the cluster - chip captures ctc - clusters relying on the strength of cell - cell junctions as they flow under physiological flow speed through a set of triangular pillars ( fig .
the fundamental building block of the cluster - chip is formed by three triangular pillars , two of which form a narrowing channel that funnels the cells into an opening , where the edge of the third pillar is positioned to bifurcate the laminar flow .
as blood flows , single blood cells and single ctcs divert to one of the two streamlines at the bifurcation , passing through the 12 m  100 m opening ( fig .
in contrast , ctc - clusters are held by the leading edge of the bifurcating pillar under a dynamic force balance , even if they are deformable enough to squeeze through either one of the openings ( fig .
sharp bifurcating edge retains the captured ctc - cluster in both streamlines simultaneously and under this dynamic balance , cell - cell junctions within a ctc - cluster serve as points of support for a stable equilibrium ( not possible for a single cell ) while the bifurcating pillar serves as fulcrum ( fig .
the cluster - chip is optimized to handle cellular aggregates with processing flow speeds limited well below the physiological blood flow speed in human capillaries . therefore , captured ctc clusters are not subjected to shear forces higher than those occur in vivo during circulation .
1d ) is much lower than existing microfluidic and filter - based ctc isolation technologies . yet
the chip can interrogate clinical blood specimens at a rate of 2.5 ml / hr due to its highly parallel architecture ( fig .
the cluster - chip is purposely designed to also capture two - cell clusters because , our analysis shows ~92% of ctc - clusters are of oligoclonal nature , including the majority of two - cell clusters , and characterized by an elevated metastatic potential compared to single ctcs .
the cluster - chip operates fundamentally different from filter - based technologies such as porous membranes or microfluidic traps .
the cluster - chip captures cell clusters independent of their deformability allowing capture of ctc - clusters that might otherwise squeeze through a smaller pore ( fig .
1 ) . moreover , captured clusters are retained under a dynamic force balance unlike filters where cells are primarily retained due to their surface tension and are exposed to damaging stresses .
finally the cluster - chip specifically captures cell clusters and does not trap single cells and this specificity enables clog - free processing of unprocessed whole blood samples . to characterize the device , we first spiked artificially formed clusters of the fluorescently labeled mda - mb-231 human breast cancer cells into unlabeled blood samples from healthy donors and captured them using the cluster - chip . to ensure against any chip - mediated cell aggregation , we introduced a 1:1 mixture of gfp - tagged single cells and mcherry - tagged clusters ( 230 cells ) into whole blood , followed by cluster - chip capture ( fig .
all cancer cell clusters captured on the chip were exclusively mcherry positive , and all gfp - tagged single cells flowed unimpeded through the chip , without adhering to the captured clusters ( fig .
this is consistent with our probabilistic analysis , based on the rarity of ctcs within a blood specimen and the large number of uniformly distributed traps ( supplementary fig .
2 ) to quantify the capture efficiency , we imaged and counted clusters captured on the cluster - chip and those that flowed through undetected ( supplementary fig .
the capture efficiency increases with the number of cells within the cluster and decreases with increasing flow rates ( fig .
the reduced capture at high flow rates may result from the failure of the dynamic force balancing smaller clusters , as well as the breaking up of captured clusters under higher shear stress .
we therefore selected 2.5 ml / hr as the optimal flow rate , providing both high capture efficiency and high throughput ( supplementary video 1 ) . at 2.5
ml / hr , the cluster - chip captured 169/171 ( 99% ) mda - mb-231 clusters with 4 cells ( fig .
the cluster - chip captured 28/40 ( 70% ) of 3-cell clusters and 48/117 ( 41% ) of 2-cell clusters .
distribution of captured 2-cell and 3-cell clusters to subsequent rows indicates that the capture efficiency for small clusters can further be improved by adding more rows ( supplementary fig .
4 ) . also , the effectiveness of the ctc - cluster trap in capturing larger clusters ( 4-cell or more ) at 2.5 ml / hr flow rate was confirmed as captured clusters were predominantly ( > 80% ) found in the first row . to ensure against possible damage to the captured clusters at 2.5 ml / hr , we compared the cluster size distribution in the spiked population with the captured population on the cluster - chip .
we characterized the artificial clusters of fluorescently labeled mda - mb-231 cells using microscopy ( supplementary fig .
