Before the 1970s, the majority of high-grade musculoskeletal tumors involving the distal femur were treated with transfemoral amputation owing to an unacceptably high rate of recurrence associated with local resection [10, 19, 31, 47]. As effective chemotherapeutic regimens were developed, limb salvage using various techniques gained popularity among orthopaedic oncologists [1, 11, 19, 20, 24, 37, 45, 49, 60, 69]. Today, with effective neoadjuvant chemotherapy, limb salvage is indicated in as much as 90% of patients with musculoskeletal malignancies involving the distal femur [6, 7, 14, 44, 53–55, 57].

Numerous studies document relatively high implant survival after limb salvage for tumors involving the distal femur [3, 4, 8, 26, 27, 29, 35, 43, 44, 50, 54, 55, 57, 61, 71]. Studies that are available, however, do not stratify patients on the basis of tumor grade, stage of disease, or life expectancy to define the disease-specific survival of implants. This makes it difficult for surgeons to accurately predict how long the implants will last for a given patient population and life expectancy. Additionally, there are limited data available with which to compare implant survival of contemporary modular implant designs with older custom-designed implants no longer in use [8, 44, 48, 70]. Critics of a cemented endoprosthetic reconstruction technique cite rates of aseptic loosening from 8.4% to greater than 30% [2, 30, 38, 63] as the main rationale for abandoning its use in favor of newer designs.

Given the paucity of long-term data concerning cemented distal femoral implants and the heightened interest in alternate fixation designs, we sought to answer the following four questions: (1) Do newer cemented modular implant designs have improved survivorship compared with older custom-designed components? (2) Does tumor grade or stage influence implant survival? (3) What is the typical long-term functional result after a cemented distal femoral replacement? (4) What are the complications associated with this technique?

From the charts, we recorded the index diagnosis and disease stage at the time of presentation (according to the system described by Enneking et al. [22, 25]), length of followup, postoperative function scores, implant type and manufacturer, and any major postoperative events (systemic or local complications, repeat surgery for any reason, revision of stemmed components, and/or local recurrence).

All endoprosthetic reconstructions were performed by the same surgeon (JJE), and all tumor resections followed generally accepted oncologic principles [7, 12, 14, 15]. A longitudinal medial incision extended from the tibial tubercle proximally following the course of the sartorius muscle, and the neurovascular bundle was identified and protected. Tourniquets were never used. All previous open biopsy sites were left in continuity with the resected mass; needle biopsy sites were ignored. The femoral and tibial osteotomies were made with the intention that postreconstruction leg lengths would be equal. A rotating-hinge knee mechanism was used in all cases that incorporated an 8-mm all-polyethylene nonmetal-backed tibial component. The distance between the distal end of the metal femoral component and the undersurface of the all-polyethylene tibial component when assembled was 17 mm. To ensure leg length equality, the femoral osteotomy was made 1 cm longer than the femoral component length, and 7 mm of proximal tibia was resected. The location of the patella relative to the joint line was never a conscious consideration. The level of resection was marked on the femur proximally with an osteotome, followed by a slightly more proximal mark on the femur and a mark on the proximal tibia (distal to the level of resection). The distance between the latter two marks was measured and recorded. This preresection distance should equal the postreconstruction distance to ensure limb length equality. A final mark was placed at the most anterior aspect of the femur to ensure proper femoral component rotation as the location of the linea aspera was not always exactly posterior.

After the femoral osteotomy, the proximal marrow was sent for frozen-section analysis to confirm a negative marrow margin. A trial tibial component was placed, and in all cases, an intraoperative radiograph was obtained to ensure placement perpendicular to the mechanical axis of the tibia. The trial hinge mechanism was reduced, and restoration of the preresection extremity length and rotation were verified using marks previously made on the proximal tibia and femur. The neurovascular bundle was palpated to ensure there was not excessive tension on the vessels, and a Doppler probe at the ankle confirmed the presence of the posterior tibial and dorsalis pedis pulses. We routinely used antibiotic-impregnated cement for all endoprosthetic reconstructions. The all-polyethylene tibial and patellar components were cemented first, followed by the femoral component separately. All patients were administered 100 mg Solu-Cortef^® (Pfizer Inc, New York, NY) before placement of the femoral component, and the prosthesis was introduced slowly to avoid causing a fat embolism.

