
Citation: Cindy E. McKinney, Katherine M. Baumgarner. CRISPR engineering cardiometabolic disease models using human iPSC[J]. AIMS Cell and Tissue Engineering, 2018, 2(3): 185-202. doi: 10.3934/celltissue.2018.3.185
[1] | Nour Khlaifat, Ali Altaee, John Zhou, Yuhan Huang . A review of the key sensitive parameters on the aerodynamic performance of a horizontal wind turbine using Computational Fluid Dynamics modelling. AIMS Energy, 2020, 8(3): 493-524. doi: 10.3934/energy.2020.3.493 |
[2] | Azevedo Joaquim, Mendonça Fábio . Small scale wind energy harvesting with maximum power tracking. AIMS Energy, 2015, 2(3): 297-315. doi: 10.3934/energy.2015.3.297 |
[3] | Nelson Batista, Rui Melicio, Victor Mendes . Darrieus-type vertical axis rotary-wings with a new design approach grounded in double-multiple streamtube performance prediction model. AIMS Energy, 2018, 6(5): 673-694. doi: 10.3934/energy.2018.5.673 |
[4] | Sri Kurniati, Sudirman Syam, Arifin Sanusi . Numerical investigation and improvement of the aerodynamic performance of a modified elliptical-bladed Savonius-style wind turbine. AIMS Energy, 2023, 11(6): 1211-1230. doi: 10.3934/energy.2023055 |
[5] | Nathnael Bekele, Wondwossen Bogale . Parametric study of a diffuser for horizontal axis wind turbine power augmentation. AIMS Energy, 2019, 7(6): 841-856. doi: 10.3934/energy.2019.6.841 |
[6] | Salih Nawaf Akour, Mahmoud Azmi Abo Mhaisen . Parametric design analysis of elliptical shroud profile. AIMS Energy, 2021, 9(6): 1147-1169. doi: 10.3934/energy.2021053 |
[7] | Nadwan Majeed Ali, Handri Ammari . Design of a hybrid wind-solar street lighting system to power LED lights on highway poles. AIMS Energy, 2022, 10(2): 177-190. doi: 10.3934/energy.2022010 |
[8] | Ammar E. Ali, Nicholas C. Libardi, Sohel Anwar, Afshin Izadian . Design of a compressed air energy storage system for hydrostatic wind turbines. AIMS Energy, 2018, 6(2): 229-244. doi: 10.3934/energy.2018.2.229 |
[9] | Majid Deldar, Afshin Izadian, Sohel Anwar . Analysis of a hydrostatic drive wind turbine for improved annual energy production. AIMS Energy, 2018, 6(6): 908-925. doi: 10.3934/energy.2018.6.908 |
[10] | Pedro Neves, Morten Gleditsch, Cindy Bennet, Mathias Craig, Jon Sumanik-Leary . Assessment of locally manufactured small wind turbines as an appropriate technology for the electrification of the Caribbean Coast of Nicaragua. AIMS Energy, 2015, 3(1): 41-74. doi: 10.3934/energy.2015.1.41 |
Three trends in generating and providing electricity can be observed: Firstly, utilizing free primary, i.e., renewable energy, avoiding the cost for CO2-emission certificates and other end-of-lifetime waste disposal cost. Secondly, distributed small and volatile energy resources are combined into a small smart grid to improve reliability and robustness of decentralized grids. "Smart" in this context implies the control of the production and distribution utilizing smart meters, smart appliances, storage facilities like batteries and renewable energy resources. This can be of particular interest for rural electricity distribution networks and the future infrastructure required for electric vehicles. As an example, within its Seventh framework programme, the European Commission supported numerous projects like "Open Systems for Energy Services", "Smart … rural grid innovating resilient electricity distribution infrastructures, services and business models", "Scalable energy management infrastructure for aggregation of households" (FP7 [1]). Thirdly, in some cases the cost for feeding the power into a grid (or reversely drawing electricity from a grid) may exceed all other cost. A link-up to a public grid even may be economically impossible in remote areas.
This paper exclusively deals with small horizontal axis wind turbines (HAWT) for grid-independent or small smart grid systems, Figure 1. Obviously, the current and future demand provides enough support to sustain a significant number of manufacturers. In highly industrialized areas of the world, advanced methods allow manufacturing at high levels of quality and even mass production, whereas in other parts of the world simple manufacturing techniques are necessary, Figure 2. In the past ill-conceived small wind turbines have damaged the reputation for such machines. Today standards and testing institutions increasingly provide consumers with realistic and comparable performance ratings of competing products. Examples are the British small wind turbine standard [2], the German annual market survey on small wind turbines [3] and the Austrian small turbine test field Energie-For Schungspark Lichtenegg [4]. On the other hand, not all small turbine manufacturers, especially the small batch producers, may have access to the engineering capacity to design an efficient turbine.
A number of studies have been undertaken on wind turbines focusing on structural analysis, rotor dynamics and optimization of the shape of wind turbines. Yuan chang Chen et al. [19,20] and Wel Chen et al. [21], recently studied and reported extensively on the dynamics of the blade rotor and blade modeling. Many computational approaches have also found applications in aerodynamic design of wind turbines such as computational Fluid Dynamics (CFD), Wake Method and Blade Momentum (BEM) theory. BEM theory is widely used in aerodynamic design of wind turbines due to its simplicity and accuracy [26]. With blade optimization, power coefficient close to Betz limit of 59.2% can be realized with wind turbines.
On aerodynamics performance optimization, a number of studies are reported in the literature [22,23,24]. Ceyhan [22] undertook a study on the aerodynamic performance optimization of horizontal axis wind turbine blades using the BEM theory and genetic Algorithm. In the study, the chord and twist distribution were the key variables during the design and were optimized for optimum power production. Using differential evolution method, Clifton- Smith and wood [23], undertook a research with the aim of maximizing power coefficient and minimizing the starting time of small wind turbines blades. Liu et al. [24], developed an optimization method for wind turbines blades in order to maximize the annual energy output. A 7.5% increase in the annual energy output was realized in the study. Meng-Hsien [25], undertook a different study both numerically and experimentally on a small wind turbine blade, where one blade was designed using the BEM theory and the other was non-twisted blade. It was found out that the blade designed with BEM theory had higher coefficient of performance compared to the non-twisted blade.
Most wind turbines optimizations are conducted for wind turbines working in on design conditions. Wind turbines are exposed to different working conditions. In addition, matching the electric generator to the turbine performance characteristics curves is fundamental in ensuring the components are protected against extreme design effects.
Hence, the objective of the paper is to report a procedure for designing blades for small HAWTs. The turbine rotor with these blades should yield a shaft power as close as possible to theoretical maximum and match best to a given electric generator. The underlying theory is an advanced version of the well-established blade-element-momentum (BEM) theory, encoded in our own in-house MATLABTM code deapWind1 and validated extensively Kaufmann [5]. Eventually, as an exemplary case study, this paper describes the design of a small generator/battery charger with a 1 m diameter turbine rotor. Starting point is a one-year histogram of measured wind speed at the candidate site at Dedan Kimathi University of Technology in rural central Kenya. Upon design and manufacturing, a concluding wind tunnel experiment demonstrates how well the methodology works.
The turbine design methodology comprises three fundamental steps: (i) The design of the HAWT rotor, especially its profiled and twisted blades, (ii) the prediction of its performance characteristics in terms of shaft power, shaft torque and axial thrust force on the complete rotor, (iii) the overall power produced when "loaded" by the torque from the electric generator. Upon this last steps, it is straightforward to determine the overall electric power output for a given—say annual—wind speed histogram. Eventually, measures to achieve low cut-in wind speed and switch-off features for high winds have to be designed. The latter steps are out of the scope of this paper.
The blade design is based on the standard GLAUERT/SCHMITZ blade element momentum (BEM) theory as described for instance Gasch and Twele [6] or Gerhard et al. [7]). It is summarized only briefly; some more details are presented in the following section. The turbine design process starts with the specification of:
● the design wind speed far upstream of the turbine c0, design,
● the design rotor diameter Dtip ( = 2rtip),
● the density of the air ρ, the turbine will operate with, and
● the design tip speed ratio λdesign, of the turbine
λdesign≡utipc0,design=πDtipnc0,design | (1) |
with the circumferential velocity of the blade tip due to its rotation utip and the rotor speed n.
