human blood, tissue, and vessel, and as required and identified by the IEC 61685 standard 1999, it can be applied for a proper BMF and TMM.[14] However, when the tubing materials are lacking acoustic properties, the deformation of the Doppler spectrum will lead to the refraction at the vessel wall[15] and attenuation.[16]

Regarding acoustical and physical properties, the most convenient tubing materials are known as C-flex™. This type of tube has an attenuation of 58 dB/cm at 8 MHz and a velocity of sound of 1557 m/s.[16],[17] Even the C-Flex tubing has a sound velocity (Vs) identical to human tissue, the attenuation of C-Flex is nearly ten times greater than the tissue.[18],[19]

Moreover, the Doppler test flow (in stand-alone systems and the Doppler part of duplex scanners) phantom was used to describe Doppler US systems. The development and compatibility of a Doppler flow test object to the actual values of the IEC 1685 was carried out. However, Doppler flow phantom was composed of five main parts: tube (VMM), TMM, BMF, flow pump, and tank. The tube allows a link between the BMF with TMM and the carrying of the blood. The acoustical and physical properties (backscattering, viscosity, sound velocity, density, and α) of these parts were agreed with IEC 1685 values.[16],[19],[20],[21],[22],[23],[24],[25],[26],[27]

Vascular wall-less flow phantoms

Wall-less flow phantom is a VMM which allows the BMF to an immediate link with the TMM with no tubing material applied to fabricate it. There are several factors to consider for the fabrication of a vascular wall-less flow phantom, such as depth, flow waveform (straight, tortuous, oblique), flow rate, and sizes (diameters) of the vessel. For a clinicalin vitro application, the ideal vessel diameters between 3 mm and 10 mm are recommended and should mimic human vessels. For preclinical uses, the vessel diameters are ideally between 0.5 and 2 mm and should mimic rat and mouse vessels. For a clinicalin vitro application, the highest phantom dimension is ideally between 150 and 300 mm; however, for preclinical application, the range is between 50 and 100 mm. The dimensions of preclinical flow phantom are usually less than that of clinical flow phantom.[14],[28]

In another study, Allard et al. (1999) investigated wall-less flow phantoms that made of 9.52 mm as a vessel diameter. The TMM made of a mixture of 8% glycerol, 3% of the very strong agar gel, and 89% of distilled water, was the acoustic speed of TMM which was identical to that of soft tissue. The metal rod worked like the mold for the vessel. Vessel lumen preserved in its original form throughout time, and the wall-less flow phantom was not absorbing H2O. To prevent drying of the agar gel and potential deformation, the phantom was maintained in a water bath. Experimental researches were carried out at room temperature in a horizontal constant flow loop sample. A linear array transducer with 4-MHz (L7-4) was utilized to generate Doppler scan images.

In a previous study, Poepping et al. (2004) prepared a VMM, which is composed of both silicone (polydimethylsiloxane) and elastomer (Sylgard 184). The setup is integrated by a base and a treating factor permitting the mixture to treat for 7 days at specific temperatures ranging between 25°C and 35°C. Four mixtures of cellulose particles with 50-μm as a scatter with different concentrations by weight (0%, 1%, 3%, and 5%) were added and examined for relevant properties, including the Vs, visual appearance, and attenuation with the B-mode US image. Furthermore, the TMM used a different material mixed with a specific amount by weight, such as silicon carbide (SC), aluminum oxide (Al2O3), formaldehyde, high-gel strength agar, glycerol, and distilled water to obtain a proper Vs, backscatter, and attenuation properties. The pulse transmission mechanism was used to measure the TMM attenuation coefficients for Sylgard 184 mixtures. All measurements were conducted through pulse echo single-element unfocused probe and pulse which extend from 2 to 7.5 MHz at room temperature. The attenuation coefficient of TMM at 5 MHz was 0.56 dB/cm and MHz with Vs of 1539 m/s.