Implants were manufactured by one of three companies: Stryker/Howmedica (Mahwah, NJ), Techmedica (Camarillo, CA), and Dow-Corning Wright Corp (Arlington, TN). All implants used a rotating-hinge knee mechanism. The 156 implants (83.9%) manufactured by Stryker/Howmedica used the Kinematic™ rotating-hinge mechanism [33]. The 28 implants (15.1%) manufactured by Techmedica used the Noiles™ rotating hinge, whereas the two (1.1%) manufactured by Dow-Corning Wright used the Lacey rotating-hinge knee (Figs. 1, 2). Initially, the first 101 (54.3%) prostheses were custom designed by two of the senior authors (JMK, JJE) as a one-piece femoral component [56]. Seventy-three of 101 custom implants were Co-Cr-Mo alloy components manufactured by Howmedica. The bodies were casted using the lost-wax method, and the casted stems, based on the Zickel nail design, were welded to the body. All 28 of the Techmedica components were manufactured completely from titanium. In 1990, modular endoprostheses were introduced and subsequently used in 85 patients (45.7%). Conventional nonmetal-backed polyethylene tibial components were used in all cases. All patellae were resurfaced using a nonmetal-backed all-polyethylene single central-pegged component.

Fig. 1A–C (A) A custom endoprosthesis featuring a body casted by the lost-wax method and used from 1980 to 1985 is shown. The stem, based on the Zickel nail design, was welded to the body. (B) An extramedullary porous coating was added to the prosthesis used from 1985 to 1990, which acts as a scaffolding for soft tissue ingrowth. This presumably protects the stem from debris wear and may reduce aseptic loosening. (C) A contemporary modular endoprosthesis used since 1990 features titanium segments and Co-Cr-Mo alloy Morse tapers that prevent cold welding.

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Fig. 2 The Lacey, Kinematic, and Noiles rotating-hinge mechanisms used in this series are shown.

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Before the introduction of the continuous passive motion (CPM) machine, patients initially were immobilized in a cast for 2 to 3 weeks before physical therapy. Since the introduction of the CPM machine in the early 1980s, all patients were placed into a CPM machine in the operating room. Motion was commenced from –5° extension to 30° to 45° flexion and gradually increased to greater than 90° flexion before discharge. A towel roll under the heel was used three times daily for 1 hour to ensure full extension was achieved. On the third postoperative day, patients were made weightbearing as tolerated with ambulatory supports and a knee immobilizer, which were used for 6 to 8 weeks. The CPM machine was used at home for 12 hours a day for 1 month to help ensure maximum flexion was achieved.

Patients were followed every 2 to 3 weeks for the first 2 months after surgery, then on a quarterly basis for 2 years, semiannually for an additional 2 years, and annually thereafter. Radiographs of the affected limb were obtained at each postoperative visit, along with quarterly chest radiographs and semiannual chest CT. Postoperative function was evaluated for each patient using the Musculoskeletal Tumor Society (MSTS) function score [23]. One hundred sixty of the 186 patients (86.0%) were available for functional evaluation and did not undergo amputation during the followup period.

Patient and prosthesis survival rates and 95% confidence intervals (CIs) were determined for all three groups using the Kaplan-Meier product-limit method [34]. Patient survival was analyzed using death attributable to disease progression as an end point. Prosthesis survivorship was determined for custom and modular implants separately using revision of the stemmed components for any reason as an end point. For purposes of implant survival, we did not include surgery attributable to failure of the bushings, the axle, or the metal tibial bearing component, all of which were managed successfully without the need for revision of major stemmed components. Implant and patient survival curves for the two types of implants and three grades or stages of malignancy were compared using the log-rank method [42]. Statistical analysis was performed using a commercially available statistics package (R, Version 2.9.0, The R Foundation for Statistical Computing, Vienna, Austria).