Essentially, c0, design and Dtip determine the power harvested by the turbine, and λdesign, its rotational speed for a given c0, design. Each blade is thought as a number of blade elements (BE) with a small radial size δr, stacked from root to tip, Figure 3 left. The BEs in a coaxial strip form themselves into an elementary blade cascade (CA). The most relevant geometrical parameters of each local BE are, Figure 3 right,
● the chord length, l,
● the pitch angle, γ,
● the angular distance, t, between two circumferentially adjacent BE's,
● the number of blades, B, and
● the solidity, σ, of the CA
σ≡ℓt=ℓ2πr/2πrBB | (2) |
Figure 4 left shows schematically a wind turbine with a boundary stream tube. The free stream wind speed far upstream, c0 is decelerated to c3 far down stream in the wake. c3 comprises a circumferential velocity component cu3 (i.e., the swirl) and an axial ( = meridional) cm3. The spatially averaged velocities at the entrance and exit plane of a CA are depicted in Figure 4 right. c's indicates absolute frame of reference, w's rotating frame of reference flow velocities; u is the circumferential velocity of the CA due to the rotation of the rotor. Again, c2 comprises a circumferential and a meridional velocity component cu2 and cm2, respectively. Instead of carrying on with dimensional quantities, the standard GLAUERT/SCHMITZ theory deals with the non-dimensional axial and tangential induction factors
a≡1−cmc0 with cm=c1=cm2 and a′≡−12cu2u. | (3a, b) |
For maximum power extraction from the wind the classic BETZ theory [8] requires
cm=12(c0+cm3) | (4) |
which is assumed to hold true, also within the GLAUERT/SCHMITZ theory. The outcome of the combined application of the axial and angular momentum conservation are design values of a and a' or in other words, the kinematics of the flow, each local BE ensures in order to provide maximum power output at a specified design wind speed, c0, design. The design values of a and a' are depicted in Figure 5. They are functions of the relative radial position r/rtip and λdesign of each BE considered.
The effect of any flow deflecting elementary blade cascade CA is attributed to lift and drag forces δL and δD from all BE's in the CA which are considered to be isolated infinite span airfoil sections aligned to the free stream incoming flow velocity w∞ with an angle of attack α, Figure 6 left. Key parameters of an airfoil sections are its lift coefficient CL and its drag/lift ratio ε, defined as
CL≡δL12ρw2∞ℓδr,ε≡CDCL with CD≡δD12ρw2∞ℓδr. | (5a, b, c) |
The airfoil shape is chosen by the designer, who also has to identify the CL(α) and CD(α) from wind tunnel data or other sources. The inflow velocity to each BE corresponds to the vector mean of the inlet and outlet relative velocities w1 and w2; its magnitude is
w∞=12√4c2m,1+(2u−cu2)2=c0√(1−adesign)2+(1+a′design)2(rrtipλdesign)2 | (6) |
and the flow angle
β∞=arctan(2cm,12u−cu2)=arctan(1−adesign1+a′designrtipr1λdesign) | (7) |
Eventually, this results in the solidity of each elementary blade cascade CA.
σdesign(rrtip)=4a′designrrtipλDCL,D(1−adesign)(1−εdesignrrtipλD1+a′design1−adesign)√1+(1+a′design1−adesign)2(rrtipλdesign)2. | (8) |
and the pitch angle
γdesign=β∞−αdesign. | (9) |
In our implementation the public domain software XFOIL (Drela, [9,10]) is integrated, which yields the airfoil lift and drag coefficients as a function of the chosen airfoil shape, angle of attack and the Reynolds number
Re=w∞ℓν, | (10) |
ν being the kinematic viscosity of the air.
Finally, the geometrical parameters σdesign, hence l for the chosen number B of rotor blades, and γdesign are sufficient to draw the blades and the complete rotor.
The goal of this analysis is the aerodynamic performance of the rotor with its geometry as found in the previous section. Among others the shaft power, the shaft torque and the axial thrust the rotor experiences due to the incoming wind are most relevant. These quantities are not only of interest at its design point λdesign, but also at all off-design operating points (i.e., at arbitrary values of λ≡πDtipn/πDtipnc0c0)—preferably in terms of the non-dimensional power, torque and thrust coefficients
CP≡PSρ2π4D2tipc30,CM≡MSρ2π8D3tipc20(=CPλ) and CT≡Faxρ2π4D2tipc20 | (11a, b, c) |
CP (λ), CM (λ) and CT (λ) are the non-dimensional performance characteristics of the turbine.
The method chosen for estimating the performance characteristics is again based on the blade element momentum (BEM) theory, although refined for reasons of accuracy. In contrast to the design method, the flow velocities, or synonymously a and a', and the angle of attack, α, hence lift and drag at each BE need to be computed for arbitrary values of λ. For the sake of completeness, some more steps, which have been omitted in section 2.1 are presented in this section. Full details can be found in Kaufmann [5].
Starting point is the conservation of axial momentum applied to the fluid in a coaxial strip from 0 to 3 as in Figure 4 left. It yields the axial force acting on the elementary blade cascade CA
δFax,CA=(c0−cm3)δ˙m. | (12) |
The mass flow rate through the CA is
δ˙m=ρcm1δA=ρcm12πrδr. | (13) |
The theoretical shaft power is obtained via EULER's turbine equation (i.e., conservation of angular momentum, friction ignored) as
δPth,CA=u(cu2−cu1)δ˙m |
Eventually, with the definitions of the induction factors Eq (3a, b), the CA thrust and power coefficients become;
CT,CA≡δFax,CAρc20πrδr=4a(1−a) | (14a) |
and
CP,th,CA≡δPth,CAρc30πrδr=4a′(1−a)(rrtipλ)2, | (14b) |
respectively. For any given value of λ, the two Eq (14a, b) bear the four unknown quantities CT, CA, CP, th, CA, a and a'. Additional equations are obtained by considering each CA as a set of isolated BE's experiencing a lift and a drag force. Referring to Figure 6 right the force components on one BE in the CA are
δFBE,ax=12ρw2∞(CLcosβ∞+CDsinβ∞)ℓδr | (15a) |
and
δFBE,u=12ρw2∞(CLsinβ∞−CDcosβ∞)ℓδr. | (15b) |
Eventually, the local thrust and power coefficient of the complete CA (consisting of B BE's) are obtained as
CT,CA(≡BδFax,BEρc20πrδr)=Bℓrtip2πrrtip((1−a)2+(rrtipλ)2(1+a′)2)(CLcosβ∞+CDsinβ∞) | (16a) |
and
CP,CA(≡BδPBEρc30πrδr)=Bℓrtip2πrrtip((1−a)2+(rrtipλ)2(1+a′)2)(CLcosβ∞−CDsinβ∞)rrtipλ, | (16b) |
respectively. Eventually, equating CT, CA from Eq (14a) and (16a) and CP, th, CA = CP, CA from Eq (14b) and (16b) yields two non-linear equations for the two unknowns a and a' for any λ considered:
4a(1−a)=Bℓrtip2πrrtip((1−a)2+(rrtipλ)2(1+a′)2)(CLcosβ∞+CDsinβ∞) | (17a) |
4a′(1−a)(rrtipλ)=Bℓrtip2π((1−a)2+(rrtipλ)2(1+a′)2)(CLcosβ∞−CDsinβ∞)λ | (17b) |
So far the analysis refers to one CA at r/rtip. The overall turbine thrust and power coefficients, i.e., the targeted characteristics of the complete rotor, are obtained by summation over all CA's:
CT(λ)(≡Fax(λ)12ρc20πD2tip4)=∑all CA'sCT,CA(λ)2πrδrπD2tip4 | (18a) |
CP,th(λ)(≡Pth(λ)12ρc30πD2tip4)=∑all CA'sCP,CA(λ)2πrδrπD2tip4 | (18b) |
A number of supplementary semi-empirical models are required to take into account effects that had been neglected so far. For instance, friction was partly excluded resulting in a theoretical CP, th. or: At the blade tip a radial flow component develops causing a tip vortex. And the root region of the blade in the vicinity of the hub is affected by vortex type secondary flows.