5 ) followed by gently spiking into whole blood collected from a healthy donor ( online methods ) .
comparison of the size distribution before and after processing show that cluster - chip does preserve the integrity of captured clusters ( fig .
. moreover , majority ( > 95% ) of captured clusters were found in the first row excluding the possibility of damage due to bifurcating cluster traps . to compare the cluster - chip with filter - based isolation techniques , we processed simulated samples using the cluster - chip and membrane filters with 5m pore - diameter .
simulated samples were prepared by spiking clusters of mda - mb-231 cells into whole blood collected from healthy donors .
we processed whole blood sample using the cluster - chip at 2.5 ml / hr at room temperature .
the simulated samples processed with filters were diluted 1:10 ( v / v ) as whole blood samples led to clogging . in direct comparisons , the cluster - chip has higher cluster capture efficiency than membrane filters operated at different filtration pressures ( 0.11.5 psi ) ( fig .
at 1.5 psi , typically used for filtration , we found that cluster capture is inefficient . at 0.1 psi , which is substantially lower than pressures typically employed for filtration , cluster capture efficiency increased to ~26% . at 0.1 psi ,
the effective whole blood processing rate of filter is comparable to the cluster - chip so further reduction is not practical ( fig .
compared to single cell capture efficiencies reported for membrane filters , there may be two reasons for the lower cluster capture efficiency in our experiments .
first , clusters are more likely to be lost during the wash step compared to single cells , which are partially or fully squeezed in pores .
second , we counted only intact clusters excluding some that were damaged ( supplementary fig .
nevertheless , the operational conditions for filters were not optimized for clusters in our experiments and we can not exclude that by changing some of the parameters , capture rate of viable clusters could increase . to compare the cluster - chip with another microfluidic platform , we processed matched specimens through the herringbone - chip ( hb - chip ) , an antibody - based capturing chamber that we had first employed in detecting such clusters .
we used three cell lines representing varying epcam expression levels observable across ctcs : mcf-7 , representing high epcam - expressing epithelial breast cancer cells ; mda - mb-231 , mesenchymal 
triple - negative  breast cancer cells with low epcam expression , and mcf10a - lbx1 , an emt - induced breast cell line with virtually absent epcam expression . in direct comparisons ,
the cluster - chip had 50% and 400% higher efficiency than the anti - epcam coated hb - chip in capturing mcf7 and mda - mb-231 clusters , respectively ( fig .
mcf10a - lbx1 clusters were not captured by the hb - chip , but were readily identified in the cluster - chip ( 10 differential capture ) ( fig .
, the reliance on physical properties of clusters rather than on restricted cancer cell surface epitopes to isolate clusters makes the cluster - chip uniquely suited to studying cancers across different clinical settings .
these include epithelial cancers in which activation of emt during cancer cell invasion triggers loss of epithelial markers , as well as non - epithelial cancers , such as melanoma . besides sensitive
capture , viable release of captured ctc - clusters is critically important for downstream molecular and functional assays .
despite the fact that clusters are not tethered to the cluster - chip through antibody - mediated interactions , we observed that release of captured ctc - clusters is incomplete , especially for large clusters , following reversal of the flow . using reverse flow rates of 2.5250 ml / hr
only succeeded in releasing 114/308 ( 37% ) of captured clusters . to address this problem , we tested sample processing at lower temperatures , known to reduce non - specific cell adhesion .
3a ) , so as to cool the samples transiently , thereby avoiding prolonged cold exposure which is known to activate platelets .
processing samples at 4c substantially improved the cluster release efficiency : 188/236 ( 80% ) of captured clusters were released under 250 ml / hr reverse flow .
the improvement was particularly evident at low reverse flow speeds , which enabled the use of low shear forces , thereby enhancing release of viable cells ( fig .
processing at 4c and release of clusters under 250 ml / hr reverse flow had no notable effect on cell viability ( supplementary fig .
we note that the cluster - chip technology is also compatible with non - adherent coating materials and sacrificial layer approaches .
processing blood samples at 4c also proved to substantially reduce non - specific binding by contaminating blood cells .
in experiments with blood samples from healthy donors , the temperature - dependent reduction in on - chip leukocyte contamination was as high as 50-fold ( fig .
moreover , less non - specific binding of leukocytes to the chip translates into a 15-fold higher product purity for cold - processed samples ( fig .
