Figure 1. (a) Top view of the microfluidic-magnetophoretic device, (b) Schematic representation of the channel cross-sections studied in this work, and (c) the magnet position relative to the channel location (Sepy and Sepz are the magnet separation distances in y and z, respectively).

Continuous-Flow Separation of Magnetic Particles from Biofluids: How Does the Microdevice Geometry Determine the Separation Performance?

by 
Cristina González Fernández1, Jenifer Gómez Pastora2, Arantza Basauri1, Marcos Fallanza1, Eugenio Bringas1, Jeffrey J. Chalmers2 and Inmaculada Ortiz1,*
1Department of Chemical and Biomolecular Engineering, ETSIIT, University of Cantabria, Avda. Los Castros s/n, 39005 Santander, Spain
2William G. Lowrie Department of Chemical and Biomolecular Engineering, The Ohio State University, 151 W. Woodruff Ave., Columbus, OH 43210, USA
*Author to whom correspondence should be addressed.
Sensors 2020, 20(11), 3030; https://doi.org/10.3390/s20113030
Received: 16 April 2020 / Revised: 21 May 2020 / Accepted: 25 May 2020 / Published: 27 May 2020
(This article belongs to the Special Issue Lab-on-a-Chip and Microfluidic Sensors)

Abstract

The use of functionalized magnetic particles for the detection or separation of multiple chemicals and biomolecules from biofluids continues to attract significant attention. After their incubation with the targeted substances, the beads can be magnetically recovered to perform analysis or diagnostic tests. Particle recovery with permanent magnets in continuous-flow microdevices has gathered great attention in the last decade due to the multiple advantages of microfluidics. As such, great efforts have been made to determine the magnetic and fluidic conditions for achieving complete particle capture; however, less attention has been paid to the effect of the channel geometry on the system performance, although it is key for designing systems that simultaneously provide high particle recovery and flow rates. Herein, we address the optimization of Y-Y-shaped microchannels, where magnetic beads are separated from blood and collected into a buffer stream by applying an external magnetic field. The influence of several geometrical features (namely cross section shape, thickness, length, and volume) on both bead recovery and system throughput is studied. For that purpose, we employ an experimentally validated Computational Fluid Dynamics (CFD) numerical model that considers the dominant forces acting on the beads during separation. Our results indicate that rectangular, long devices display the best performance as they deliver high particle recovery and high throughput. Thus, this methodology could be applied to the rational design of lab-on-a-chip devices for any magnetically driven purification, enrichment or isolation.

Keywords: particle magnetophoresis; CFD; cross section; chip fabrication

Korea Abstract

생체 유체에서 여러 화학 물질과 생체 분자의 검출 또는 분리를위한 기능화 된 자성 입자의 사용은 계속해서 상당한 관심을 받고 있습니다. 표적 물질과 함께 배양 한 후 비드를 자기 적으로 회수하여 분석 또는 진단 테스트를 수행 할 수 있습니다. 연속 흐름 마이크로 장치에서 영구 자석을 사용한 입자 회수는 마이크로 유체의 여러 장점으로 인해 지난 10 년 동안 큰 관심을 모았습니다. 

따라서 완전한 입자 포획을 달성하기 위한 자기 및 유체 조건을 결정하기 위해 많은 노력을 기울였습니다. 그러나 높은 입자 회수율과 유속을 동시에 제공하는 시스템을 설계하는 데있어 핵심이기는 하지만 시스템 성능에 대한 채널 형상의 영향에 대해서는 덜주의를 기울였습니다. 

여기에서 우리는 자기 비드가 혈액에서 분리되고 외부 자기장을 적용하여 버퍼 스트림으로 수집되는 YY 모양의 마이크로 채널의 최적화를 다룹니다. 비드 회수 및 시스템 처리량에 대한 여러 기하학적 특징 (즉, 단면 형상, 두께, 길이 및 부피)의 영향을 연구합니다. 

이를 위해 분리 중에 비드에 작용하는 지배적인 힘을 고려하는 실험적으로 검증 된 CFD (Computational Fluid Dynamics) 수치 모델을 사용합니다. 우리의 결과는 직사각형의 긴 장치가 높은 입자 회수율과 높은 처리량을 제공하기 때문에 최고의 성능을 보여줍니다. 