A customary model for the flow in the blade root and tip region is due to BETZ/PRANDTL and Glauert [11] (see e.g., a summary in Sorensen [12], Gasch and Twele [6], Moriaty and Hansen [13]). The thrust and power coefficients derived from momentum conservation (Eq (15a, b)) are modified by a factor F1 that gradually reduces the axial and tangential forces from those CA's which are located close to the blade tip and the hub:
CT,CA=F1⋅4a(1−a) | (19a) |
CP,th,CA=F1⋅4a′(1−a)(rrtipλ)2 | (19b) |
with
F1=4π2arccos(exp(B21−rrtiprrtipsinβ∞))⋅arccos(exp(B2rrtip−rhubrtiprrtipsinβ∞)) | (20) |
Since the flow "leaks" around the blade tip from pressure to suction side, lift and drag of airfoil sections in the tip region are different from what the infinite span polar data suggest. Shen et al. proposed in [14] a correction
F2=2πarccos[exp(−(exp(−0.125(Bλ−21))+0.1)B21−rrtipsinβ∞)] | (21) |
that is incorporated into Eq (17a, b):
CT,CA=Bℓ2πr((1−a)2+(rrtipλ)2(1+a′)2)⋅F2⋅(CLcosβ∞+CDsinβ∞) | (22a) |
CP,CA=Bℓ2πr((1−a)2+(rrtipλ)2(1+a′)2)⋅F2⋅(CLcosβ∞−CDsinβ∞)rrtipλ | (22b) |
In practice, as the axial induction factor a exceeds a critical value acrit≈ 1/3, complicated flow patterns result in much larger thrust coefficients as compared to the prediction by the basic BEM. Hence, Eq (14a) is replaced according to Buhl [15] by;
CT,CA=89+(4F1−409)a+(509−4F1)a2 for a≥0.4. | (23) |
As in the design part, the polar data of the infinite span airfoil sections are obtained via XFOIL. Post stall data, however, are obtained from Viterna et al. [16].
Some literature suggests solving the non-linear Eq (18a, b) with all their hidden supplementary model equations for a and a' explicitly (see e.g., the textbooks of Hansen [17] or Sørensen [12]). Since the authors encountered stability problems, an implicit scheme was set up [5]. It is encoded in our own inhouse MATLAB code, deapWind, which turned out to be very stable and reliable.
Once the non-dimensional performance characteristics are known, it is trivial converting them into dimensional:
n=λ⋅c0πDtip,PS(n)=CP(n)⋅ρ2π4D2tipc30MS(n)=CM(n)⋅ρ2π8D3tipc20,Fax(n)=CT(n)⋅ρ2π4D2tipc20 | (24a, b, c, d) |
It is worth noting that the value of Re stays the same only, if the size of the turbine Dtip is preserved and c0 equals the design wind speed c0, design. If the dimensional performance curves are required for other than the original design parameters, for instance for various wind speeds c0, two options are possible: Either eqs. (24a, b, c, d) are used neglecting the effect of Re, or running the performance prediction scheme as described in section 2.2 for each c0. The first option is faster and often sufficient for most practical purposes.
The results of two parametric studies targeting at small wind turbines illustrate the outcome of the design and performance prediction method. The first study shows the effect of the choice of λdesign, the second the impact of the number of blades B chosen for the rotor.
For a design wind speed c0, design = 6 m/s three rotors with each a diameter Dtip = 3.0 m and λdesign = 4.5, 7.5 and 10 are designed. NREL's S83x airfoils are chosen which were originally designed as "a family of quiet, thick, natural-laminar-flow airfoils for 1 to 3 m-diameter turbines" (SOMERS [18]). In particular, the root, middle and outer part of the blades are made from S835, S833 and S834 airfoils with a thickness/chord ratio of 21, 18 and 15%, respectively.
Computing airfoil lift and drag polars with XFOIL requires an assumption how the initially laminar boundary layer becomes turbulent in chord wise direction on the airfoil pressure and suction side. Particularly at low Re, which are typical for small wind turbines, the chord wise position of the laminar/turbulent transition depends on many details. This has a substantial effect on the predicted lift and drag. XFOIL offers the option "natural transition", where the position of laminar/turbulent transition is calculated using the eN-method with a chosen threshold amplification ratio of Ncrit. Ncrit is a measure of the quality of the flow incident to the airfoil with, 15 for very clean inflow, 1 for very "dirty" (corresponding to a free stream turbulence level of 2%) with the consequence of transition very close to the airfoil leading edge; in a second option, positions x/l ( = 0: leading edge, = 1: trailing edge) at the pressure and suction side are specified where transition is forced at the latest, Drela [10].
In these two parametric studies Ncrit is set to 1 with natural transition accordingly. The XFOIL-computed polars for the three BE's at hub, mid-span and blade tip are depicted in Figure 7. At each BE αdesign is chosen close to the most favorable minimum drag/lift ratio, ε. Table 1 shows the results for three-bladed rotors. Increasing values of λdesign lead to slimmer blades. As expected CP always reaches its peak close to λdesign but stays with approx. 0.42 the same. Note that the theoretical (BETZ) limit is 0.59. CM is affected severely by the choice of λdesign: The lower λdesign, the larger CM. The effect of λdesign on CT is mainly at λ > λdesign. The dimensional characteristics in the lower row throw further light on the properties of the different designs: Increasing λdesign shifts the peak power to larger rotor speeds, resulting in lower shaft torques. Nevertheless, the peak powers are very similar.
![]() |
A frequent but naive argument is to increase the number of blades for more power. The results of a variation of number B of blades chosen while keeping λdesign = 7.5 are compiled in Table 2. The performance characteristics are very similar, irrespective of the number of blades chosen. It must be noted that the spanwise distribution of solidity and blade pitch of all three rotors is kept the same as obtained by Eqs (9, 10). The minor effect of B stems from the impact of Re and those loss mechanisms that are a function of B. Hence, a criterion for the choice of B—among others—is the technical practicability of many slim or a few more massive blades, but not the power output.
![]() |
The objective of this exemplary case study is the design of a HAWT for a small generator/battery charger. The analysis involves matching the wind turbine rotor performance curves to the torque characteristic of the battery charger. Upon manufacturing, a concluding wind tunnel experiment validates the theoretical analysis.
Starting point is a one-year histogram of measured wind speed data collected at the candidate site, which is the campus of Dedan Kimathi University of Technology, Nyeri in central Kenya. The wind data were monitored from December 2016 to December 2017. The data includes the measured wind speeds and directions. Figure 8 visualizes the hours of occurrence of the ten (10) minutes averages of prevailing wind speeds at this site. Obviously, at this site wind speeds in the 4, 5 and 6 m/s wind speed bins are most prevalent. For the micro turbine to be designed c0, design = 6 m/s is chosen. The specified air density is ρ = 1.058 kg/m3, which corresponds to the altitude above sea level of the planned site for the turbine.
At any rotor speed n, the shaft torque provided by the turbine rotor must equal the torque required by the electric generator:
MS,Turb=MS,Gen | (25) |
The generator/charger unit characteristic MS, Gen(n), is determined experimentally by coupling the shaft of the electric generator to an auxiliary electric motor. The torque required by the generator is measured for any set speed via a torque measurement shaft in-between. The measured generator/charger characteristic for the controller status "Battery empty—charge" is the red curve in the middle graph of Figure 10.
It is worth to note that for maximum energy yield the generator/charger characteristic should be a quadratic parabola. Once parameterized correctly this would enable to operate the turbine at maximum CP for any c0. This strategy is provided by more advanced controllers or grid-connected turbines. In contrast, objective of this case study is the aerodynamic design of a rotor to the given generator/charger characteristic that ensures unambiguous rotor speed for any wind speed, keeps the rotor diameter as small as possible and provides a maximum annual energy output for the given wind resource.
The electric generator/battery charger unit consists of three main components:
● The electric generator; the turbine rotor is attached to the shaft of the generator without gearbox
● The battery to be charged
● The control unit, essentially comprising a 3-phase rectifier, a charge controller, a voltage threshold switch acting on a power relay which connects the generator to a load resistor rather to the charge controller, and a supply point to consume e.g., USB ports for charging wireless phones.
Its layout is depicted in Figure 9. The charge controller distinguishes between the bulk mode "Battery empty—charge with a current up to 2 A" and the float mode "Battery full—trickle charge with 0.6 A". Power provided by the turbine rotor but not absorbed by the battery is dumped via the load resistor. Voltage and current at the charge controller can be monitored via Bluetooth® on a smart phone.