3d ) , which is particularly important for downstream molecular applications . we applied the technology to blood samples collected from patients with metastatic cancer .
patients with breast cancer ( n=27 ) , melanoma ( n=20 ) and prostate cancer ( n=13 ) ( supplementary table 1 ) provided consent according to an irb - approved protocol at massachusetts general hospital , and 4 ml of blood was directly processed through the cluster - chip , followed by immunofluorescence staining ( online methods ) .
we scored positive those clusters that were a ) positive for specific and well - established cancer - associated markers for the disease type , and b ) cd45 ( leukocyte marker ) negative .
previous studies indicate that those specific markers are very accurate for identifying bona fide cancer cells in circulation .
a representative ctc - cluster from a patient with metastatic breast cancer is shown with on - chip capture ( fig .
in addition to fluorescence microscopic imaging of live cells , we used scanning electron microscopy ( sem ) to image fixed ctc - clusters on the chip from the same patient ( fig .
, we observed a ctc - cluster highly strained even under the very low flow speed in the cluster - chip .
this case shows the extent that a ctc - cluster can deform and also points to the need for elasticity - independent capture mechanism of the cluster - chip , which the filter - based technologies fail to achieve .
we identified ctc - clusters in 11/27 patients with breast cancer ( 40.7% , ~0.5 clusters / ml ) ; 6/20 patients with melanoma ( 30% , ~0.15/ml ) and 4/13 patients with prostate cancer ( 31% , ~0.28/ml ) ( fig .
4b ) . for some patients , multiple ( 23 ) blood samples were obtained and patients scored positive when a ctc - cluster was observed during at least one time - point .
the number of cells within a ctc - cluster ranged from 2 to 19 cells and follows a trend toward exponential distribution ( fig .
we compared the number of ctc - clusters captured using the cluster - chip with the number of single ctcs simultaneously identified using ctc - ichip and found no correlation ( supplementary fig .
9 ) . when processing patient samples , we observed cell debris and fibrins , which did not interfere with chip operation due to large number of traps working in parallel . to test the versatility of the cluster - chip to address biology of ctc - clusters , we first measured tumor cell proliferation markers to explore intra - tumor cell heterogeneity , and then analyzed non - tumor cells that were adherent to tumor cells within the clusters . staining for the proliferation marker ki67
correlates well with invasiveness and poor outcome in comparison with mitotic activity index or phospho - histone h3 staining . in a patient with metastatic breast cancer with large numbers of single and clustered ctcs ,
costaining of ctc - clusters for ki67 , cytokeratin ( tumor marker ) and cd45 showed no notable difference between the proliferative index of these two cell populations : 34/64 ( 53% ) ctcs within clusters were ki67-positive , compared with 162/439 ( 40% ) single ctcs ( fig . 5a and supplementary fig .
the low shear stress of the cluster - chip also facilitates the identification of heterologous cell types that may be attached to tumor cells .
given recent progress in immunotherapy of cancer , the identification of leukocyte populations adherent to tumor cells in the circulation is of particular interest .
overall , we found non - tumor cells to be rare among clusters captured using the cluster - chip ( < 5% of 60 patients ) . while these cells consistently expressed of the pan - leukocyte marker cd45 ( fig .
, we used the cluster - chip to capture ctc - clusters from the blood of a breast cancer patient , released ctc - clusters in solution , stained them against the leukocyte cell surface markers , and then isolated intact ctc - clusters individually using a micromanipulator ( fig .
, we retrieved 15 ctc - clusters , and each of those clusters was individually subjected to rna - sequencing analysis using a next generation platform ( solid 5500 ) .
expression analysis revealed that a ) all brx-11 ctc - clusters expressed low but detectable levels of ctc markers such as keratins , muc1 , epcam and/or cdh1 , b ) 14/15 ctc - clusters expressed high levels of timp1 , a matrix metalloproteinase widely associated to breast cancer cell survival and absent in wbcs , and c ) all brx-11 ctc - clusters were associated to platelets transcripts , while control wbcs were not , consistent with previous reports ( fig .
most ctc - clusters appeared to exist in a hybrid epithelial / mesenchymal state ( supplementary fig .