Vascular wall-less flow phantom is applied for the evaluation and estimation of Doppler US. Thus, the image distortion results from the tube walls are declined using phantoms. Homogeneous flow phantom was structured by the European Commission Project (ECP) agar-based TMM; it also featured Al2O3, benzalkonium chloride, SC, H2O, and glycerol. This vascular wall-less flow phantom was reported to have the suitable strength (durability) and longevity to flow. However, the agar-based TMM was subjected to rupture at the bifurcation top (apex).[29],[30]

Wall-less flow phantoms for a clinical study (7.9 mm) that made of metal core containers with dimensions of 10 cm × 10 cm × 23 cm were mounted in melting temperature of 69°C. Before pouring, the phantom was fixed with reticulated foam and put around the connectors. TMM was composed of agar, then poured into the container, and let it set. However, the limitation of using the agar-based TMM was due to leakage the BMF during a high flow rate. The problem was solved through the expansion of a new powerful TMM relied on the utilization of two types of gels; Konjac carrageenan (KC) was used instead of agar. The ingredients by %weight was K powder, C powder, Al2O3 powder 3 μm, Al2O3 powder 0.3 μm, H2O, 400 grains SC powder, glycerol, and Pc powder which used to adjusting the temperature of the gel with %weight of 1.5%, 1.5%, 0.96%, 0.89%, 84%, 0.54%, 10%, and 0.7%, respectively. Several items were estimated as a portion of the ECP which made the TMM. The brand of US scanner equipment (Meagher et al., 2007; Watts et al., 2007) used for examining the flow phantom was named HDI 5000 Philips Medical US system. The system is provided with linear array transducer L12-5 to scan the flow channels, collect longitudinal imaging of all areas, and measurement of flow. The acoustical properties of TMM were perfect, and it is meeting the requirements of IEC 1685 draft report. At room temperature, it had a velocity of sound of 1550 ± 6 m/s and attenuation (dB/cm) behavior 2.81 ± 0.08 with 5 MHz as a frequency.[31],[32]

The great-strength agar is utilized because it produces TMM with firmer and more robust and thus, the likelihood of breakage or tear will decrease when exposed to the strength of high-flow rates. TMM was prepared by mixing H2O, SC, Al2O3, benzalkonium chloride, glycerol, and Struers agar materials continuously with a magnetic stirring rod. It was then cooled to 42°C with the keep of stirring and then poured the mixing materials into the test container. The VMM was made by casting the metallic rod inside the wall-less TMM channel with about 8-mm diameter. US scanner equipment (HDI 5000 Philips with linear array transducer L12-5) used for examining the flow phantom was the same equipment used in the previous studies by Meagher et al. (2007). The acoustical properties of TMM were perfect, and it is meeting the requirements of IEC 1685 draft report. At room temperature, it had a velocity of sound of 1541 ± 3 m/s and an attenuation (dB/cm) behavior 0.5 ± 0.03 with nearly 3–10 MHz as a frequency.

Fabrication of wall-less flow phantoms is necessary to prevent problems that resulted by US deformation through the tube wall.[14],[28] TMM was created by utilizing two hydrogel materials, namely KC. The KC is composed of two organic materials and was added with H2O to produce a flexible and strong material. TMM is prepared by mixing SC, Al2O3, glycerol, and KC materials. The KC-based TMM had a velocity of sound of 1548 ± 3 m/s and attenuation (dB/cm) behavior of 0.01024f2 + 0.3639f, where f is transferred frequency (MHz).[14],[32]

Vascular wall-less flow phantom for preclinical study (1 mm) was fabricated. The phantom was made of the plastic box and connected with plastic pipe connectors to allow the connection of the BMF reservoir with a flexible tube. A straight rod supplies a mold to mimic the vessel. Thus, as the rod is removed from the KC-based TMM, it will simulate the vessel VMM shape. Therefore, the blood can be pumped through the VMM. The phantom size is determined by the size of the container and the rod. For avoiding leaking of the BMF, the pipe connectors are fixed with the KC-based TMM using a reticulated foam. However, the main drawback of the KC-based TMM is that it is not adequate for long-term storage.[14] Instruments and recipes required in preparing TMM (KC-based TMM) were listed and mentioned in a previous study [Figure 4] and [Table 1].[32]
Figure 4: Konjac carrageenan-based tissue-mimicking material flow phantom used with the Visualsonics Vevo 770 preclinical scanner[14]