Different turbine rotor types with λdesign ranging from 3.0 to 5.0 and Dtip from 0.8 m to 1.3 m have been designed. The hub diameter is fixed to 0.19 m in order to fit to the outer diameter of the electric generator. Mainly for low manufacturing cost, the rotor is two-bladed. Laminar/turbulent transition was fixed to x/l = 0.02 on each BE suction side and 0.05 on the pressure side, assuming that the foreseen method of manufacture does not yield to perfect smooth and precise blade surfaces, with the consequence of laminar/turbulent transition close to the blade leading edge.
Relevant parameters of some of the rotor/charger assemblies are compiled in Table 3. One criterion for selection is the annual energy output at the shaft of the rotor
AEOS=∑all k binsCP,kρ2π4D2tipc30,k⋅Δtk | (26) |
Dtip[m] | λ | AEOS[kWh/a] | n at c0 = 6 m/s [rpm] | n at c0 = 12 m/s [rpm] | Fax at c0 = 12 m/s [N] | Remarks | |
1 | 0.8 | 4.0 | 108 | 500 | 1990 | 28 | lowest AEOS, glancing intersection of torque curves at high c0 may yield ambiguous rotational speeds |
2 | 1.0 | 3.0 | 132 | 530 | 1250 | 31 | low AEOS |
3 | 1.0 | 4.0 | 162 | 560 | 1690 | 44 | best compromise |
4 | 1.0 | 5.0 | 176 | 580 | 1990 | 51 | Largest n @ c0 = 12 m/s largest Dtip |
5 | 1.2 | 4.0 | 181 | 591 | 1470 | 64 | large Dtip, large T @ c0 = 12 m/s [N] |
6 | 1.3 | 4.0 | 168 | 591 | 1360 | 73 | large Dtip, largest T @ c0 = 12 m/s [N] |
which translates into the electric energy output when subtracting all electric losses. Other criterions are the rotor speed at the most prevalent wind speed 6 m/s and at high winds, here 12 m/s. Low rotor speeds are easier to handle and produce less noise. Also, the axial thrust is a criterion. Large axial thrust forces require more expensive structures to hold the turbine.
The rotor ultimately selected has the parameters Dtip = 1 m and λdesign = 4.0. Important geometrical parameters of each BE are compiled in Table 4. Figure 10 illustrates the synthesis of the measured generator characteristic ("mode Battery empty—charge", red line with red crosses in the middle diagram) and this rotor at different wind speeds; the black circles indicate the operating points of the complete assembly. Figure 8 right shows the predicted shaft energy output at each wind speed bin of the turbine/generator assembly.
BE | r/rtip | L [m] | γ [°] |
1 | 0.190 | 0.306 | 29.178 |
2 | 0.248 | 0.300 | 24.236 |
3 | 0.306 | 0.284 | 20.326 |
4 | 0.364 | 0.265 | 17.223 |
5 | 0.421 | 0.246 | 14.738 |
6 | 0.479 | 0.229 | 12.721 |
7 | 0.537 | 0.214 | 11.069 |
8 | 0.595 | 0.201 | 9.693 |
9 | 0.653 | 0.189 | 8.540 |
10 | 0.711 | 0.179 | 7.562 |
11 | 0.769 | 0.170 | 6.726 |
12 | 0.826 | 0.162 | 6.006 |
13 | 0.884 | 0.155 | 5.382 |
14 | 0.942 | 0.149 | 4.835 |
15 | 1.000 | 0.143 | 4.358 |
The software deapWind yields the BE coordinates of 15 BE's along the span. From that a 3D CAD model and 2D technical drawings are established. For manufacturing a traditional technique is chosen that requires a standard carpenter's workshop only: The blades are carved from a high quality wood block with the help of a grid of drill holes, Figure 11. The perpendicular distance from each of the grid point on the blade surface to the surface of the block is measured in the 3D CAD model. This is performed for both sides of the blade. This distance is the depth of the 8 mm holes to be drilled. The drilling of the holes is to ensure that the correct depth of material removal is achieved. It acts as a guide on the maximum depth of material removal obtain the blade profile. The material was removed manually to almost the end of the drilled holes that mark the surface of the blades. The finishing was done using rough and fine sand papers. In order to achieve the finest surface finish, the blades were applied with wood filler, allowed to dry up, then filed using the finest sand papers. At the hub, the material removal and smoothening was achieved by use of rough and fine wood files.
For the experiments, the rotor was mounted upstream on the drive train, comprising a steel shaft, separate bearings and the electric generator. The battery charger was connected to the generator. The complete assembly was tested in the University of Siegen wind tunnel. This wind tunnel is a closed-circuit type allowing a maximum wind speed of the wind tunnel of 70 m/s at a turbulence intensity less than 0.35%. Figure 12 shows the experimental set up in the wind tunnel (all dimensions are in millimeters). The wind speed was measured using a propeller anemometer, the rotational speed with an optical laser tachometer. The wind speed was varied in steps. Upon steady-state operation, the rotational speed of the turbine was recorded. It is important to note that the air density in the wind tunnel lab was approx. ρ = 1.17 kg/m3, resulting in different dimensional turbine performance characteristics as compared to those in the previous sections. This has been taken into account. Ideally, the shaft power of the rotor would have been measured. This was not possible. The electric power was measured instead.
A comparison of the rotational speed of the complete rotor/charger assembly in bulk mode ("Battery empty—charge") at different wind speeds is depicted in Figure 13 left. Obviously, the "loading" of the rotor by the electric generator is very close to what was expected from the previous analysis. This partly validates the aerodynamic rotor design. The difference of predicted rotor shaft power and the measured electric power, Figure 13 right, is an indicator for the electric overall efficiency
ηel≡Pel/PelPSPS | (27) |
of the complete assembly. A major loss is attributed to the electric generator. Its electric efficiency characteristic was measured separately—similarly as the complete generator/charger/battery characteristics before, and is depicted for n = 560 rpm in Figure 14. At PS = 29 W (corresponding to c0 = 6 m/s) the generator's electric efficiency is 47%. Other electric losses stem from the battery charger, and—up from c0 = 7.5 m/s—then active load resistor for protecting the battery. Eventually, fundamental errors due to blockage of the wind tunnel test section by the rotor and a potentially reduced turbine efficiency due to the manual manufacture may account for a lower than predicted power coefficient of the rotor. Note, that the turbine shaft power could not be measured directly during the wind tunnel measurement campaign.
An analytical method for the aerodynamic design of horizontal of axis wind turbines including performance prediction was described. The underlying theory for design and shaft power and thrust force prediction is an advanced version of the well-established blade-element-momentum (BEM) theory, encoded in our own in-house MATLABTM code deapWind. The procedure yields the geometry of the aerodynamically profiled and twisted blades which are designed to yield maximum power output for a given design wind speed.
Two parametric studies illustrated typical outcomes of the design and performance prediction method: (i) A variation of the design tip speed ratio λdesign; the higher λdesign the larger the rotational speed at a given wind speed and the smaller the torque. Hence, the choice of λdesign allows to match the turbine to sites with either low or high mean wind speeds. Moreover, the higher λdesign the slimmer the blades, which may have an impact on manufacture and structural health. (ii) A variation of the number of blades B in a rotor, while keeping λdesign constant; as expected the results proved that the non-dimensional turbine performance characteristics are nearly independent of the number of blades chosen; a minor effect of B stems from the impact of Re and the various aerodynamic loss mechanisms taken into account in the advanced blade-element-momentum theory. Hence, a criterion for the choice of B—among others—is the technical practicability of many slim or a few more massive blades, but not the power output as occasionally naively proposed.