따라서 이 방법론은 자기 구동 정제, 농축 또는 분리를 위한 랩온어 칩 장치의 합리적인 설계에 적용될 수 있습니다.

Figure 1. (a) Top view of the microfluidic-magnetophoretic device, (b) Schematic representation of the channel cross-sections studied in this work, and (c) the magnet position relative to the channel location (Sepy and Sepz are the magnet separation distances in y and z, respectively).
Figure 1. (a) Top view of the microfluidic-magnetophoretic device, (b) Schematic representation of the channel cross-sections studied in this work, and (c) the magnet position relative to the channel location (Sepy and Sepz are the magnet separation distances in y and z, respectively).
Figure 2. (a) Channel-magnet configuration and (b–d) magnetic force distribution in the channel midplane for 2 mm, 5 mm and 10 mm long rectangular (left) and U-shaped (right) devices.
Figure 2. (a) Channel-magnet configuration and (b–d) magnetic force distribution in the channel midplane for 2 mm, 5 mm and 10 mm long rectangular (left) and U-shaped (right) devices.
Figure 3. (a) Velocity distribution in a section perpendicular to the flow for rectangular (left) and U-shaped (right) cross section channels, and (b) particle location in these cross sections.
Figure 3. (a) Velocity distribution in a section perpendicular to the flow for rectangular (left) and U-shaped (right) cross section channels, and (b) particle location in these cross sections.
Figure 4. Influence of fluid flow rate on particle recovery when the applied magnetic force is (a) different and (b) equal in U-shaped and rectangular cross section microdevices.
Figure 4. Influence of fluid flow rate on particle recovery when the applied magnetic force is (a) different and (b) equal in U-shaped and rectangular cross section microdevices.
Figure 5. Magnetic bead capture as a function of fluid flow rate for all of the studied geometries.
Figure 5. Magnetic bead capture as a function of fluid flow rate for all of the studied geometries.
Figure 6. Influence of (a) magnetic and fluidic forces (J parameter) and (b) channel geometry (θ parameter) on particle recovery. Note that U-2mm does not accurately fit a line.
Figure 6. Influence of (a) magnetic and fluidic forces (J parameter) and (b) channel geometry (θ parameter) on particle recovery. Note that U-2mm does not accurately fit a line.
Figure 7. Dependence of bead capture on the (a) functional channel volume and (b) particle residence time (tres). Note that in the curve fitting expressions V represents the functional channel volume and that U-2mm does not accurately fit a line.
Figure 7. Dependence of bead capture on the (a) functional channel volume and (b) particle residence time (tres). Note that in the curve fitting expressions V represents the functional channel volume and that U-2mm does not accurately fit a line.

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Full Text View
Fluid velocity magnitude including velocity vectors and blood volumetric fraction contours for scenario 3: (a,b) Magnet distance d = 0; (c,d) Magnet distance d = 1 mm.

Numerical Analysis of Bead Magnetophoresis from Flowing Blood in a Continuous-Flow Microchannel: Implications to the Bead-Fluid Interactions

Scientific Reports volume 9, Article number: 7265 (2019) Cite this article

Abstract

이 연구에서는 비드 운동과 유체 흐름에 미치는 영향에 대한 자세한 분석을 제공하기 위해 연속 흐름 마이크로 채널 내부의 비드 자기 영동에 대한 수치 흐름 중심 연구를 보고합니다.

수치 모델은 Lagrangian 접근 방식을 포함하며 영구 자석에 의해 생성 된 자기장의 적용에 의해 혈액에서 비드 분리 및 유동 버퍼로의 수집을 예측합니다.

다음 시나리오가 모델링됩니다. (i) 운동량이 유체에서 점 입자로 처리되는 비드로 전달되는 단방향 커플 링, (ii) 비드가 점 입자로 처리되고 운동량이 다음으로부터 전달되는 양방향 결합 비드를 유체로 또는 그 반대로, (iii) 유체 변위에서 비드 체적의 영향을 고려한 양방향 커플 링.