Modular implants had greater survivorship (p = 0.011) than those of a custom design, with a 15-year survivorship rate of 93.7% versus 51.7% (Fig. 3). Of the 186 index procedures, 35 stemmed components (18.8%) were revised: 32 revisions were performed owing to mechanical failure, whereas an additional three revisions were necessary owing to nonmechanical complications. Thirty-one custom-casted stems were revised; 19 were revised for aseptic loosening of the femoral stem, nine for fatigue fracture, two for infection, and one for local recurrence. Only four of 85 forged modular components were revised: three for aseptic loosening and one for a fatigue fracture of a casted (not forged) Morse taper component. There were no stem fractures among forged modular implants. Failure of the rotating-hinge mechanism necessitated replacement of the bushings and/or axle without revision of the stemmed components in 22 patients (11.8%) at a mean of 159.7 months (range, 1.6–291.1 months) from the index procedure; six of these patients (3.2%) ultimately required a second bushing change. Using revision of the stemmed components for any reason as an end point, overall prosthesis survival rates at 10, 20, and 25 years were 77.2%, 57.9%, and 50.2%, respectively (Fig. 4; Table 2).

Fig. 3A–B  Kaplan-Meier survivorship analyses show (A) custom (n = 101) versus (B) modular (n = 85) implant survival. The dashed lines represent the 95% CI.

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Fig. 4 The Kaplan-Meier survivorship analysis shows overall prosthesis survival (n = 186). The dashed lines represent the 95% CI.

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Table 2 Implant survival, patient survival, and overall limb salvage data

Survival	5 years			10 years			15 years			20 years			25 years
	%	95% CI		%	95% CI		%	95% CI		%	95% CI		%	95% CI
		Lower	Upper		Lower	Upper		Lower	Upper		Lower	Upper		Lower	Upper
Implant survival
Low grade (n = 43)	83.3%	71.9%	96.5%	73.5%	58.5%	92.3%	73.5%	58.5%	92.3%	61.2%	40.1%	93.6%	30.6%	7.2%	100.0%
Stage IIA/IIB (n = 122)	89.8%	83.5%	96.5%	78.4%	68.2%	90.2%	55.7%	41.6%	74.7%	50.7%	35.8%	71.7%	45.0%	29.7%	68.4%
Stage III (n = 21)	85.7%	63.3%	100.0%	NA			NA			NA			NA
Custom (n = 101)	83.5%	75.2%	92.7%	69.2%	58.1%	82.4%	51.7%	39.1%	68.4%	48.7%	35.9%	66.0%	42.2%	29.4%	60.7%
Modular (n = 85)	93.7%	87.9%	99.9%	93.7%	87.9%	99.9%	93.7%	87.9%	99.9%	NA			NA
Overall (n = 186)	87.7%	82.2%	93.7%	77.2%	68.7%	86.7%	61.6%	50.1%	75.7%	57.9%	45.6%	73.5%	50.2%	36.8%	68.5%
Patient survival by diagnosis
Low grade (n = 43)	100.0			100.0			100.0			100.0			100.0
Stage IIA/IIB (n = 122)	65.3%	56.9%	74.9%	57.7%	48.7%	68.4%	56.0%	46.8%	67.0%	56.0%	46.8%	67.0%	56.0%	46.8%	67.0%
Stage III (n = 21)	25.6%	11.6%	56.4%	NA			NA			NA			NA
Overall limb salvage	91.3%	86.7%	96.3%	89.0%	83.5%	94.8%	85.2%	77.9%	93.1%	78.8%	68.6%	90.6%	78.8%	68.6%	90.6%

CI = confidence interval; NA = not available.