Eventually, a more comprehensive case study dealt with a micro wind turbine for a small low cost generator/battery charger. A goal was to foresee turbine blades of high aerodynamic quality that can be manufactured with techniques available in less developed regions of the world. The analysis involved matching the turbine rotor performance curves to the torque characteristic of the battery charger, manufacture of the rotor and a concluding wind tunnel experiment for validation of the theoretical analysis. Starting point was a one-year histogram of measured wind speed data collected at the candidate site in rural central Kenya. Prior to the wind turbine design, the generator torque/speed characteristic was determined experimentally in a laboratory by coupling the shaft of the electric generator to an auxiliary electric motor. The torque was measured for any set speed via a torque measurement shaft in-between. The generator was connected to the charge controller and empty battery. The interplay of various turbine rotors and the drive train/battery charging was simulated. Criterions for selection of the rotor were the annual energy output at the shaft, the rotor speed at the most prevalent wind speed and at high winds, and the axial thrust exerted on the rotor by the wind. A blade manufacturing technique was chosen that requires a standard carpenter's workshop only. Compared to 3D printing and additive manufacturing, this technology is simple, cheap and accessible to less developed nations for developing wind turbines for providing energies to communities off the national grids. Finally, the complete rotor/drive train//battery charger assembly was tested in the University of Siegen wind tunnel. The rotational speed for various wind speeds are very close to what was expected from the previous analysis. This partly validates the aerodynamic rotor design. The difference of predicted rotor shaft power and measured electric generator power. i.e., the value of the overall electric efficiency, is mainly attributed to the electric losses in the generator and the battery charger circuit.
Upcoming efforts must provide for passive yaw and storm protection. A tail vane can act as a passive yaw system, or a downwind installation of the rotor. The predicted thrust may facilitate the design of any mechanical tilt mechanism and eventually dimensioning of the tower. Safe cut-out at high winds and early cut-in of the turbine can be assisted by an advanced electric control.
S. K. Musau designed and manufactured the micro turbine described in the case study. K. Stahl assisted in designing the turbine including the electric part and guided the wind tunnel experiments and data evaluation. K. Volkmer created the software deapWind by linking an extended version of an existing wind turbine design method with N. Kaufmann's turbine performance prediction procedure. Th. Carolus is the leader for the project and compiled the manuscript with the help of all co-authors.
The project was partly funded by the Erasmus+ Programme of the European Union (Key Action 107 Mobility with partner countries). Partner were the University of Siegen and Dedan Kimathi University of Technology, Kenya. The authors gratefully appreciate this financial support. The authors also want to thank S. Kreklow and T. Schönemann from the University of Siegen electronic workshop for the design of the electronic circuits, J. Janssens from the mechanical workshop for the assistance in manufacturingthe turbine blades, A. Bald for providing the test opportunity of the wind turbine in the University Siegen aeroacoustic wind tunnel and B. Homrighausen supervising the complete project. Special thanks also Harrison T. Ngetha for his support.
To the best of our knowledge, there is no conflict of interest.
[1] |
Orban JC, Walrave Y, Mongardon N, et al. (2017) Causes and characteristics of death in intensive care units. Anesthesiology 126: 882–889. doi: 10.1097/ALN.0000000000001612
![]() |
[2] |
Lovett M, Lee K, Edwards A, et al. (2009) Vascularization strategies for tissue engineering. Tissue Eng Part B Rev 15: 353–370. doi: 10.1089/ten.teb.2009.0085
![]() |
[3] |
Griffith CK, Miller C, Sainson RCA, et al. (2005) Diffusion limits of an in vitro thick prevascularized tissue. Tissue Eng 11: 257–266. doi: 10.1089/ten.2005.11.257
![]() |
[4] |
Jain RK, Au P, Tam J, et al. (2005) Engineering vascularized tissue. Nat Biotechnol 23: 821–823. doi: 10.1038/nbt0705-821
![]() |
[5] |
Phelps EA, García AJ (2010) Engineering more than a cell: Vascularization strategies in tissue engineering. Curr Opin Biotechnol 21: 704–709. doi: 10.1016/j.copbio.2010.06.005
![]() |
[6] |
Bertassoni LE, Cecconi M, Manoharan V, et al. (2014) Hydrogel bioprinted microchannel networks for vascularization of tissue engineering constructs. Lab Chip 14: 2202–2211. doi: 10.1039/C4LC00030G
![]() |
[7] |
Rouwkema J, Rivron NC, van Blitterswijk CA (2008) Vascularization in tissue engineering. Trends Biotechnol 26: 434–441. doi: 10.1016/j.tibtech.2008.04.009
![]() |
[8] |
Ikada Y (2006) Challenges in tissue engineering. J R Soc Interface 3: 589–601. doi: 10.1098/rsif.2006.0124
![]() |
[9] |
Griffith LG, Naughton G (2002) Tissue engineering--current challenges and expanding opportunities. Science 295: 1009–1014. doi: 10.1126/science.1069210
![]() |
[10] |
Kang HW, Lee SJ, Ko IK, et al. (2016) A 3D bioprinting system to produce human-scale tissue constructs with structural integrity. Nat Biotechnol 34: 312–319. doi: 10.1038/nbt.3413
![]() |
[11] |
Berthiaume F, Maguire TJ, Yarmush ML (2011) CH02CH19-Yarmush. Annu Rev Chem Biomol Eng 2: 403–430. doi: 10.1146/annurev-chembioeng-061010-114257
![]() |
[12] |
Hollister SJ (2005) Porous scaffold design for tissue engineering. Nat Mater 4: 518–524. doi: 10.1038/nmat1421
![]() |
[13] |
Chan BP, Leong KW (2008) Scaffolding in tissue engineering: general approaches and tissue-specific considerations. Eur Spine J 17: 467–479. doi: 10.1007/s00586-008-0745-3
![]() |
[14] |
Novosel EC, Kleinhans C, Kluger PJ (2011) Vascularization is the key challenge in tissue engineering. Adv Drug Deliv Rev 63: 300–311. doi: 10.1016/j.addr.2011.03.004
![]() |
[15] |
Zhao X, Liu L, Wang J, et al. (2016) In vitro vascularization of a combined system based on a 3D printing technique. J Tissue Eng Regen Med 10: 833–842. doi: 10.1002/term.1863
![]() |
[16] | Pashneh-Tala S, MacNeil S, Claeyssens F (2015) The tissue-engineered vascular graft-past, present, and future. Tissue Eng Part B Rev 22. |
[17] |
O'Brien FJ (2011) Biomaterials & scaffolds for tissue engineering. Mater Today 14: 88–95. doi: 10.1016/S1369-7021(11)70058-X
![]() |
[18] | He Y, Lu F (2016) Development of synthetic and natural materials for tissue engineering applications using adipose stem cells. Stem Cells Int 2016: 5786257. |
[19] |