결과는 세 가지 시나리오에서 비드 궤적에 약간의 차이가 있지만 특히 높은 자기력이 비드에 적용될 때 유동장에 상당한 변화가 있음을 나타냅니다.

따라서 높은 자기력을 사용할 때 비드 운동과 유동장의 체적 효과를 고려한 정확한 전체 유동 중심 모델을 해결해야 합니다. 그럼에도 불구하고 비드가 중간 또는 낮은 자기력을 받을 때 계산적으로 저렴한 모델을 안전하게 사용하여 자기 영동을 모델링 할 수 있습니다.

Sketch of the magnetophoresis process in the continuous-flow microdevice.
Sketch of the magnetophoresis process in the continuous-flow microdevice.
Schematic view of the microdevice showing the working conditions set in the simulations.
Schematic view of the microdevice showing the working conditions set in the simulations.
Bead trajectories for different magnetic field conditions, magnet placed at different distances “d” from the channel: (a) d = 0; (b) d = 1 mm; (c) d = 1.5 mm; (d) d = 2 mm
Bead trajectories for different magnetic field conditions, magnet placed at different distances “d” from the channel: (a) d = 0; (b) d = 1 mm; (c) d = 1.5 mm; (d) d = 2 mm
Separation efficacy as a function of the magnet distance. Comparison between one-way and two-way coupling.
Separation efficacy as a function of the magnet distance. Comparison between one-way and two-way coupling.
(a) Fluid velocity magnitude including velocity vectors and (b) blood volumetric fraction contours with magnet distance d = 0 mm for scenario 1 (t = 0.25 s).
(a) Fluid velocity magnitude including velocity vectors and (b) blood volumetric fraction contours with magnet distance d = 0 mm for scenario 1 (t = 0.25 s).
luid velocity magnitude including velocity vectors and blood volumetric fraction contours for scenario 2: (a,b) Magnet distance d = 0 mm at t = 0.4 s; (c,d) Magnet distance d = 1 mm at t = 0.4 s.
luid velocity magnitude including velocity vectors and blood volumetric fraction contours for scenario 2: (a,b) Magnet distance d = 0 mm at t = 0.4 s; (c,d) Magnet distance d = 1 mm at t = 0.4 s.
Fluid velocity magnitude including velocity vectors and blood volumetric fraction contours for scenario 3: (a,b) Magnet distance d = 0; (c,d) Magnet distance d = 1 mm.
Fluid velocity magnitude including velocity vectors and blood volumetric fraction contours for scenario 3: (a,b) Magnet distance d = 0; (c,d) Magnet distance d = 1 mm.
Blood volumetric fraction contours. Scenario 1: (a) Magnet distance d = 0 and (b) Magnet distance d = 1 mm; Scenario 2: (c) Magnet distance d = 0 and (d) Magnet distance d = 1 mm; and Scenario 3: (e) Magnet distance d = 0 and (f) Magnet distance d = 1 mm.
Blood volumetric fraction contours. Scenario 1: (a) Magnet distance d = 0 and (b) Magnet distance d = 1 mm; Scenario 2: (c) Magnet distance d = 0 and (d) Magnet distance d = 1 mm; and Scenario 3: (e) Magnet distance d = 0 and (f) Magnet distance d = 1 mm.

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Author information

  1. Edward P. Furlani is deceased.

Affiliations

  1. Department of Chemical and Biomolecular Engineering, ETSIIT, University of Cantabria, Avda. Los Castros s/n, 39005, Santander, SpainJenifer Gómez-Pastora, Eugenio Bringas & Inmaculada Ortiz
  2. Flow Science, Inc, Santa Fe, New Mexico, 87505, USAIoannis H. Karampelas
  3. Department of Chemical and Biological Engineering, University at Buffalo (SUNY), Buffalo, New York, 14260, USAEdward P. Furlani
  4. Department of Electrical Engineering, University at Buffalo (SUNY), Buffalo, New York, 14260, USAEdward P. Furlani
Full Text View
Figure 3. (a) Velocity distribution in a section perpendicular to the flow for rectangular (left) and Ushaped (right) cross section channels, and (b) particle location in these cross sections.

Continuous-Flow Separation of Magnetic Particles from Biofluids: How Does the Microdevice Geometry Determine the Separation Performance?