Modular implant survival was greater (p = 0.001) than patient survival for those in disease Groups 2 and 3. All patients initially diagnosed with low-grade or aggressive benign tumors (Group 1, n = 43) survived (Fig. 5; Table 2). The 10-, 20-, and 25-year disease-specific survival rates for patients diagnosed with high-grade localized disease (Group 2) were 57.7%, 56.0%, and 56.0%, respectively (Fig. 6; Table 2). The 5- and 10-year disease-specific survival rates for patients diagnosed with Stage III sarcomas, metastatic disease, lymphoma, and myeloma (Group 3) were 25.6% and 0%, respectively (Fig. 7; Table 2).

Fig. 5 The Kaplan-Meier survivorship analysis shows survival among patients with low-grade or benign disease (Group 1; n = 43).

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Fig. 6 The Kaplan-Meier survivorship analysis shows survival among patients with high-grade localized (Stage IIA/IIB) disease (Group 2; n = 122). The dashed lines represent the 95% CI.

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Fig. 7 The Kaplan-Meier survivorship analysis shows patient and prosthesis survival among patients with Stage III primary sarcoma, metastatic disease to the distal femur, myeloma, or lymphoma (Group 3; n = 21). The dashed lines represent the 95% CI.

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Among the 160 patients for whom we had functional evaluations and who retained their implants, the mean postoperative MSTS score was 86.7% (mean score, 26.0; range, 11–29). The postoperative ROM on final assessment revealed mean flexion of 110.0° (range, 45°–140°), mean passive extension to 1.3° (range, 0°–40°), and mean active extension lag of 6.9° (range, 0°–120°). A postoperative flexion contracture was observed in seven patients, with a mean value of 10.0° (range, 5°–40°).

Seven systemic complications occurred in seven patients, including four cardiac arrhythmias, and single cases of chemotherapy-related fungal sepsis, acute leukemia, and steroid-induced avascular necrosis of multiple joints. One hundred four local complications occurred in 88 patients; a single complication occurred in 72 patients, and 16 patients experienced multiple complications. Complications included mechanical failure in 54 (29.0%; Fig. 8), superficial wound-related issues in 13 (7.0%), local recurrence in 13 (7.0%), temporary peroneal nerve palsy in seven (3.8%), deep infections in six (3.2%), cement extrusion through a vascular channel in three (1.6%), flexion contracture in three (1.6%), patellofemoral subluxation in two (1.1%), positive oncologic margins in two (1.1%), and stress fracture in one (0.05%). Eighty-one complications required at least one additional surgical procedure. Mechanical failure of the prosthesis occurred in 54 cases (29.0%). Thirty-two were stemmed component revisions and 22 involved replacement of the bushings only, as described previously. Six of 13 patients with local recurrence were treated with an amputation, and seven were palliated. Eight of the 13 patients (61.5%) with local recurrence ultimately died of their disease, and five of the 13 (38.5%) are alive. Of the five patients who currently are alive, four remain disease-free at 50, 141, 166, and 205 months. One patient currently is alive with metastatic pulmonary disease at 38 months after the index procedure. Eighteen of the 186 patients (9.7%) ultimately required amputation after either the index or later revision procedure and were categorized as having failed limb salvage efforts. The reason for amputation was infection in nine patients, local recurrence in six, positive surgical margins in two, and metastasis to the pelvis in one.

Fig. 8A–D  The common modes of mechanical failure seen in this series of cemented rotating-hinge distal femoral endoprostheses from 1980 to 2008 are shown. (A) A radiograph shows aseptic loosening of a custom-casted femoral stem 24 years after the index reconstruction. The absence of extramedullary porous coating on the proximal body is evident. In our series, there were 22 total instances of aseptic loosening: 19 custom and three modular. (B) Fatigue fractures of a custom-casted femoral stem (right) and femoral body (left) are illustrated. There was only one fatigue fracture of a modular component, which was a casted (not forged) Morse taper segment. In our series, there were 10 total fatigue fractures: nine custom and one modular. (C) An axial photograph shows a fractured hollow, custom-casted femoral body. (D) In our series, there were 22 failures of the rotating-hinge bushings, as illustrated in this photograph, 15 custom and seven modular.