Kim JJ, Hou L, Yang G, et al. (2017) Microfibrous scaffolds enhance endothelial differentiation and organization of induced pluripotent stem cells. Cell Mol Bioeng 10: 417–432. doi: 10.1007/s12195-017-0502-y
![]() |
[20] | Plunkett N, O'Brien FJ (2010) IV.3. Bioreactors in tissue engineering. Stud Health Technol Inform 152: 214–230. |
[21] |
Kolesky DB, Homan KA, Skylar-Scott MA, et al. (2016) Three-dimensional bioprinting of thick vascularized tissues. Proc Natl Acad Sci 113: 3179–3184. doi: 10.1073/pnas.1521342113
![]() |
[22] | Kolte D, McClung JA, Aronow WS (2016) Vasculogenesis and angiogenesis. Transl Res in Coron Artery Dis 49–65. |
[23] |
Risau W (1997) Mechanisms of angiogenesis. Nat 386: 671–674. doi: 10.1038/386671a0
![]() |
[24] |
Carmeliet P, Jain RK (2000) Angiogenesis in cancer and other diseases. Nat 407: 249–257. doi: 10.1038/35025220
![]() |
[25] |
Carmeliet P (2000) Mechanisms of angiogenesis and arteriogenesis. Nat Med 6: 389–395. doi: 10.1038/74651
![]() |
[26] | Lanza RP, Langer RS, Vacanti J (2014) Principles of Tissue Engineering. Elsevier. |
[27] | Gao Y (2017) Biology of Vascular Smooth Muscle: Vasoconstriction and Dilatation, Singapore: Springer Singapore. |
[28] | Ardalani H, Assadi AH, Murphy WL (2014) Structure, function, and development of blood vessels: lessons for tissue engineering. In, Engineering in Translational Medicine, London: Springer London, 155–182. |
[29] | Rhodin JAG (1980) Architecture of the vessel wall. In, Comprehensive Physiology, Hoboken: John Wiley & Sons, 1–31. |
[30] |
Kossmann CE, Palade GE (1961) Blood capillaries of the heart and other organs. Circulation 24: 368–384. doi: 10.1161/01.CIR.24.2.368
![]() |
[31] |
Burton AC (1954) Relation of structure to function of the tissues of the wall of blood vessels. Physiol Rev 34: 619–642. doi: 10.1152/physrev.1954.34.4.619
![]() |
[32] |
Yamamoto H, Ehling M, Kato K, et al. (2015) Integrin β1 controls VE-cadherin localization and blood vessel stability. Nat Commun 6: 6429. doi: 10.1038/ncomms7429
![]() |
[33] | Okabe E, Todoki K, Ito H (1990) Microcirculation: function and regulation in microvasculature. In, Dynamic Aspects of Dental Pulp, Dordrecht: Springer Netherlands, pp 151–166. |
[34] | Ji S, Guvendiren M (2017) Recent advances in bioink design for 3D bioprinting of tissues and organs. Front Bioeng Biotechnol 5: 23. |
[35] |
Hölzl K, Lin S, Tytgat L, et al. (2016) Bioink properties before, during and after 3D bioprinting. Biofabrication 8: 032002. doi: 10.1088/1758-5090/8/3/032002
![]() |
[36] |
Hospodiuk M, Dey M, Sosnoski D, et al. (2017) The bioink: A comprehensive review on bioprintable materials. Biotechnol Adv 35: 217–239. doi: 10.1016/j.biotechadv.2016.12.006
![]() |
[37] |
Smith CM, Stone AL, Parkhill RL, et al. (2004) Three-dimensional bioassembly tool for generating viable tissue-engineered constructs. Tissue Eng 10: 1566–1576. doi: 10.1089/ten.2004.10.1566
![]() |
[38] |
Chen CY, Barron JA, Ringeisen BR (2006) Cell patterning without chemical surface modification: cell–cell interactions between printed bovine aortic endothelial cells (BAEC) on a homogeneous cell-adherent hydrogel. Appl Surf Sci 252: 8641–8645. doi: 10.1016/j.apsusc.2005.11.088
![]() |
[39] |
Gao Q, He Y, Fu J, et al. (2015) Coaxial nozzle-assisted 3D bioprinting with built-in microchannels for nutrients delivery. Biomater 61: 203–215. doi: 10.1016/j.biomaterials.2015.05.031
![]() |
[40] |
Norotte C, Marga FS, Niklason LE, et al. (2009) Scaffold-free vascular tissue engineering using bioprinting. Biomaterials 30: 5910–5917. doi: 10.1016/j.biomaterials.2009.06.034
![]() |
[41] |
Zhang YS, Arneri A, Bersini S, et al. (2016) Bioprinting 3D microfibrous scaffolds for engineering endothelialized myocardium and heart-on-a-chip. Biomater 110: 45–59. doi: 10.1016/j.biomaterials.2016.09.003
![]() |
[42] |
Lee VK, Kim DY, Ngo H, et al. (2014) Creating perfused functional vascular channels using 3D bio-printing technology. Biomater 35: 8092–8102. doi: 10.1016/j.biomaterials.2014.05.083
![]() |
[43] | Yin Yu, Ozbolat IT (2014) Tissue strands as "bioink" for scale-up organ printing. Conf Proc IEEE Eng Med Biol Soc 2014: 1428–1431. |
[44] |
Wilkens CA, Rivet CJ, Akentjew TL, et al. (2016) Layer-by-layer approach for a uniformed fabrication of a cell patterned vessel-like construct. Biofabrication 9: 015001. doi: 10.1088/1758-5090/9/1/015001
![]() |
[45] |
Cui X, Boland T (2009) Human microvasculature fabrication using thermal inkjet printing technology. Biomater 30: 6221–6227. doi: 10.1016/j.biomaterials.2009.07.056
![]() |
[46] |
Darland DC, Massingham LJ, Smith SR, et al. (2003) Pericyte production of cell-associated VEGF is differentiation-dependent and is associated with endothelial survival. Dev Biol 264: 275–288. doi: 10.1016/j.ydbio.2003.08.015
![]() |
[47] |
Korff T, Kimmina S, Martiny-Baron G, et al. (2001) Blood vessel maturation in a 3-dimensional spheroidal coculture model: direct contact with smooth muscle cells regulates endothelial cell quiescence and abrogates VEGF responsiveness. FASEB J 15: 447–457. doi: 10.1096/fj.00-0139com
![]() |
[48] |
Lee VK, Lanzi AM, Ngo H, et al. (2014) Generation of Multi-scale Vascular Network System Within 3D Hydrogel Using 3D Bio-printing Technology. Cell Mol Bioeng 7: 460–472. doi: 10.1007/s12195-014-0340-0
![]() |
[49] |
Jia W, Gungor-Ozkerim PS, Zhang YS, et al. (2016) Direct 3D bioprinting of perfusable vascular constructs using a blend bioink. Biomater 106: 58–68. doi: 10.1016/j.biomaterials.2016.07.038
![]() |
[50] |
Jang J, Park HJ, Kim SW, et al. (2017) 3D printed complex tissue construct using stem cell-laden decellularized extracellular matrix bioinks for cardiac repair. Biomater 112: 264–274. doi: 10.1016/j.biomaterials.2016.10.026
![]() |
[51] |
Jia J, Richards DJ, Pollard S, et al. (2014) Engineering alginate as bioink for bioprinting. Acta Biomater 10: 4323–4331. doi: 10.1016/j.actbio.2014.06.034
![]() |
[52] |
Das S, Pati F, Choi YJ, et al. (2015) Bioprintable, cell-laden silk fibroin–gelatin hydrogel supporting multilineage differentiation of stem cells for fabrication of three-dimensional tissue constructs. Acta Biomater 11: 233–246. doi: 10.1016/j.actbio.2014.09.023
![]() |
[53] |
Blaeser A, Duarte Campos DF, Puster U, et al. (2016) Controlling shear stress in 3D bioprinting is a key factor to balance printing resolution and stem cell integrity. Adv Healthc Mater 5: 326–333. doi: 10.1002/adhm.201500677
![]() |
[54] |
Hipp J, Atala A (2008) Sources of stem cells for regenerative medicine. Stem Cell Rev 4: 3–11. doi: 10.1007/s12015-008-9010-8
![]() |
[55] |
Wilson KD, Wu JC (2015) Induced pluripotent stem cells. JAMA 313: 1613. doi: 10.1001/jama.2015.1846
![]() |
[56] |
Wong CW, Chen YT, Chien CL, et al. (2018) A simple and efficient feeder-free culture system to up-scale iPSCs on polymeric material surface for use in 3D bioprinting. Mater Sci Eng C 82: 69–79. doi: 10.1016/j.msec.2017.08.050
![]() |