Cristina González Fernández,1 Jenifer Gómez Pastora,2 Arantza Basauri,1 Marcos Fallanza,1 Eugenio Bringas,1 Jeffrey J. Chalmers,2 and Inmaculada Ortiz1,*
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생체 유체에서 자성 입자의 연속 흐름 분리 : 마이크로 장치 형상이 분리 성능을 어떻게 결정합니까?

Abstract

The use of functionalized magnetic particles for the detection or separation of multiple chemicals and biomolecules from biofluids continues to attract significant attention. After their incubation with the targeted substances, the beads can be magnetically recovered to perform analysis or diagnostic tests. Particle recovery with permanent magnets in continuous-flow microdevices has gathered great attention in the last decade due to the multiple advantages of microfluidics. As such, great efforts have been made to determine the magnetic and fluidic conditions for achieving complete particle capture; however, less attention has been paid to the effect of the channel geometry on the system performance, although it is key for designing systems that simultaneously provide high particle recovery and flow rates. Herein, we address the optimization of Y-Y-shaped microchannels, where magnetic beads are separated from blood and collected into a buffer stream by applying an external magnetic field. The influence of several geometrical features (namely cross section shape, thickness, length, and volume) on both bead recovery and system throughput is studied. For that purpose, we employ an experimentally validated Computational Fluid Dynamics (CFD) numerical model that considers the dominant forces acting on the beads during separation. Our results indicate that rectangular, long devices display the best performance as they deliver high particle recovery and high throughput. Thus, this methodology could be applied to the rational design of lab-on-a-chip devices for any magnetically driven purification, enrichment or isolation.

생체 유체에서 여러 화학 물질과 생체 분자의 검출 또는 분리를 위한 기능화된 자성 입자의 사용은 계속해서 상당한 관심을 받고 있습니다. 표적 물질과 함께 배양 한 후 비드는 자기적으로 회수되어 분석 또는 진단 테스트를 수행 할 수 있습니다.

연속 흐름 마이크로 장치에서 영구 자석을 사용한 입자 회수는 마이크로 유체의 여러 장점으로 인해 지난 10 년 동안 큰 관심을 모았습니다. 따라서 완전한 입자 포획을 달성하기 위한 자기 및 유체 조건을 결정하기 위해 많은 노력을 기울였습니다.

그러나 높은 입자 회수율과 유속을 동시에 제공하는 시스템을 설계하는데 있어 핵심이기는 하지만 시스템 성능에 대한 채널 형상의 영향에 대해서는 덜 주의를 기울였습니다.

여기에서 우리는 자기 비드가 혈액에서 분리되어 외부 자기장을 적용하여 버퍼 스트림으로 수집되는 Y-Y 모양의 마이크로 채널의 최적화를 다룹니다. 비드 회수 및 시스템 처리량에 대한 여러 기하학적 특징 (즉, 단면 형상, 두께, 길이 및 부피)의 영향을 연구합니다.

이를 위해 분리 중에 비드에 작용하는 지배적인 힘을 고려하는 실험적으로 검증된 CFD (Computational Fluid Dynamics) 수치 모델을 사용합니다.

우리의 결과는 직사각형의 긴 장치가 높은 입자 회수율과 높은 처리량을 제공하기 때문에 최고의 성능을 보여줍니다. 따라서 이 방법론은 자기 구동 정제, 농축 또는 분리를 위한 랩 온어 칩 장치의 합리적인 설계에 적용될 수 있습니다.