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Table 1: A summary for phantom materials

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Currently available wall-less flow phantoms (commercial)

Shelley's TMM (anthropomorphic) carotid bifurcation flow phantom is designed to very carefully and accurately simulate complex geometries' physiological vessel and is compatible with Doppler US. TMM was created using agar-based TMM. Length, width, and height of this phantom are 265 mm × 120 mm × 65 mm, respectively. The scatter particles are added to the VMM to enhance echogenicity and speckle pattern. The acoustical and physical properties were suitable [Figure 5].[33]
Figure 5: Ideal flow phantom for Doppler and color Doppler flow research and development applications[33]

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Doppler flow phantom with model U-245-based TMM designs for the evaluation and estimation of diagnostic Doppler US. The phantom model U-245 has a long-lasting TMM (urethane) and mix two wall-less flow vessels (agar-based TMM). The vessel size is 8.0 mm and was placed horizontally 2.0 cm below the scanning surface mimicking the common carotid artery and a 4.0 mm vessel. The flow phantom was connected to Shelley gear motor pump system; the BMF has filled the pump and produces the most accurate, repeatable, and realistic flow waveforms for Doppler US testing. Overall dimensions (length, width, and height) of this phantom are 17 cm × 10 cm × 21.5 cm, respectively. The acoustical properties were suitable and agreed the requirements of IEC 1685 [Figure 6].[34]
Figure 6: The model U-245 tissue equivalent Doppler flow phantom is for the evaluation of diagnostic Doppler ultrasound[34]

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Gear (motor) pump system

Multiflow gear pump system has many properties that make it typical to produce steady and pulsatile flow, such as a fast temporal response, loss of backflow, and capacity to monitor gear pump velocity. A multiflow gear pump system is available which provides several of the flow output, allowing make of flow phantoms suitable with a different range of flow rates. For instance, the flow rate is from a small number of milliliter per minute to hundreds or thousands number of milliliter per minute; also, monitor of pump velocity permits the generating of time-changing or pulsatile fluid flow.[14],[16],[18],[28]

Limitations of the flow phantoms

The main limitation during fabrication of the flow phantom is the repeating pouring of TMM inside the phantom box which takes more than five times and could lead to losing of large amounts of items, because in each time, the air bubbles were produced on the TMM surface, and sometimes, the TMM was immediately cooled during the pouring process, and this produces several layers of TMM and then affects the acoustical features measurements. However, the direct cooled of TMM refers to the effect of the gelatin on the TMM strength.


We thank our colleagues from the Medical Imaging Department, Faculty of Allied Health Sciences, the Hashemite University, who provided insight and expertise that greatly assisted the review, although they may not agree with all the interpretations of this article.

Financial support and sponsorship


Conflicts of interest

There are no conflicts of interest.