11 ) , a phenotype observed in instances of breast ctcs and consistent with the possibility of grouped migration .
5c ) expressed transcriptional signatures of tissue - derived macrophages ( e.g. high cd14 , cd33 and cd68 expression ) as well as cd45 , keratins , timp1 and platelets transcripts ( fig .
no enrichment for other leukocyte subclasses were observed , including t cells , b cells , natural killer ( nk ) cells , hematopoietic stem cells ( hscs ) and granulocytes ( fig .
the cluster - chip captures ctc - clusters relying on the strength of cell - cell junctions as they flow under physiological flow speed through a set of triangular pillars ( fig .
the fundamental building block of the cluster - chip is formed by three triangular pillars , two of which form a narrowing channel that funnels the cells into an opening , where the edge of the third pillar is positioned to bifurcate the laminar flow .
as blood flows , single blood cells and single ctcs divert to one of the two streamlines at the bifurcation , passing through the 12 m  100 m opening ( fig .
in contrast , ctc - clusters are held by the leading edge of the bifurcating pillar under a dynamic force balance , even if they are deformable enough to squeeze through either one of the openings ( fig .
sharp bifurcating edge retains the captured ctc - cluster in both streamlines simultaneously and under this dynamic balance , cell - cell junctions within a ctc - cluster serve as points of support for a stable equilibrium ( not possible for a single cell ) while the bifurcating pillar serves as fulcrum ( fig .
the cluster - chip is optimized to handle cellular aggregates with processing flow speeds limited well below the physiological blood flow speed in human capillaries . therefore , captured ctc clusters are not subjected to shear forces higher than those occur in vivo during circulation .
1d ) is much lower than existing microfluidic and filter - based ctc isolation technologies . yet
the chip can interrogate clinical blood specimens at a rate of 2.5 ml / hr due to its highly parallel architecture ( fig .
the cluster - chip is purposely designed to also capture two - cell clusters because , our analysis shows ~92% of ctc - clusters are of oligoclonal nature , including the majority of two - cell clusters , and characterized by an elevated metastatic potential compared to single ctcs .
the cluster - chip operates fundamentally different from filter - based technologies such as porous membranes or microfluidic traps .
the cluster - chip captures cell clusters independent of their deformability allowing capture of ctc - clusters that might otherwise squeeze through a smaller pore ( fig .
1 ) . moreover , captured clusters are retained under a dynamic force balance unlike filters where cells are primarily retained due to their surface tension and are exposed to damaging stresses .
finally the cluster - chip specifically captures cell clusters and does not trap single cells and this specificity enables clog - free processing of unprocessed whole blood samples .
to characterize the device , we first spiked artificially formed clusters of the fluorescently labeled mda - mb-231 human breast cancer cells into unlabeled blood samples from healthy donors and captured them using the cluster - chip . to ensure against any chip - mediated cell aggregation
, we introduced a 1:1 mixture of gfp - tagged single cells and mcherry - tagged clusters ( 230 cells ) into whole blood , followed by cluster - chip capture ( fig .
all cancer cell clusters captured on the chip were exclusively mcherry positive , and all gfp - tagged single cells flowed unimpeded through the chip , without adhering to the captured clusters ( fig .
this is consistent with our probabilistic analysis , based on the rarity of ctcs within a blood specimen and the large number of uniformly distributed traps ( supplementary fig .
2 ) to quantify the capture efficiency , we imaged and counted clusters captured on the cluster - chip and those that flowed through undetected ( supplementary fig .
the capture efficiency increases with the number of cells within the cluster and decreases with increasing flow rates ( fig .
the reduced capture at high flow rates may result from the failure of the dynamic force balancing smaller clusters , as well as the breaking up of captured clusters under higher shear stress .
we therefore selected 2.5 ml / hr as the optimal flow rate , providing both high capture efficiency and high throughput ( supplementary video 1 ) . at 2.5
ml / hr , the cluster - chip captured 169/171 ( 99% ) mda - mb-231 clusters with 4 cells ( fig .
the cluster - chip captured 28/40 ( 70% ) of 3-cell clusters and 48/117 ( 41% ) of 2-cell clusters .