Keywords: particle magnetophoresis, CFD, cross section, chip fabrication

Figure 1 (a) Top view of the microfluidic-magnetophoretic device, (b) Schematic representation of the channel cross-sections studied in this work, and (c) the magnet position relative to the channel location (Sepy and Sepz are the magnet separation distances in y and z, respectively).
Figure 1 (a) Top view of the microfluidic-magnetophoretic device, (b) Schematic representation of the channel cross-sections studied in this work, and (c) the magnet position relative to the channel location (Sepy and Sepz are the magnet separation distances in y and z, respectively).
Figure 2. (a) Channel-magnet configuration and (b–d) magnetic force distribution in the channel midplane for 2 mm, 5 mm and 10 mm long rectangular (left) and U-shaped (right) devices.
Figure 2. (a) Channel-magnet configuration and (b–d) magnetic force distribution in the channel midplane for 2 mm, 5 mm and 10 mm long rectangular (left) and U-shaped (right) devices.
Figure 3. (a) Velocity distribution in a section perpendicular to the flow for rectangular (left) and Ushaped (right) cross section channels, and (b) particle location in these cross sections.
Figure 3. (a) Velocity distribution in a section perpendicular to the flow for rectangular (left) and Ushaped (right) cross section channels, and (b) particle location in these cross sections.
Figure 4. Influence of fluid flow rate on particle recovery when the applied magnetic force is (a) different and (b) equal in U-shaped and rectangular cross section microdevices.
Figure 4. Influence of fluid flow rate on particle recovery when the applied magnetic force is (a) different and (b) equal in U-shaped and rectangular cross section microdevices.
Figure 5. Magnetic bead capture as a function of fluid flow rate for all of the studied geometries.
Figure 5. Magnetic bead capture as a function of fluid flow rate for all of the studied geometries.
Figure 6. Influence of (a) magnetic and fluidic forces (J parameter) and (b) channel geometry (θ parameter) on particle recovery. Note that U-2mm does not accurately fit a line.
Figure 6. Influence of (a) magnetic and fluidic forces (J parameter) and (b) channel geometry (θ parameter) on particle recovery. Note that U-2mm does not accurately fit a line.
Figure 7. Dependence of bead capture on the (a) functional channel volume, and (b) particle residence time (tres). Note that in the curve fitting expressions V represents the functional channel volume and that U-2mm does not accurately fit a line.
Figure 7. Dependence of bead capture on the (a) functional channel volume, and (b) particle residence time (tres). Note that in the curve fitting expressions V represents the functional channel volume and that U-2mm does not accurately fit a line.
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Advances in Nanotechnology

Advances in Nanotechnology

This article was contributed by Prof. Edward Furlani and his students from the University at Buffalo, SUNY.

Microfluidics와 nanofluidics는 나노와 나노사이의 기능을 가진 재료와 시스템을 통한 유체 흐름의 과학과 기술을 포함하는 분야입니다. 최근 몇 년 사이에 이 분야의 연구는 재료 개발과 시스템의 급속한 발전된 유체공정의 독특한 이점으로 증가해 왔습니다. Microfluidic 및 nanofluidic 시스템은 화학 반응, 유체 가열, 혼합 및 감지와 같은 순차적 또는 다중화된 공정을 포함할 수 있는 응용 분야에서 마이크로 사이즈의 유체 유동은 매우 효율적이고 반복 가능하며 신속한 처리를 가능하게 합니다. 풀 라니 (Furlani) 교수 그룹의 연구는 새로운 공정 및 장치 개발에 대한 모델링 및 시뮬레이션을 보여줍니다. 이 연구의 대부분은 뉴턴 및 비 뉴턴 유체, 열 전달, 상변화 분석, 자유표면 및 다상분석, 유체와 관련된 유체 현상을 연구하기 위해 최첨단 전산 유체역학을 강조합니다. 매체 상호작용, 다공성 매체를 통한 유동, 완전히 결합된 유체구조 및 입자, 유체 상호작용에 대해 콜로이드. 국제 나노 기술 학술 대회에서 3 편의 논문이 발표될 예정입니다. 2014년 6월 15일부터 18 일까지 워싱턴 DC의 Gaylord National Hotel 및 Convention Center에서 개최됩니다. 이들은 버팔로 대학교 (University at Buffalo)에서 진행되는 획기적인 결과를 선보입니다. 여기에서는 이러한 작품의 미리 보기와 FLOW-3D로 생성된 시뮬레이션 결과 중 일부를 제시합니다.