  References Top

Grand-Perret V, Jacquet JR, Leguerney I, Benatsou B, Grégoire JM, Willoquet G, et al. A novel microflow phantom dedicated to ultrasound microvascular measurements. Ultrason Imaging 2018;40:325-38.  Back to cited text no. 1
Oglat AA, Matjafri MZ, Suardi N, Oqlat MA, Abdelrahman MA, Oqlat AA. A review of medical Doppler ultrasonography of blood flow in general and especially in common carotid artery. J Med Ultrasound 2018;26:3-13.  Back to cited text no. 2
[PUBMED]  [Full text]  
Oglat AA, Matjafri MZ, Suardi N, Oqlat MA, Abdelrahman MA, Oqlat AA, et al. Chemical items used for preparing tissue-mimicking material of wall-less flow phantom for Doppler ultrasound imaging. J Med Ultrasound 2018;26:123-7.  Back to cited text no. 3
[PUBMED]  [Full text]  
Oglat AA, Suardi N, Matjafri MZ, Oqlat MA, Abdelrahman MA, Oqlat AA. A review of suspension-scattered particles used in blood-mimicking fluid for Doppler ultrasound imaging. J Med Ultrasound 2018;26:68-76.  Back to cited text no. 4
[PUBMED]  [Full text]  
Oglat AA, Matjafri MZ, Suardi N, Abdelrahman MA, Oqlat MA, Oqlat AA. A new scatter particle and mixture fluid for preparing blood mimicking fluid for wall-less flow phantom. J Med Ultrasound 2018;26:134-42.  Back to cited text no. 5
[PUBMED]  [Full text]  
Ammar AO, Matjafri MZ, Suardi N, Oqlat MA, Oqlat AA, Abdelrahman MA, et al. Characterization and construction of a robust and elastic wall-less flow phantom for high pressure flow rate using Doppler ultrasound applications. Nat Eng Sci 2018;3:359-77.  Back to cited text no. 6
Culjat MO, Goldenberg D, Tewari P, Singh RS. A review of tissue substitutes for ultrasound imaging. Ultrasound Med Biol 2010;36:861-73.  Back to cited text no. 7
Dabrowski W, Dunmore-Buyze J, Cardinal HN, Fenster A. A real vessel phantom for flow imaging: 3-D Doppler ultrasound of steady flow. Ultrasound Med Biol 2001;27:135-41.  Back to cited text no. 8
Browne JE. A review of Doppler ultrasound quality assurance protocols and test devices. Phys Med 2014;30:742-51.  Back to cited text no. 9
Grice JV, Pickens DR, Price RR. Technical Note: A new phantom design for routine testing of Doppler ultrasound. Med Phys 2016;43:4431.  Back to cited text no. 10
Lai SS, Yiu BY, Poon AK, Yu AC. Design of anthropomorphic flow phantoms based on rapid prototyping of compliant vessel geometries. Ultrasound Med Biol 2013;39:1654-64.  Back to cited text no. 11
Law YF, Cobbold RS, Johnston KW, Bascom PA. Computer-controlled pulsatile pump system for physiological flow simulation. Med Biol Eng Comput 1987;25:590-5.  Back to cited text no. 12
Hoskins PR, Anderson T, McDicken WN. A computer controlled flow phantom for generation of physiological Doppler waveforms. Phys Med Biol 1989;34:1709-17.  Back to cited text no. 13
Zhou X, Kenwright DA, Wang S, Hossack JA, Hoskins PR. Fabrication of two flow phantoms for Doppler ultrasound imaging. IEEE Trans Ultrason Ferroelectr Freq Control 2017;64:53-65.  Back to cited text no. 14
Thompson RS, Aldis GK, Linnett IW. Doppler ultrasound spectral power density distribution: Measurement artefacts in steady flow. Med Biol Eng Comput 1990;28:60-6.  Back to cited text no. 15
Ramnarine KV, Anderson T, Hoskins PR. Construction and geometric stability of physiological flow rate wall-less stenosis phantoms. Ultrasound Med Biol 2001;27:245-50.  Back to cited text no. 16
Hoskins P, Ramnarine K. Doppler test devices. In: Doppler Ultrasound: Physics, Instrumentation and Signal Processing. 2nd ed., Vol. 4. Chichester, UK: Wiley; 2000. p. 2010.  Back to cited text no. 17