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Historically, a debate existed among orthopaedic oncologists regarding which was the most durable method of reconstruction after distal femoral resection. Although high long-term implant survival and functional scores have been reported with a wide variety of reconstructive methods [5, 7, 14, 44, 53–55, 57, 65], our experience with osteoarticular allografts between 1975 and 1979 was poor, and in 1980 we abandoned this method of reconstruction in favor of a cemented endoprosthetic technique [13, 14, 51]. Recently, critics of this technique have cited high rates of aseptic loosening as the major reason for using alternative fixation methods [2, 38]. Such criticism does not consider the potential improvement in cemented implant survival over historical rates attributable to design modifications. We asked the following four questions: (1) Do newer implant designs perform better than older custom-designed implants? (2) Does tumor diagnosis influence implant survival? (3) What is the typical long-term functional result after distal femoral replacement? (4) What are the complications associated with endoprosthetic reconstruction of the distal femur?

The major limitations of this study are its retrospective design, the lack of a control group, and the lack of a prestudy power analysis. The first two limitations are difficult to overcome for numerous reasons. First, musculoskeletal tumors are rare, and although a prospective design certainly would enhance the validity of our conclusions, it would be exceedingly difficult to amass a large series of patients prospectively. Second, comparison to a control group is virtually impossible because other methods of reconstruction were used only rarely at our institution. In the absence of a prestudy power analysis, we have limited our conclusions to address the differences in survival rates and refrained from drawing conclusions when no difference was seen in the data. The questions addressed at the start of this paper will be addressed in light of these few but important limitations.

Largely owing to the low incidence of musculoskeletal sarcomas, few studies document the long-term durability of contemporary cemented distal femoral endoprostheses (Table 3). Published implant survival rates vary from 46.3% to 93.0%, potentially a reflection of heterogeneous patient and implant study populations. When compared with primary total joint implants, the modifications made to cemented endoprosthetic designs have been relatively few. These modifications include the addition of extramedullary porous coating, the development of modular segments, and the use of forged metals that have the potential to reduce the incidence of fatigue fracture [8, 28, 45, 62]. The evolution of the implants used at our institution reflects this general development of endoprosthetic design (Table 4). The data presented here suggest the use of contemporary modular components improve the durability and longevity of the cemented prosthesis when used in distal femoral applications. Although custom-casted stems can last two to three decades, modular designs maintain the intrinsic benefit of immediate availability and the ability to intraoperatively tailor components based on the resection level. Malo et al. [44] reported modular implants were associated with an improved MSTS functional score among 56 patients. Numerous authors [8, 43, 48, 70] have similarly reported modular endoprostheses survive longer than historical custom-designed implants. In our series, the mean time to revision of the four failures among modular implants was 12.5 months (range, 1.6–21.4 months), indicating these failures were possibly the result of technical error rather than implant design (Fig. 9). Three of four modular failures were attributable to aseptic loosening, likely the result of poor cement technique as noted previously. The fourth failure of a modular implant was attributable to fatigue fracture of a casted, not forged, Morse taper segment, emphasizing the importance of this particular design feature. The revision implants for the three cases of aseptic loosening have outlasted the original primary reconstructions. Currently, the mean time from revision surgery for these patients is 138.6 months (range, 107.4–181.2 months). All four patients who underwent revision of a modular implant still maintain successful limb salvage. Although an improvement in survival was seen in this series, we recognize the need for novel implant designs in special circumstances, such as short residual periarticular segments, which we have dealt with by designing a custom implant with cross-stem pin fixation [6]. A compressive intramedullary device based on Wolff’s law (Compress^®; Biomet Inc, Warsaw, IN) was developed to improve fixation in such situations and to reduce the need for custom-designed cemented implants. Five- to 10-year reports of implant survivorship after the use of this device have been promising [2, 38].