Analysis of Stem Cell Culture Performance in a Microcarrier Bioreactor System

Koushik Ponnuru1, Jincheng Wu1, Preeti Ashok1, Emmanuel S. Tzanakakis1,3,4,5,6 and Edward P. Furlani1,2

1Dept. of Chemical and Biological Engineering, 2 Dept. of Electrical Engineering, 3Dept. of Biomedical Engineering, 4New York State Center of Excellence in Bioinformatics and Life Sciences, 5Western New York Stem Cell Culture and Analysis Center, 6Genetics, Genomics and Bioinformatics, University at Buffalo, SUNY

(left) Shear stress distribution along with velocity vectors in a cross sectional plane of the bioreactor running at 60 rpm; (right) Kolmogorov length scale distribution at the same plane under the same conditions.

CFD 기반 시뮬레이션과 실험결과의 조합으로 교반 탱크의 마이크로 캐리어 생물 반응기 시스템에서 세포 배양에 대한 난류 전단응력의 영향에 대한 분석을 제시합니다. Corning’s bench-scale spinner flask의 3D 계산 모델은 최첨단 CFD 소프트웨어 인 FLOW-3D를 사용하여 제작되었습니다. 임펠러 속도, 배양액 및 입자 크기와 같은 매개변수가 마이크로 캐리어 입자에 작용되는 전단응력에 미치는 영향을 CFD 분석을 사용하여 연구하였습니다. 이것은 세포가 겪는 정확한 전단 조건을 예측하고 세포의 손상을 방지하는 최적의 작동조건을 확인하는데 사용됩니다. 또한, 다원능 마커 Oct4, Sox2 및 Nanog를 운반하는 세포의 비율을 세포 계측법 및 정량적 PCR을 사용하여 측정함으로써 hPSCs의 다능성 전단효과를 연구합니다.

Numerical Analysis of Fully-Coupled Particle-Fluid Transport and Free-Flow Magnetophoretic Sorting in Microfluidic Systems

Chenxu Liu1, Xiaozheng Xue1 and Edward P. Furlani 1,2

1Dept. of Chemical and Biological Engineering, 2Dept. of Electrical Engineering, University at Buffalo, SUNY

Magnetic nanoparticle chaining and rotating following an external field and causing the mixing of two different molecular concentrations.

Magnetic 입자는 생체 의학 및 임상 진단 응용을 위해 생체 재료를 선택적으로 분리 및 분류하는 마이크로 유체시스템에 점점 더 많이 사용되고 있습니다. 그러한 시스템의 합리적인 설계에 사용될 수 있는 전산모델이 도입되었습니다. 이 모델은 자기 및 유체 역학적 힘, 완전 결합 입자 – 유체 상호 작용 및 입자의 자기 조립을 유도하는 자기 쌍극자와 쌍극자의 상호 작용을 비롯한 입자 수송에 대한 지배적 메커니즘을 고려합니다. 응용 프로그램을 통해 연속흐름 분리시스템 및 회전 조립 체인을 기반으로 하는 미세 유체 혼합프로세스로 시연됩니다.

Numerical Analysis of Laser Induced Photothermal Effects using Colloidal Plasmonic Nanostructures

Ioannis H. Karampelas1, Young Hwa Kim2 and Edward P. Furlani 1,2

1Dept. of Chemical and Biological Engineering, 2 Dept. of Electrical Engineering, University at Buffalo, SUNY

Photothermal heat cycle of a nanocage (a=50nm, t=5nm) (perspective 1/8 view): plot of nanocage temperature vs. time, pulse duration indicated by the red arrow and dashed line and inset plots showing various phases of the thermo -fluidic cycle: (a) nanobubble formation, (b) nanobubble (maximum size), (c) nanobubble collapse, (d) cooling.