Hoskins PR. Simulation and validation of arterial ultrasound imaging and blood flow. Ultrasound Med Biol 2008;34:693-717.  Back to cited text no. 18
Rickey DW, Picot PA, Christopher DA, Fenster A. A wall-less vessel phantom for Doppler ultrasound studies. Ultrasound Med Biol 1995;21:1163-76.  Back to cited text no. 19
Foster FS, Mehi J, Lukacs M, Hirson D, White C, Chaggares C, et al. A new 15-50 MHz array-based micro-ultrasound scanner for preclinical imaging. Ultrasound Med Biol 2009;35:1700-8.  Back to cited text no. 20
Hoskins PR. Estimation of blood velocity volumetric flow and wall shear rate using Doppler ultrasound. Ultrasound 2011;19:120-9.  Back to cited text no. 21
King DM, Moran CM, McNamara JD, Fagan AJ, Browne JE. Development of a vessel-mimicking material for use in anatomically realistic Doppler flow phantoms. Ultrasound Med Biol 2011;37:813-26.  Back to cited text no. 22
Moran CM, Pye SD, Ellis W, Janeczko A, Morris KD, McNeilly AS, et al. A comparison of the imaging performance of high resolution ultrasound scanners for preclinical imaging. Ultrasound Med Biol 2011;37:493-501.  Back to cited text no. 23
Steel R, Fish PJ, Ramnarine KV, Criton A, Routh HF, Hoskins PR. Velocity fluctuation reduction in vector Doppler ultrasound using a hybrid single/dual-beam algorithm. IEEE Trans Ultrason Ferroelectr Freq Control 2003;50:89-93.  Back to cited text no. 24
Yang X, Hollis L, Adams F, Khan F, Hoskins PR. A fast method to estimate the wall shear stress waveform in arteries. Ultrasound 2013;21:23-8.  Back to cited text no. 25
Teirlinck CJ, Bezemer RA, Kollmann C, Lubbers J, Hoskins PR, Ramnarine KV, et al. Development of an example flow test object and comparison of five of these test objects, constructed in various laboratories. Ultrasonics 1998;36:653-60.  Back to cited text no. 26
Kenwright DA, Sadhoo N, Rajagopal S, Anderson T, Moran CM, Hadoke PW, et al. Acoustic assessment of a konjac–carrageenan tissue-mimicking material aT 5–60 MHZ. Ultrasound Med Biol 2014;40:2895-902.  Back to cited text no. 27
Kenwright DA, Laverick N, Anderson T, Moran CM, Hoskins PR. Wall-less flow phantom for high-frequency ultrasound applications. Ultrasound Med Biol 2015;41:890-7.  Back to cited text no. 28
Ramnarine KV, Hoskins PR, Routh HF, Davidson F. Doppler backscatter properties of a blood-mimicking fluid for Doppler performance assessment. Ultrasound Med Biol 1999;25:105-10.  Back to cited text no. 29
Tortoli P, Morganti T, Bambi G, Palombo C, Ramnarine KV. Noninvasive simultaneous assessment of wall shear rate and wall distension in carotid arteries. Ultrasound Med Biol 2006;32:1661-70.  Back to cited text no. 30
Watts DM, Sutcliffe CJ, Morgan RH, Meagher S, Wardlaw J, Connell M, et al. Anatomical flow phantoms of the nonplanar carotid bifurcation, part I: Computer-aided design and fabrication. Ultrasound Med Biol 2007;33:296-302.  Back to cited text no. 31
Meagher S, Poepping TL, Ramnarine KV, Black RA, Hoskins PR. Anatomical flow phantoms of the nonplanar carotid bifurcation, part II: Experimental validation with Doppler ultrasound. Ultrasound Med Biol 2007;33:303-10.  Back to cited text no. 32
Technologies, S.M.I. Carotid Bifurcation Doppler Flow Phantoms. Available from: http://www.simutec.com/Docs/Carotid%20Bifurcation%20 Doppler%20Flow%20Phantoms%20low-res.pdf.[Last accessed on 2020 Apr 14].  Back to cited text no. 33
Technologies, S.M.I. Model U-245 Doppler Flow Phantom. Available from: http://www.simutec.com/Docs/U-245%20Doppler%20 Phantom%20LR.pdf. [Last accessed on 2020 Apr 14].  Back to cited text no. 34


  [Figure 1], [Figure 2], [Figure 3], [Figure 4], [Figure 5], [Figure 6]

  [Table 1]

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