Table 3 Review of the available literature

Study	Year	Number of patients	Mean followup (years)	Implant survivorship/revision ratea				Mean MSTS scorea	Amputationa	Infectiona	Local recurrencea
				0–9 years	10–14 years	15–19 years	≥ 20 years
Bradish et al. [4]	1987	40	8	80.0%				15E, 14G, 3F, 5Pb,c	5.0%	7.5%	12.5%
Shih et al. [58]	1993	61	2-6	0–42%g				7E, 19G, 15F, 20Pb,c	8.2%	8.2%	4.9%
Capannna et al. [8]d	1994	95	4.3	75%e				20E, 43G, 12F, 9Pb,c	7.4%	5.0%	5.3%
Rougraff et al. [54]f	1994	34	11		32.4%g			76.7%h	26.0%	NA	11.0%
Malawer and Chou [43]i	1995	31	3.5j	80.0%	80.0%			NAk	12.9%	19.4%	0.0%
Choong et al. [9]	1996	32	3.5j	6.7%g				6E, 14G, 9F, 3Pb,c	0.0%	3.3%	3.1%
Kawai et al. [35]	1998	40	8j	72.0%	58.0%			80.0%	7.5%	10.0%	0.0%
Malo et al. [44]l	2001	56	3	NA				80.4%	NA	NA	NA
Bickels et al. [3]	2002	110	7.8j	93.0%	88.0%			94G/E, 9F, 7Pb,c	3.6%	5.4%	5.4%
Zeegen et al. [71]i	2004	55	5	82%m				NA	NA	NA	NA
Torbert et al. [61]i	2005	57	4.7	84.0%	66.0%			NA	6.5%	2.2%	6.8%
Frink et al. [26]n	2005	83	12	86.0%	86.0%	86.0%		88.0%	NA	NA	2.3%
Sharma et al. [57]	2006	77	4.3	84.0%	79.0%			30b	6.5%	7.8%	6.5%
Schwab et al. [55]o	2006	43	7.5	NA				78.0%	NA	NA	NA
Gosheger et al. [27]i	2006	103	3.8	65.9%				80.0%	NA	12.0%	0.5%
Myers et al. [50]p	2007	335	12	83.0%	78.0%			NA	17.0%	14.0%	6.0%
Jeys et al. [32]g,i	2008	228	9j		68.6%		46.3%	NA	9.2%	12.7%	5.3%
Current studyq	2010	186	8	87.7%	77.2%	61.6%	50.2%	86.7%	9.7%	3.2%	7.0%

^aNumbers (as reported) converted to percentages for ease of comparison; ^baccording to the 1987 scoring system described by Enneking et al. [21]; ^c E = excellent, G = good, F = fair, P = poor, according to the 1987 MSTS scoring system [21]; ^dall uncemented implants; ^eneither revision rates reported nor survivorship analysis done; reported as percentage of good or excellent clinical results; ^fdata for all limb salvage reconstructions reported; ^gpercentage of implants revised reported; ^hdata given for all 73 patients who had limb salvage (including rotationplasties, allograft and allograft-prosthetic composites, and others); ⁱdata for implants at all anatomic sites reported; ^jmedian; ^kfunction for all sites reported at 83.3% with no significant difference between anatomic sites; ^lfunctional outcomes only evaluated; ^mdata reported for all 63 implants; ⁿ83 of 144 patients reported who survived greater than 5 years; ^oonly patellofemoral complications reported; ^pincludes 162 fixed-hinge knees and 173 rotating-hinge knees; survival of rotating-hinge knees only shown; all prostheses custom-made; ^qKaplan-Meier survivorship of implant; MSTS = Musculoskeletal Tumor Society; NA = not available or not studied.

Table 4 Distal femoral implant evolution at University of California Los Angeles*

Date	Implant design	Manufacturer/features	Tumor group (n = 186)
1980–1990	Custom (JJE/JMK)	Stryker/Howmedica	73
		Kinematic™ rotating hinge
		Made of vitallium
		Casted hollow body by lost-wax method
		Welded Zickel nail stem
		Extramedullary porous coating added in 1985 [61]
		Techmedica	28
		All-titanium one piece
		Noiles™ hinge
		Total custom implants	101
1990–2003	Modular	Stryker/Howmedica	53
		Kinematic™ rotating hinge
		Forged modular replacement system
		Titanium segments
		Extramedullary porous coating
		Dow-Corning Wright	2
		Modular titanium
		Lacey hinge
2003–2008	Modular	Stryker Global Modular Replacement System	30
		Kinematic™ rotating hinge
		Forged modular components
		Titanium segments
		Extramedullary porous coating
		Larger axle and bushings
		Press-fit stem option (none in this series)
		Cobalt-chrome Morse taper
		Total modular implants	85