distribution of captured 2-cell and 3-cell clusters to subsequent rows indicates that the capture efficiency for small clusters can further be improved by adding more rows ( supplementary fig .
the effectiveness of the ctc - cluster trap in capturing larger clusters ( 4-cell or more ) at 2.5 ml / hr flow rate was confirmed as captured clusters were predominantly ( > 80% ) found in the first row . to ensure against possible damage to the captured clusters at 2.5 ml / hr , we compared the cluster size distribution in the spiked population with the captured population on the cluster - chip .
we characterized the artificial clusters of fluorescently labeled mda - mb-231 cells using microscopy ( supplementary fig .
5 ) followed by gently spiking into whole blood collected from a healthy donor ( online methods ) .
comparison of the size distribution before and after processing show that cluster - chip does preserve the integrity of captured clusters ( fig .
. moreover , majority ( > 95% ) of captured clusters were found in the first row excluding the possibility of damage due to bifurcating cluster traps . to compare the cluster - chip with filter - based isolation techniques , we processed simulated samples using the cluster - chip and membrane filters with 5m pore - diameter .
simulated samples were prepared by spiking clusters of mda - mb-231 cells into whole blood collected from healthy donors .
we processed whole blood sample using the cluster - chip at 2.5 ml / hr at room temperature .
the simulated samples processed with filters were diluted 1:10 ( v / v ) as whole blood samples led to clogging . in direct comparisons , the cluster - chip has higher cluster capture efficiency than membrane filters operated at different filtration pressures ( 0.11.5 psi ) ( fig .
typically used for filtration , we found that cluster capture is inefficient . at 0.1 psi , which is substantially lower than pressures typically employed for filtration , cluster capture efficiency increased to ~26% . at 0.1 psi ,
the effective whole blood processing rate of filter is comparable to the cluster - chip so further reduction is not practical ( fig .
compared to single cell capture efficiencies reported for membrane filters , there may be two reasons for the lower cluster capture efficiency in our experiments .
first , clusters are more likely to be lost during the wash step compared to single cells , which are partially or fully squeezed in pores .
second , we counted only intact clusters excluding some that were damaged ( supplementary fig .
nevertheless , the operational conditions for filters were not optimized for clusters in our experiments and we can not exclude that by changing some of the parameters , capture rate of viable clusters could increase . to compare the cluster - chip with another microfluidic platform ,
we processed matched specimens through the herringbone - chip ( hb - chip ) , an antibody - based capturing chamber that we had first employed in detecting such clusters .
we used three cell lines representing varying epcam expression levels observable across ctcs : mcf-7 , representing high epcam - expressing epithelial breast cancer cells ; mda - mb-231 , mesenchymal 
triple - negative  breast cancer cells with low epcam expression , and mcf10a - lbx1 , an emt - induced breast cell line with virtually absent epcam expression . in direct comparisons ,
the cluster - chip had 50% and 400% higher efficiency than the anti - epcam coated hb - chip in capturing mcf7 and mda - mb-231 clusters , respectively ( fig .
mcf10a - lbx1 clusters were not captured by the hb - chip , but were readily identified in the cluster - chip ( 10 differential capture ) ( fig .
, the reliance on physical properties of clusters rather than on restricted cancer cell surface epitopes to isolate clusters makes the cluster - chip uniquely suited to studying cancers across different clinical settings .
these include epithelial cancers in which activation of emt during cancer cell invasion triggers loss of epithelial markers , as well as non - epithelial cancers , such as melanoma .
besides sensitive capture , viable release of captured ctc - clusters is critically important for downstream molecular and functional assays . despite the fact that clusters are not tethered to the cluster - chip through antibody - mediated interactions , we observed that release of captured ctc - clusters is incomplete , especially for large clusters , following reversal of the flow . using reverse flow rates of 2.5250 ml / hr only succeeded in releasing 114/308 ( 37% ) of captured clusters . to address this problem , we tested sample processing at lower temperatures , known to reduce non - specific cell adhesion .