Colloidal 귀금속 (plasmonic) 나노 구조는 나노 입자 합성에서부터 바이오 이미징 (bioimaging), 의학 요법 (medical therapy)에 이르기까지 다양한 광열 (photothermal) 분야에서 점점 더 많이 사용되고 있습니다. 많은 응용분야에서, 펄스 레이저는 plasmonic 공진 주파수에서 나노 구조를 사용하며, 이는 광자의 흡수 및 고도로 국부화된 파장필드의 향상을 가져옵니다. 원격 소스로부터 효율적인 나노 스케일 가열하는 것 외에도, 합성동안 나노 입자의 구조를 조정함으로써 근적외선 스펙트럼을 통한 공진 가열파장을 조정할 수 있습니다. 우리 그룹은 nanosecond-pulsed, laser-heated colloidal metallic nanoparticles 및 열 유체 거동을 예측하는 전산모델을 개발했습니다. 이 모델은 플라즈몬 공명, 입자에서 주변 유체로의 열 전달 및 균일한 기포 핵 형성을 유도하는 유체의 위상변화에서 나노 입자 내의 에너지 전환을 시뮬레이션 하는데 사용되었습니다. nanorods, nanotori, nanorings 및 nanocages 등 다양한 nanoparticle 형상이 연구되었습니다. 이 분석은 레이저 강도, 입사 파장, 편광, 펄스 지속 시간 및 나노 입자의 방향 및 모양과 같은 공정 매개 변수가 광열 공정을 최적화하도록 조정될 수 있음을 보여줍니다. Plasmonic nanoparticles는 악성 조직의 약물 치료, 약물 전달 및 생체치료에 사용됩니다.

Advances in Nanotechnology

Advances in Nanotechnology

This article was contributed by Prof. Edward Furlani and his students from the University at Buffalo, SUNY.

 

Microfluidics와 nanofluidics는 나노와 나노사이의 기능을 가진 재료와 시스템을 통한 유체 흐름의 과학과 기술을 포함하는 분야입니다. 최근 몇 년 사이에 이 분야의 연구는 재료 개발과 시스템의 급속한 발전된 유체공정의 독특한 이점으로 증가해 왔습니다. Microfluidic 및 nanofluidic 시스템은 화학 반응, 유체 가열, 혼합 및 감지와 같은 순차적 또는 다중화된 공정을 포함할 수 있는 응용 분야에서 마이크로 사이즈의 유체 유동은 매우 효율적이고 반복 가능하며 신속한 처리를 가능하게 합니다. 풀 라니 (Furlani) 교수 그룹의 연구는 새로운 공정 및 장치 개발에 대한 모델링 및 시뮬레이션을 보여줍니다. 이 연구의 대부분은 뉴턴 및 비 뉴턴 유체, 열 전달, 상변화 분석, 자유표면 및 다상분석, 유체와 관련된 유체 현상을 연구하기 위해 최첨단 전산 유체역학을 강조합니다. 매체 상호작용, 다공성 매체를 통한 유동, 완전히 결합된 유체구조 및 입자, 유체 상호작용에 대해 콜로이드. 국제 나노 기술 학술 대회에서 3 편의 논문이 발표될 예정입니다. 2014년 6월 15일부터 18 일까지 워싱턴 DC의 Gaylord National Hotel 및 Convention Center에서 개최됩니다. 이들은 버팔로 대학교 (University at Buffalo)에서 진행되는 획기적인 결과를 선보입니다. 여기에서는 이러한 작품의 미리 보기와 FLOW-3D로 생성된 시뮬레이션 결과 중 일부를 제시합니다.

Analysis of Stem Cell Culture Performance in a Microcarrier Bioreactor System

Koushik Ponnuru1, Jincheng Wu1, Preeti Ashok1, Emmanuel S. Tzanakakis1,3,4,5,6 and Edward P. Furlani1,2

1Dept. of Chemical and Biological Engineering, 2 Dept. of Electrical Engineering, 3Dept. of Biomedical Engineering, 4New York State Center of Excellence in Bioinformatics and Life Sciences, 5Western New York Stem Cell Culture and Analysis Center, 6Genetics, Genomics and Bioinformatics, University at Buffalo, SUNY

(left) Shear stress distribution along with velocity vectors in a cross sectional plane of the bioreactor running at 60 rpm; (right) Kolmogorov length scale distribution at the same plane under the same conditions.