[57] |
Faulkner-Jones A, Fyfe C, Cornelissen DJ, et al. (2015) Bioprinting of human pluripotent stem cells and their directed differentiation into hepatocyte-like cells for the generation of mini-livers in 3D. Biofabrication 7: 044102. doi: 10.1088/1758-5090/7/4/044102
![]() |
[58] |
Ma X, Qu X, Zhu W, et al. (2016) Deterministically patterned biomimetic human iPSC-derived hepatic model via rapid 3D bioprinting. Proc Natl Acad Sci 113: 2206–2211. doi: 10.1073/pnas.1524510113
![]() |
[59] |
Miller JS, Stevens KR, Yang MT, et al. (2012) Rapid casting of patterned vascular networks for perfusable engineered three-dimensional tissues. Nat Mater 11: 768–774. doi: 10.1038/nmat3357
![]() |
[60] |
Kolesky DB, Truby RL, Gladman AS, et al. (2014) 3D bioprinting of vascularized, heterogeneous cell-laden tissue constructs. Adv Mater 26: 3124–3130. doi: 10.1002/adma.201305506
![]() |
[61] | Sukmana I (2012) Microvascular guidance: a challenge to support the development of vascularised tissue engineering construct. The Sci World J 2012: 201352. |
[62] |
Kim JA, Kim HN, Im SK, et al. (2015) Collagen-based brain microvasculature model in vitro using three-dimensional printed template. Biomicrofluidics 9: 024115. doi: 10.1063/1.4917508
![]() |
[63] | Muscari C, Giordano E, Bonafè F, et al. (2014) Strategies affording prevascularized cell-based constructs for myocardial tissue engineering. Stem Cells Int 2014: 434169. |
[64] |
Bogorad MI, DeStefano J, Karlsson J, et al. (2015) Review: in vitro microvessel models. Lab Chip 15: 4242–4255. doi: 10.1039/C5LC00832H
![]() |
[65] |
Moon JJ, West JL (2008) Vascularization of engineered tissues: approaches to promote angio-genesis in biomaterials. Curr Top Med Chem 8: 300–310. doi: 10.2174/156802608783790983
![]() |
[66] |
Yang P, Huang X, Shen J, et al. (2013) Development of a new pre-vascularized tissue-engineered construct using pre-differentiated rADSCs, arteriovenous vascular bundle and porous nano-hydroxyapatide-polyamide 66 scaffold. BMC Musculoskelet Disord 14: 318. doi: 10.1186/1471-2474-14-318
![]() |
[67] |
Zhu W, Qu X, Zhu J, et al. (2017) Direct 3D bioprinting of prevascularized tissue constructs with complex microarchitecture. Biomater 124: 106–115. doi: 10.1016/j.biomaterials.2017.01.042
![]() |
[68] |
Mirabella T, MacArthur JW, Cheng D, et al. (2017) 3D-printed vascular networks direct therapeutic angiogenesis in ischaemia. Nat Biomed Eng 1: 0083. doi: 10.1038/s41551-017-0083
![]() |
[69] |
Gelber MK, Hurst G, Comi TJ, et al. (2018) Model-guided design and characterization of a high-precision 3D printing process for carbohydrate glass. Addit Manuf 22: 38–50. doi: 10.1016/j.addma.2018.04.026
![]() |
[70] |
Xu C, Lee W, Dai G, et al. (2018) Highly elastic biodegradable single-network hydrogel for cell printing. ACS Appl Mater Interfaces 10: 9969–9979. doi: 10.1021/acsami.8b01294
![]() |
[71] |
Hinton TJ, Jallerat Q, Palchesko RN, et al. (2015) Three-dimensional printing of complex biological structures by freeform reversible embedding of suspended hydrogels. Sci Adv 1: e1500758–e1500758. doi: 10.1126/sciadv.1500758
![]() |
[72] |
Suntornnond R, Tan EYS, An J, et al. (2017) A highly printable and biocompatible hydrogel composite for direct printing of soft and perfusable vasculature-like structures. Sci Rep 7: 1–11. doi: 10.1038/s41598-016-0028-x
![]() |
[73] |
Lee V, Singh G, Trasatti JP, et al. (2014) Design and Fabrication of Human Skin by Three-Dimensional Bioprinting. Tissue Eng Part C Methods 20: 473–484. doi: 10.1089/ten.tec.2013.0335
![]() |
[74] | Qilong Z, Juan W, Huanqing C, et al. (2018) Programmed shape‐morphing scaffolds enabling facile 3D endothelialization. Adv Funct Mater 0: 1801027. |
[75] |
Yu Y, Moncal KK, Li J, et al. (2016) Three-dimensional bioprinting using self-assembling scalable scaffold-free "tissue strands" as a new bioink. Sci Rep 6: 28714. doi: 10.1038/srep28714
![]() |
[76] |
Xu C, Chai W, Huang Y, et al. (2012) Scaffold-free inkjet printing of three-dimensional zigzag cellular tubes. Biotechnol Bioeng 109: 3152–3160. doi: 10.1002/bit.24591
![]() |
[77] |
Zhang Y, Yu Y, Chen H, et al. (2013) Characterization of printable cellular micro-fluidic channels for tissue engineering. Biofabrication 5: 25004. doi: 10.1088/1758-5082/5/2/025004
![]() |
[78] | Visser CW, Kamperman T, Karbaat LP, et al. (2018) In-air microfluidics enables rapid fabrication of emulsions, suspensions, and 3D modular (bio)materials. Sci Adv 4: 1–9. |
[79] | Daniel JT, Jessop ZM, Whitaker IS (2017) 3D Bioprinting for Reconstructive Surgery Techniques and Applications. Woodhead Publishing. |
[80] |
Mandrycky C, Wang Z, Kim K, et al. (2016) 3D bioprinting for engineering complex tissues. Biotechnol Adv 34: 422–434. doi: 10.1016/j.biotechadv.2015.12.011
![]() |
[81] |
Catros S, Fricain JC, Guillotin B, et al. (2011) Laser-assisted bioprinting for creating on-demand patterns of human osteoprogenitor cells and nano-hydroxyapatite. Biofabrication 3: 025001. doi: 10.1088/1758-5082/3/2/025001
![]() |
[82] |
Catros S, Guillotin B, Bačáková M, et al. (2011) Effect of laser energy, substrate film thickness and bioink viscosity on viability of endothelial cells printed by laser-assisted bioprinting. Appl Surf Sci 257: 5142–5147. doi: 10.1016/j.apsusc.2010.11.049
![]() |
[83] |
Grogan SP, Chung PH, Soman P, et al. (2013) Digital micromirror device projection printing system for meniscus tissue engineering. Acta Biomater 9: 7218–7226. doi: 10.1016/j.actbio.2013.03.020
![]() |
[84] |
Sorkio A, Koch L, Koivusalo L, et al. (2018) Human stem cell based corneal tissue mimicking structures using laser-assisted 3D bioprinting and functional bioinks. Biomater 171: 57–71. doi: 10.1016/j.biomaterials.2018.04.034
![]() |
[85] |
Gruene M, Pflaum M, Deiwick A, et al. (2011) Adipogenic differentiation of laser-printed 3D tissue grafts consisting of human adipose-derived stem cells. Biofabrication 3: 015005. doi: 10.1088/1758-5082/3/1/015005
![]() |
[86] |
Foyt DA, Norman MDA, Yu TTL, et al. (2018) Exploiting advanced hydrogel technologies to address key challenges in regenerative medicine. Adv Healthc Mater 7: 1700939. doi: 10.1002/adhm.201700939
![]() |
[87] |
Shanjani Y, Pan CC, Elomaa L, et al. (2015) A novel bioprinting method and system for forming hybrid tissue engineering constructs. Biofabrication 7: 045008. doi: 10.1088/1758-5090/7/4/045008
![]() |
[88] | Aguilar JP, Lipka M, Primo GA, et al. (2018) 3D Electrophoresis-assisted lithography (3DEAL): 3D molecular printing to create functional patterns and anisotropic hydrogels. Adv Funct Mater 28: 1–10. |
[89] |
Hribar KC, Meggs K, Liu J, et al. (2015) Three-dimensional direct cell patterning in collagen hydrogels with near-infrared femtosecond laser. Sci Rep 5: 17203. doi: 10.1038/srep17203
![]() |
[90] |
Wang Z, Jin X, Dai R, et al. (2016) An ultrafast hydrogel photocrosslinking method for direct laser bioprinting. RSC Adv 6: 21099–21104. doi: 10.1039/C5RA24910D