3a ) , so as to cool the samples transiently , thereby avoiding prolonged cold exposure which is known to activate platelets .
processing samples at 4c substantially improved the cluster release efficiency : 188/236 ( 80% ) of captured clusters were released under 250 ml / hr reverse flow .
the improvement was particularly evident at low reverse flow speeds , which enabled the use of low shear forces , thereby enhancing release of viable cells ( fig .
processing at 4c and release of clusters under 250 ml / hr reverse flow had no notable effect on cell viability ( supplementary fig .
we note that the cluster - chip technology is also compatible with non - adherent coating materials and sacrificial layer approaches .
processing blood samples at 4c also proved to substantially reduce non - specific binding by contaminating blood cells . in experiments with blood samples from healthy donors ,
the temperature - dependent reduction in on - chip leukocyte contamination was as high as 50-fold ( fig .
, less non - specific binding of leukocytes to the chip translates into a 15-fold higher product purity for cold - processed samples ( fig .
patients with breast cancer ( n=27 ) , melanoma ( n=20 ) and prostate cancer ( n=13 ) ( supplementary table 1 ) provided consent according to an irb - approved protocol at massachusetts general hospital , and 4 ml of blood was directly processed through the cluster - chip , followed by immunofluorescence staining ( online methods ) .
we scored positive those clusters that were a ) positive for specific and well - established cancer - associated markers for the disease type , and b ) cd45 ( leukocyte marker ) negative .
previous studies indicate that those specific markers are very accurate for identifying bona fide cancer cells in circulation .
a representative ctc - cluster from a patient with metastatic breast cancer is shown with on - chip capture ( fig .
in addition to fluorescence microscopic imaging of live cells , we used scanning electron microscopy ( sem ) to image fixed ctc - clusters on the chip from the same patient ( fig .
4a ) . in one case , we observed a ctc - cluster highly strained even under the very low flow speed in the cluster - chip .
this case shows the extent that a ctc - cluster can deform and also points to the need for elasticity - independent capture mechanism of the cluster - chip , which the filter - based technologies fail to achieve .
we identified ctc - clusters in 11/27 patients with breast cancer ( 40.7% , ~0.5 clusters / ml ) ; 6/20 patients with melanoma ( 30% , ~0.15/ml ) and 4/13 patients with prostate cancer ( 31% , ~0.28/ml ) ( fig .
4b ) . for some patients , multiple ( 23 ) blood samples were obtained and patients scored positive when a ctc - cluster was observed during at least one time - point .
the number of cells within a ctc - cluster ranged from 2 to 19 cells and follows a trend toward exponential distribution ( fig .
we compared the number of ctc - clusters captured using the cluster - chip with the number of single ctcs simultaneously identified using ctc - ichip and found no correlation ( supplementary fig .
when processing patient samples , we observed cell debris and fibrins , which did not interfere with chip operation due to large number of traps working in parallel .
to test the versatility of the cluster - chip to address biology of ctc - clusters , we first measured tumor cell proliferation markers to explore intra - tumor cell heterogeneity , and then analyzed non - tumor cells that were adherent to tumor cells within the clusters . staining for the proliferation marker ki67
correlates well with invasiveness and poor outcome in comparison with mitotic activity index or phospho - histone h3 staining . in a patient with metastatic breast cancer with large numbers of single and clustered ctcs ,
costaining of ctc - clusters for ki67 , cytokeratin ( tumor marker ) and cd45 showed no notable difference between the proliferative index of these two cell populations : 34/64 ( 53% ) ctcs within clusters were ki67-positive , compared with 162/439 ( 40% ) single ctcs ( fig . 5a and supplementary fig .
the low shear stress of the cluster - chip also facilitates the identification of heterologous cell types that may be attached to tumor cells .
given recent progress in immunotherapy of cancer , the identification of leukocyte populations adherent to tumor cells in the circulation is of particular interest .
overall , we found non - tumor cells to be rare among clusters captured using the cluster - chip ( < 5% of 60 patients ) . while these cells consistently expressed of the pan - leukocyte marker cd45 ( fig .
, we used the cluster - chip to capture ctc - clusters from the blood of a breast cancer patient , released ctc - clusters in solution , stained them against the leukocyte cell surface markers , and then isolated intact ctc - clusters individually using a micromanipulator ( fig .