* All components in this series were cemented; all tibial components were nonmetal-backed, all-polyethylene; all used a rotating-hinge knee mechanism; all patellar components were all-polyethylene, nonmetal-backed, with a single central peg.

Fig. 9A–B  (A) An AP radiograph of the femur shows aseptic loosening of the femoral stem 12 months after endoprosthetic reconstruction with a contemporary modular implant. We suspect this occurred owing to last-minute rotational adjustment of the stem as the cement was curing. (B) A lateral radiograph shows the femur 12 years after revision to a larger cemented stem and in this case with cross-stem pin fixation, which is our preferred method of reconstruction for the majority of failures attributable to aseptic loosening.

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By stratifying patients according to disease grade and/or stage, we found a comparison of implant to patient survival provides a useful measure of disease-specific implant efficacy (Fig. 10). Patients with low-grade tumors have a normal life expectancy and thus should expect to outlive their prostheses. As a result, this group almost certainly will require at least one revision procedure in their lifetime. However, none of the patients with disseminated, Stage III disease outlived their prosthesis in this series. For patients with high-grade localized disease (Stage IIA/IIB), overall prosthesis survivorship remained greater than patient survival up to a critical time, at which point the rate of prosthetic failure became greater than patient survival. The rate of modular implant survival, however, continued to exceed patient survival with high-grade localized disease to 15 years. As long-term survival of patients with high-grade disease approaches 70% to 80% [39–41, 46, 52, 66, 67], the improved longevity of modular implants seen in this series supports the notion that a cemented endoprosthesis will continue to provide a durable method of reconstruction.

Fig. 10 A graph shows implant versus patient survival for the entire study cohort. Modular implants performed better than custom implants, with 15-year survival rates of 93.7% versus 51.7%, respectively. Patients with low-grade or benign disease and long-term survivors with high-grade localized disease should expect to undergo at least one revision procedure in their lifetime.

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The functional scores were high for the majority of patients who underwent endoprosthetic distal femoral reconstructions (Table 3). Functional scores are assigned subjectively, and although newer scoring systems have attempted to eliminate subjective terminology, a precise and accurate measurement of function remains elusive. Despite these limitations, however, our results confirm the findings of previous studies, that favorable long-term function is possible after cemented distal femoral endoprosthetic reconstructions.

The most common local complications in our patients included mechanical failure, tumor recurrence, and infection. All 54 cases of mechanical failure (including modular and custom implants) were salvaged with revision to a larger stem, cross-stem fixation, or new components. Similar to findings described elsewhere, mechanical failures of this nature did not seem to compromise the overall limb salvage effort [59, 68]. Infection, however, worsened the prognosis. Five of 19 patients with wound-related complications that occurred after the index procedure required an amputation, and among an additional six patients who had a deep infection after a second or third procedure, four required an amputation. The total amputation rate in this series for all wound-related complications after either the index or revision procedure was nine of 25 (36.0%). We previously reported our preferred method of caring for patients with wound-related issues after endoprosthetic replacement [18]. Local recurrence portended a poor prognosis in this series as 61.5% of patients had died by the time of the most recent followup.

Our study reports the improved survival of cemented distal femoral endoprostheses during the past three decades. Contemporary modular forged implants performed better than the custom-designed prostheses of the 1970s and 1980s. Although failures may occur, mechanical complications can be revised and potentially outlast the original reconstruction. We recognize revision procedures will be necessary for patients with long-term life expectancy, and the need for continued improvement in reconstruction techniques and implant design, as high-grade disease-specific survival rates may continue to improve.