CFD 기반 시뮬레이션과 실험결과의 조합으로 교반 탱크의 마이크로 캐리어 생물 반응기 시스템에서 세포 배양에 대한 난류 전단응력의 영향에 대한 분석을 제시합니다. Corning’s bench-scale spinner flask의 3D 계산 모델은 최첨단 CFD 소프트웨어 인 FLOW-3D를 사용하여 제작되었습니다. 임펠러 속도, 배양액 및 입자 크기와 같은 매개변수가 마이크로 캐리어 입자에 작용되는 전단응력에 미치는 영향을 CFD 분석을 사용하여 연구하였습니다. 이것은 세포가 겪는 정확한 전단 조건을 예측하고 세포의 손상을 방지하는 최적의 작동조건을 확인하는데 사용됩니다. 또한, 다원능 마커 Oct4, Sox2 및 Nanog를 운반하는 세포의 비율을 세포 계측법 및 정량적 PCR을 사용하여 측정함으로써 hPSCs의 다능성 전단효과를 연구합니다.

 

Numerical Analysis of Fully-Coupled Particle-Fluid Transport and Free-Flow Magnetophoretic Sorting in Microfluidic Systems

Chenxu Liu1, Xiaozheng Xue1 and Edward P. Furlani 1,2

1Dept. of Chemical and Biological Engineering, 2Dept. of Electrical Engineering, University at Buffalo, SUNY

Magnetic nanoparticle chaining and rotating following an external field and causing the mixing of two different molecular concentrations.

 

Magnetic 입자는 생체 의학 및 임상 진단 응용을 위해 생체 재료를 선택적으로 분리 및 분류하는 마이크로 유체시스템에 점점 더 많이 사용되고 있습니다. 그러한 시스템의 합리적인 설계에 사용될 수 있는 전산모델이 도입되었습니다. 이 모델은 자기 및 유체 역학적 힘, 완전 결합 입자 – 유체 상호 작용 및 입자의 자기 조립을 유도하는 자기 쌍극자와 쌍극자의 상호 작용을 비롯한 입자 수송에 대한 지배적 메커니즘을 고려합니다. 응용 프로그램을 통해 연속흐름 분리시스템 및 회전 조립 체인을 기반으로 하는 미세 유체 혼합프로세스로 시연됩니다.

 

Numerical Analysis of Laser Induced Photothermal Effects using Colloidal Plasmonic Nanostructures

Ioannis H. Karampelas1, Young Hwa Kim2 and Edward P. Furlani 1,2

1Dept. of Chemical and Biological Engineering, 2 Dept. of Electrical Engineering, University at Buffalo, SUNY

 

Photothermal heat cycle of a nanocage (a=50nm, t=5nm) (perspective 1/8 view): plot of nanocage temperature vs. time, pulse duration indicated by the red arrow and dashed line and inset plots showing various phases of the thermo -fluidic cycle: (a) nanobubble formation, (b) nanobubble (maximum size), (c) nanobubble collapse, (d) cooling.

Colloidal 귀금속 (plasmonic) 나노 구조는 나노 입자 합성에서부터 바이오 이미징 (bioimaging), 의학 요법 (medical therapy)에 이르기까지 다양한 광열 (photothermal) 분야에서 점점 더 많이 사용되고 있습니다. 많은 응용분야에서, 펄스 레이저는 plasmonic 공진 주파수에서 나노 구조를 사용하며, 이는 광자의 흡수 및 고도로 국부화된 파장필드의 향상을 가져옵니다. 원격 소스로부터 효율적인 나노 스케일 가열하는 것 외에도, 합성동안 나노 입자의 구조를 조정함으로써 근적외선 스펙트럼을 통한 공진 가열파장을 조정할 수 있습니다. 우리 그룹은 nanosecond-pulsed, laser-heated colloidal metallic nanoparticles 및 열 유체 거동을 예측하는 전산모델을 개발했습니다. 이 모델은 플라즈몬 공명, 입자에서 주변 유체로의 열 전달 및 균일한 기포 핵 형성을 유도하는 유체의 위상변화에서 나노 입자 내의 에너지 전환을 시뮬레이션 하는데 사용되었습니다. nanorods, nanotori, nanorings 및 nanocages 등 다양한 nanoparticle 형상이 연구되었습니다. 이 분석은 레이저 강도, 입사 파장, 편광, 펄스 지속 시간 및 나노 입자의 방향 및 모양과 같은 공정 매개 변수가 광열 공정을 최적화하도록 조정될 수 있음을 보여줍니다. Plasmonic nanoparticles는 악성 조직의 약물 치료, 약물 전달 및 생체치료에 사용됩니다.