5c ) . from a single time - point , we retrieved 15 ctc - clusters , and each of those clusters was individually subjected to rna - sequencing analysis using a next generation platform ( solid 5500 ) . expression analysis revealed that a ) all brx-11 ctc - clusters expressed low but detectable levels of ctc markers such as keratins , muc1 , epcam and/or cdh1 , b ) 14/15 ctc - clusters expressed high levels of timp1 , a matrix metalloproteinase widely associated to breast cancer cell survival and absent in wbcs , and c ) all brx-11 ctc - clusters were associated to platelets transcripts , while control wbcs were not , consistent with previous reports ( fig .
most ctc - clusters appeared to exist in a hybrid epithelial / mesenchymal state ( supplementary fig .
11 ) , a phenotype observed in instances of breast ctcs and consistent with the possibility of grouped migration .
5c ) expressed transcriptional signatures of tissue - derived macrophages ( e.g. high cd14 , cd33 and cd68 expression ) as well as cd45 , keratins , timp1 and platelets transcripts ( fig .
no enrichment for other leukocyte subclasses were observed , including t cells , b cells , natural killer ( nk ) cells , hematopoietic stem cells ( hscs ) and granulocytes ( fig .
we introduce a novel microfluidic technology that specifically isolates ctc - clusters from unprocessed blood samples of patients with cancer .
the dynamic capture of multicellular structures as they are impaled on triangle structures under low flow conditions offers important new capabilities that are not readily achieved with current ctc isolation strategies .
existing technologies primarily target single ctcs and employ non - optimum processing conditions that result in lower sensitivity and specificity . widely used batch purification techniques involve multiple processing steps that are likely to disrupt ctc - clusters .
high - speed fluorescence imaging of minimally enriched blood samples are efficient for ctc - cluster detection but the low purity complicates downstream molecular analysis .
microfluidic devices optimized to isolate single ctcs can also isolate ctc - clusters , although substantial losses of clusters may be associated with the optimization of flow conditions for single ctc capture .
filtering blood samples through membranes with small pores may be effective , but these approaches employ high flow rates resulting in extremely high shear forces . as such ,
ctc - clusters are likely damaged or even squeeze through relatively smaller pores , as modeled in our computer simulation . using the cluster - chip
, we determined that ctc - clusters are heterogeneous , including both actively proliferating cells as well as apparently quiescent cells .
occasionally , ctc - clusters are also found associated with cells of the immune system , and our rna sequencing data revealed that these are most likely tumor - associated macrophages .
this finding supports increasingly appreciated role played by tumor - associated macrophages in cancer progression .
the fact that such tissue - derived macrophages travel with ctc - clusters in the bloodstream has implications for the ability to noninvasively monitor tumor - immune cell interactions , a potentially important benefit , given the increasing use of immune checkpoint blockade in the treatment of multiple different types of cancer .
the cluster - chip enables label - free isolation of unfixed ctc - clusters from unprocessed whole blood specimens from patients with cancer .
the reliance on structural properties of ctc - clusters is particularly important , given the variation in tumor epitope expression , as well as the ability of highly flexible clusters to pass through simple pores .
the ability to capture ctc - clusters at relatively high frequency in patients with metastatic cancer and to release them for biological studies will enable detailed analyses of the physiological role of these clusters in the progression and metastasis of human cancer .
 cancer cells metastasize through the bloodstream either as single migratory circulating tumor cells ( ctcs ) or as multicellular groupings ( ctc - clusters ) . 
 existing technologies for ctc enrichment are designed primarily to isolate single ctcs , and while ctc - clusters are detectable in some cases , their true prevalence and significance remain to be determined . here 
 , we developed a microchip technology ( cluster - chip ) specifically designed to capture ctc - clusters independent of tumor - specific markers from unprocessed blood . 
 ctc - clusters are isolated through specialized bifurcating traps under low shear - stress conditions that preserve their integrity and even two - cell clusters are captured efficiently . using the cluster - chip , we identify ctc - clusters in 3040% of patients with metastatic cancers of the breast , prostate and melanoma . 
 rna sequencing of ctc - clusters confirms their tumor origin and identifies leukocytes within the clusters as tissue - derived macrophages . 
 together , the development of a device for efficient capture of ctc - clusters will enable detailed characterization of their biological properties and role in cancer metastasis . 