![]() |
[91] |
Miri AK, Nieto D, Iglesias L, et al. (2018) Microfluidics-enabled multimaterial maskless stereolithographic bioprinting. Adv Mater 30: e1800242. doi: 10.1002/adma.201800242
![]() |
[92] |
Mosadegh B, Xiong G, Dunham S, et al. (2015) Current progress in 3D printing for cardiovascular tissue engineering. Biomed Mater 10: 034002. doi: 10.1088/1748-6041/10/3/034002
![]() |
[93] |
Ringeisen BR, Pirlo RK, Wu PK, et al. (2013) Cell and organ printing turns 15: Diverse research to commercial transitions. MRS Bull 38: 834–843. doi: 10.1557/mrs.2013.209
![]() |
[94] |
Duan B (2017) State-of-the-art review of 3D bioprinting for cardiovascular tissue engineering. Ann Biomed Eng 45: 195–209. doi: 10.1007/s10439-016-1607-5
![]() |
[95] |
Gao Q, Liu Z, Lin Z, et al. (2017) 3D bioprinting of vessel-like structures with multilevel fluidic channels. ACS Biomater Sci Eng 3: 399–408. doi: 10.1021/acsbiomaterials.6b00643
![]() |
[96] | Khademhosseini A, Camci-Unal G (2018) 3D Bioprinting in Regenerative Engineering: Principles and Applications. CRC Press. |
[97] |
Wu Y, Lin ZY (William), Wenger AC, et al. (2018) 3D bioprinting of liver-mimetic construct with alginate/cellulose nanocrystal hybrid bioink. Bioprinting 9: 1–6. doi: 10.1016/j.bprint.2017.12.001
![]() |
[98] |
Visconti RP, Kasyanov V, Gentile C, et al. (2010) Towards organ printing: engineering an intra-organ branched vascular tree. Expert Opin Biol Ther 10: 409–420. doi: 10.1517/14712590903563352
![]() |
[99] |
Prendergast ME, Montoya G, Pereira T, et al. (2018) Microphysiological systems: automated fabrication via extrusion bioprinting. Microphysiological Syst 2: 1–16. doi: 10.21037/mps.2017.12.01
![]() |
[100] |
Charbe N, McCarron PA, Tambuwala MM (2017) Three-dimensional bio-printing: A new frontier in oncology research. World J Clin Oncol 8: 21–36. doi: 10.5306/wjco.v8.i1.21
![]() |
[101] |
Gopinathan J, Noh I (2018) Recent trends in bioinks for 3D printing. Biomater Res 22: 11. doi: 10.1186/s40824-018-0122-1
![]() |
[102] |
Guvendiren M, Molde J, Soares RMD, et al. (2016) Designing biomaterials for 3d printing. ACS Biomater Sci Eng 2: 1679–1693. doi: 10.1021/acsbiomaterials.6b00121
![]() |
[103] |
Gu Q, Tomaskovic-Crook E, Wallace GG, et al. (2017) 3D bioprinting human induced pluripotent stem cell constructs for in situ cell proliferation and successive multilineage differentiation. Adv Healthc Mater 6: 1700175. doi: 10.1002/adhm.201700175
![]() |
[104] |
Ong CS, Fukunishi T, Zhang H, et al. (2017) Biomaterial-free three-dimensional bioprinting of cardiac tissue using human induced pluripotent stem cell derived cardiomyocytes. Sci Rep 7: 4566. doi: 10.1038/s41598-017-05018-4
![]() |
[105] | Medvedev SP, Shevchenko AI, Zakian SM (2010) Induced pluripotent stem cells: problems and advantages when applying them in regenerative medicine. Acta Nat 2: 18–28. |
[106] |
Wang W, Yang J, Liu H, et al. (2011) Rapid and efficient reprogramming of somatic cells to induced pluripotent stem cells by retinoic acid receptor gamma and liver receptor homolog 1. Proc Natl Acad Sci 108: 18283–18288. doi: 10.1073/pnas.1100893108
![]() |
[107] |
Tidball AM, Dang LT, Glenn TW, et al. (2017) Rapid generation of human genetic loss-of-function ipsc lines by simultaneous reprogramming and gene editing. Stem Cell Reports 9: 725–731. doi: 10.1016/j.stemcr.2017.07.003
![]() |
[108] |
Rutz AL, Hyland KE, Jakus AE, et al. (2015) A multi-material bioink method for 3D printing tunable, cell-compatible hydrogels. Adv Mater 27: 1607–1614. doi: 10.1002/adma.201405076
![]() |
[109] |
Vatani M, Choi JW (2017) Direct-print photopolymerization for 3D printing. Rapid Prototyp J 23: 337–343. doi: 10.1108/RPJ-11-2015-0172
![]() |
[110] |
Tappa K, Jammalamadaka U (2018) Novel biomaterials used in medical 3D printing techniques. J Funct Biomater 9: 17. doi: 10.3390/jfb9010017
![]() |
[111] |
Aljohani W, Ullah MW, Zhang X, et al. (2018) Bioprinting and its applications in tissue engineering and regenerative medicine. Int J Biol Macromol 107: 261–275. doi: 10.1016/j.ijbiomac.2017.08.171
![]() |
1. | Kamal A. R. Ismail, Fatima A. M. Lino, Odenir de Almeida, Mohamed Teggar, Vicente Luiz Scalon, Willian M. Okita, Review on Small Horizontal-Axis Wind Turbines, 2024, 49, 2193-567X, 1367, 10.1007/s13369-023-08314-6 | |
2. | Mohammed Haiek, Yassine Lakhal, Nabil Ben Said Amrani, Driss Sarsri, Souleymane Samagassi, B. Djafari-Rouhani, R. Boukherroub, Y. Ziat, N. Lakouari, Z. Zarhri, Metamodeling for predicting the behavior of airfoils of wind turbine blades: An integration of artificial neural networks, 2024, 582, 2267-1242, 03002, 10.1051/e3sconf/202458203002 |
![]() |
![]() |
Dtip[m] | λ | AEOS[kWh/a] | n at c0 = 6 m/s [rpm] | n at c0 = 12 m/s [rpm] | Fax at c0 = 12 m/s [N] | Remarks | |
1 | 0.8 | 4.0 | 108 | 500 | 1990 | 28 | lowest AEOS, glancing intersection of torque curves at high c0 may yield ambiguous rotational speeds |
2 | 1.0 | 3.0 | 132 | 530 | 1250 | 31 | low AEOS |
3 | 1.0 | 4.0 | 162 | 560 | 1690 | 44 | best compromise |
4 | 1.0 | 5.0 | 176 | 580 | 1990 | 51 | Largest n @ c0 = 12 m/s largest Dtip |
5 | 1.2 | 4.0 | 181 | 591 | 1470 | 64 | large Dtip, large T @ c0 = 12 m/s [N] |
6 | 1.3 | 4.0 | 168 | 591 | 1360 | 73 | large Dtip, largest T @ c0 = 12 m/s [N] |
BE | r/rtip | L [m] | γ [°] |
1 | 0.190 | 0.306 | 29.178 |
2 | 0.248 | 0.300 | 24.236 |
3 | 0.306 | 0.284 | 20.326 |
4 | 0.364 | 0.265 | 17.223 |
5 | 0.421 | 0.246 | 14.738 |
6 | 0.479 | 0.229 | 12.721 |
7 | 0.537 | 0.214 | 11.069 |
8 | 0.595 | 0.201 | 9.693 |
9 | 0.653 | 0.189 | 8.540 |
10 | 0.711 | 0.179 | 7.562 |
11 | 0.769 | 0.170 | 6.726 |
12 | 0.826 | 0.162 | 6.006 |
13 | 0.884 | 0.155 | 5.382 |
14 | 0.942 | 0.149 | 4.835 |
15 | 1.000 | 0.143 | 4.358 |
![]() |
![]() |
Dtip[m] | λ | AEOS[kWh/a] | n at c0 = 6 m/s [rpm] | n at c0 = 12 m/s [rpm] | Fax at c0 = 12 m/s [N] | Remarks | |
1 | 0.8 | 4.0 | 108 | 500 | 1990 | 28 | lowest AEOS, glancing intersection of torque curves at high c0 may yield ambiguous rotational speeds |
2 | 1.0 | 3.0 | 132 | 530 | 1250 | 31 | low AEOS |
3 | 1.0 | 4.0 | 162 | 560 | 1690 | 44 | best compromise |
4 | 1.0 | 5.0 | 176 | 580 | 1990 | 51 | Largest n @ c0 = 12 m/s largest Dtip |
5 | 1.2 | 4.0 | 181 | 591 | 1470 | 64 | large Dtip, large T @ c0 = 12 m/s [N] |
6 | 1.3 | 4.0 | 168 | 591 | 1360 | 73 | large Dtip, largest T @ c0 = 12 m/s [N] |
BE | r/rtip | L [m] | γ [°] |
1 | 0.190 | 0.306 | 29.178 |
2 | 0.248 | 0.300 | 24.236 |
3 | 0.306 | 0.284 | 20.326 |
4 | 0.364 | 0.265 | 17.223 |
5 | 0.421 | 0.246 | 14.738 |
6 | 0.479 | 0.229 | 12.721 |
7 | 0.537 | 0.214 | 11.069 |
8 | 0.595 | 0.201 | 9.693 |
9 | 0.653 | 0.189 | 8.540 |
10 | 0.711 | 0.179 | 7.562 |
11 | 0.769 | 0.170 | 6.726 |
12 | 0.826 | 0.162 | 6.006 |
13 | 0.884 | 0.155 | 5.382 |
14 | 0.942 | 0.149 | 4.835 |
15 | 1.000 | 0.143 | 4.358 |